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23 pages, 13226 KiB  
Article
Innovative Energy Sustainable Solutions for Urban Infrastructure: Implementing Micro-Pumped Hydro Storage in Singapore’s Multi-Level Carparks
by Chiang Liang Kok, Chee Kit Ho, Yit Yan Koh, Wan Xuan Tay and Tee Hui Teo
Appl. Sci. 2024, 14(17), 7531; https://doi.org/10.3390/app14177531 - 26 Aug 2024
Viewed by 708
Abstract
As part of the initiative to achieve Singapore’s Green Plan 2030, we propose to investigate the potential of utilizing micro-pumped hydroelectric energy storage (PHES) systems in multi-level carparks (MLCP: a stacked car park that has multiple levels, may be enclosed, and can be [...] Read more.
As part of the initiative to achieve Singapore’s Green Plan 2030, we propose to investigate the potential of utilizing micro-pumped hydroelectric energy storage (PHES) systems in multi-level carparks (MLCP: a stacked car park that has multiple levels, may be enclosed, and can be an independent building) as a more environmentally friendly alternative to traditional battery storage for a surplus of solar energy. This study focuses on an MLCP with a surface area of 3311 m2 and a height of 12 m, considering design constraints such as a floor load capacity of 5 kN/m2 and the requirement for a consistent energy discharge over a 12 h period. The research identifies a Turgo turbine as the optimal choice, providing a power output of 2.9 kW at a flow rate of 0.03 m3/s with an efficiency of 85%. This system, capable of storing 1655.5 m3 of water, can supply power to 289 light bulbs (each consuming 10 W) for 15.3 h, thus having the capacity to support up to three MLCPs. These results underscore the environmental advantages of PHES over conventional batteries, highlighting its potential for integration with solar panels to decrease carbon emissions. This approach not only aligns with Singapore’s green initiatives but also promotes the development of a more sustainable energy infrastructure. Full article
(This article belongs to the Section Energy Science and Technology)
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<p>UNSDG 17 goals.</p>
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<p>Singapore’s 2030 Green Plan.</p>
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<p>Different turbine blade profiles [<a href="#B34-applsci-14-07531" class="html-bibr">34</a>].</p>
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<p>Francis turbine general description [<a href="#B34-applsci-14-07531" class="html-bibr">34</a>].</p>
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<p>Turgo turbine general description [<a href="#B34-applsci-14-07531" class="html-bibr">34</a>].</p>
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<p>Pelton turbine general description [<a href="#B34-applsci-14-07531" class="html-bibr">34</a>].</p>
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<p>Kaplan turbine general description [<a href="#B34-applsci-14-07531" class="html-bibr">34</a>].</p>
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<p>Wet and dry cell batteries.</p>
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<p>Schematic of a hydroelectric dam.</p>
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<p>Pumped storage hydropower diagram.</p>
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<p>Proposed water tank design.</p>
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<p>MLCP 2022 monthly rainfall chart.</p>
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<p>Singapore Straits Times data.</p>
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<p>Google Map aerial view of carpark.</p>
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<p>Google Street View of carpark.</p>
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<p>Francis turbine specifications (5–10 kW).</p>
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<p>Turgo turbine specifications.</p>
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<p>Pelton turbine specifications.</p>
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<p>Kaplan turbine specifications.</p>
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<p>OSC Submersible Pump specifications.</p>
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<p>OSC Submersible Pump flow rate chart.</p>
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<p>OSC Submersible Pump catalogue data.</p>
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<p>Power comparison of different turbines.</p>
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<p>Number of light bulbs powered.</p>
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<p>Operating duration of different turbines.</p>
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<p>Amount of multi-level carpark powered.</p>
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17 pages, 7216 KiB  
Article
A Double-Rotating Ferrofluid Vane Micropump with an Embedded Fixed Magnet
by Ye Wang, Zhenggui Li, Decai Li, Fang Chen, Qin Zhao, Jie Qing, Xin Li, Chao Yang, Xinyue He and Yi Zhao
Actuators 2024, 13(8), 308; https://doi.org/10.3390/act13080308 - 9 Aug 2024
Viewed by 716
Abstract
This paper introduces the prototype design, magnetic field analysis and experimental test of a double-rotating ferrofluid vane micropump with an embedded fixed magnet. The micropump is based on the working principle of a positive-displacement pump, as well as the magnetic characteristics and flow [...] Read more.
This paper introduces the prototype design, magnetic field analysis and experimental test of a double-rotating ferrofluid vane micropump with an embedded fixed magnet. The micropump is based on the working principle of a positive-displacement pump, as well as the magnetic characteristics and flow properties of magnetic fluid. Through the numerical analysis of the pump cavity magnetic field and the experimental test, the structural parameters of the micropump are optimized reasonably. The pumping flow and pumping height of the micropump were characterized at different driving speeds. The maximum pumping flow rate is approximately 410 μL/min, and the maximum pumping height is approximately 111.4 mm water column. The micropump retains the advantages of simple structure, easy manufacture, flexible control, self-sealing, self-lubrication, low heat production, etc., and can block the pumped liquid backflow. The resulting double-rotating ferrofluid blades can improve pumping efficiency and pumping capacity, and can improve pumping reliability and stability to a certain extent. Full article
(This article belongs to the Section Miniaturized and Micro Actuators)
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<p>Curve of magnetization properties of ferrofluid, where H is the magnetic field strength and σ is the magnetization of ferrofluid.</p>
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<p>Schematic diagram of micropump structure. Here, (<b>a</b>) is the main structure of the micropump, (<b>b</b>) is the overall sheme, and (<b>c</b>) is the PMMA chip for processing the pump chamber.</p>
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<p>The micropump pumping process.</p>
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<p>Magnetic field distribution of pump cavity with different rotation angles <span class="html-italic">θ.</span> (<b>a</b>) RPMs and FPM magnetic poles are in the codirectional direction. (<b>b</b>) RPMs and FPM magnetic poles are in the opposite direction.</p>
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<p>Comparison between the experimental test and the magnetic field distribution cloud map.</p>
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<p>The ferrofluid micropump test system.</p>
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<p>Micropump sample and ferrofluid morphology.</p>
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<p>Motor performance parameters and torque curve.</p>
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<p>Gradient distribution of magnetic field on permanent magnet surface.</p>
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<p>Variation in the RPM magnetic field with distance.</p>
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<p>Pumping process of the ferrofluid micropump.</p>
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<p>Micropump pumping flow at different speeds.</p>
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<p>Micropump pumping height at different speeds.</p>
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52 pages, 12014 KiB  
Review
Advancements in Insulin Pumps: A Comprehensive Exploration of Insulin Pump Systems, Technologies, and Future Directions
by Mohammad Towhidul Islam Rimon, Md Wasif Hasan, Mohammad Fuad Hassan and Sevki Cesmeci
Pharmaceutics 2024, 16(7), 944; https://doi.org/10.3390/pharmaceutics16070944 - 15 Jul 2024
Viewed by 1550
Abstract
Insulin pumps have transformed the way diabetes is managed by providing a more accurate and individualized method of delivering insulin, in contrast to conventional injection routines. This research explores the progression of insulin pumps, following their advancement from initial ideas to advanced contemporary [...] Read more.
Insulin pumps have transformed the way diabetes is managed by providing a more accurate and individualized method of delivering insulin, in contrast to conventional injection routines. This research explores the progression of insulin pumps, following their advancement from initial ideas to advanced contemporary systems. The report proceeds to categorize insulin pumps according to their delivery systems, specifically differentiating between conventional, patch, and implantable pumps. Every category is thoroughly examined, emphasizing its unique characteristics and capabilities. A comparative examination of commercially available pumps is provided to enhance informed decision making. This section provides a thorough analysis of important specifications among various brands and models. Considered factors include basal rate and bolus dosage capabilities, reservoir size, user interface, and compatibility with other diabetes care tools, such as continuous glucose monitoring (CGM) devices and so on. This review seeks to empower healthcare professionals and patients with the essential information to improve diabetes treatment via individualized pump therapy options. It provides a complete assessment of the development, categorization, and full specification comparisons of insulin pumps. Full article
(This article belongs to the Special Issue Micro/Nano Drug Delivery Systems)
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<p>List of potential factors that increase risk diabetics.</p>
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<p>Comparison between insulins type.</p>
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<p>Evolution of insulin pumps.</p>
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<p>Candidates for pump therapy.</p>
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<p>A conventional insulin pump.</p>
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<p>Classification of insulin pump.</p>
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<p>Tandem Mobi, conventional insulin pump.</p>
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<p>EOpatch, a patch pump developed by a Korean company named EOflow.</p>
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<p>A discontinued implantable pump developed by Medtronic Inc. USA [<a href="#B69-pharmaceutics-16-00944" class="html-bibr">69</a>].</p>
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<p>An illustration of the working mechanism of a sensor-augmented pump.</p>
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<p>An illustration of the working mechanism of an AID pump.</p>
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<p>An illustration of the working mechanism of an HCL pump.</p>
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<p>Illustration of a subcutaneous (SC) artificial pancreas with possible uses of glucagon to achieve a fully closed-loop system.</p>
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<p>V-Go pump mechanism.</p>
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<p>The PAQ by CeQur.</p>
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<p>CeQur simplicity by CeQur.</p>
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<p>Cellnovo patch pump.</p>
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<p>The working mechanism of Cellnovo.</p>
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<p>The JewelPump by Debiotech.</p>
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<p>Working mechanism of the piezoelectric insulin pump (JewelPump).</p>
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<p>Accu Check by Roche Diabetes Care GmbH.</p>
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<p>Medisafe with™ (MW), (<b>a</b>) pump components; (<b>b</b>) working mechanism.</p>
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<p>(<b>a</b>) Shape memory alloy technology demonstration; (<b>b</b>) Omnipod Insulin pump by Insulet; (<b>c</b>) pumping mechanism.</p>
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<p>A 3D model of a self-powered insulin pump.</p>
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42 pages, 10634 KiB  
Review
Computational Fluid–Structure Interaction in Microfluidics
by Hafiz Muhammad Musharaf, Uditha Roshan, Amith Mudugamuwa, Quang Thang Trinh, Jun Zhang and Nam-Trung Nguyen
Micromachines 2024, 15(7), 897; https://doi.org/10.3390/mi15070897 - 9 Jul 2024
Cited by 2 | Viewed by 1351
Abstract
Micro elastofluidics is a transformative branch of microfluidics, leveraging the fluid–structure interaction (FSI) at the microscale to enhance the functionality and efficiency of various microdevices. This review paper elucidates the critical role of advanced computational FSI methods in the field of micro elastofluidics. [...] Read more.
Micro elastofluidics is a transformative branch of microfluidics, leveraging the fluid–structure interaction (FSI) at the microscale to enhance the functionality and efficiency of various microdevices. This review paper elucidates the critical role of advanced computational FSI methods in the field of micro elastofluidics. By focusing on the interplay between fluid mechanics and structural responses, these computational methods facilitate the intricate design and optimisation of microdevices such as microvalves, micropumps, and micromixers, which rely on the precise control of fluidic and structural dynamics. In addition, these computational tools extend to the development of biomedical devices, enabling precise particle manipulation and enhancing therapeutic outcomes in cardiovascular applications. Furthermore, this paper addresses the current challenges in computational FSI and highlights the necessity for further development of tools to tackle complex, time-dependent models under microfluidic environments and varying conditions. Our review highlights the expanding potential of FSI in micro elastofluidics, offering a roadmap for future research and development in this promising area. Full article
(This article belongs to the Special Issue Flows in Micro- and Nano-Systems)
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<p>A schematic overview of the computational methods: Finite element method (FEM), boundary element method (BEM), molecular dynamics (MD), lattice Boltzmann method (LBM), and immersed boundary method (IBM) and application domains facilitated by these fluid–structure interaction (FSI) methods.</p>
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<p>Fluid–structure interaction: (<b>A</b>) one-way FSI, (<b>B</b>) two-way FSI.</p>
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<p>(<b>A</b>) Fluid–wall FSI, (<b>B</b>) Fluid–particle FSI. Yellow colour shows the fluid domain and grey colour shows the solid domain.</p>
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<p>Boundaries in typical FSI problem.</p>
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<p>FSI coupling approaches, (<b>A</b>) monolithic, (<b>B</b>) partitioned.</p>
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<p>Mesh discretisation approaches, (<b>A</b>) conforming meshing, (<b>B</b>) non-conforming meshing. White circle and grey area represent the regid body and fluid domain respectively. In conforming meshing scheme, mesh gets updated after every time step while in non-conforming meshing scheme, mesh remains the same.</p>
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<p>Space and time scale of different computational methods with comparative sizes.</p>
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<p>Computational methods for FSIs. (<b>A</b>) Discretisation of fluid and solid domain in the FEM; (<b>B</b>) discretisation of domain in the BEM; (<b>C</b>) molecules’ interaction in the MD method [<a href="#B106-micromachines-15-00897" class="html-bibr">106</a>]; (<b>D</b>) 2D and 3D configurations of the LBM, (<b>i</b>) 2D nine velocity configuration, (<b>ii</b>) 3D nineteen velocity configuration, (<b>iii</b>) 3D twenty seven velocity configuration [<a href="#B107-micromachines-15-00897" class="html-bibr">107</a>]; (<b>E</b>) (<b>i</b>) bounce back method [<a href="#B87-micromachines-15-00897" class="html-bibr">87</a>], (<b>ii</b>) extrapolated bounce back method illustration [<a href="#B107-micromachines-15-00897" class="html-bibr">107</a>]; (<b>F</b>) IBM as a Lagrangian and Eulerian description [<a href="#B87-micromachines-15-00897" class="html-bibr">87</a>].</p>
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<p>Microvalves and micropumps. (<b>A</b>) Ortho-planar micro check valves with different stiffness values [<a href="#B222-micromachines-15-00897" class="html-bibr">222</a>]; (<b>B</b>) Poiseuille law pressure-drop self-regulating valve [<a href="#B223-micromachines-15-00897" class="html-bibr">223</a>]; (<b>C</b>) self-adaptive planar check valve with flexible cantilever flap [<a href="#B224-micromachines-15-00897" class="html-bibr">224</a>]; (<b>D</b>) parallel membrane with low threshold pressure, self-regulating valve [<a href="#B225-micromachines-15-00897" class="html-bibr">225</a>]; (<b>E</b>) Stacked parallel membrane with low threshold pressure, regulating valve [<a href="#B226-micromachines-15-00897" class="html-bibr">226</a>]; (<b>F</b>) ellipsoid control chamber auto-regulating valve [<a href="#B221-micromachines-15-00897" class="html-bibr">221</a>].</p>
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<p>Pumping schemes. (<b>A</b>) Piezoelectric micropump utilising fixed-end PDMS valves with integrated compressible space: (<b>i</b>) dispensing mode, (<b>ii</b>) absorbing mode [<a href="#B232-micromachines-15-00897" class="html-bibr">232</a>]; (<b>B</b>) magnetically actuated membrane micropump with in-plane check valves: (<b>i</b>) priming mode, (<b>ii</b>) pumping mode [<a href="#B233-micromachines-15-00897" class="html-bibr">233</a>]; (<b>C</b>) electrostatically actuated micropump utilising four electrodes to induce peristaltic motion: (<b>i</b>) top-view, (<b>ii</b>) cross-sectional view [<a href="#B234-micromachines-15-00897" class="html-bibr">234</a>]; (<b>D</b>) thermo-pneumatic micropump with a thin polyimide membrane actuator: (<b>i</b>) cross-sectional view, (<b>ii</b>) top view [<a href="#B235-micromachines-15-00897" class="html-bibr">235</a>].</p>
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<p>Cell separation and micromixers. (<b>A</b>) Illustration of considering RBCs and WBCs as suspended particles in plasma to capture fluid–particle and fluid–wall interactions [<a href="#B238-micromachines-15-00897" class="html-bibr">238</a>]; (<b>B</b>) RBC discretisation to investigate the change in deformability of cells caused by malaria parasites, reproduced with permission from Hosseini et al. [<a href="#B240-micromachines-15-00897" class="html-bibr">240</a>]; (<b>C</b>) (<b>i</b>) setup for particle sorting in microchannels, (<b>ii</b>) particle separation, reproduced with permission from Mao et al. [<a href="#B239-micromachines-15-00897" class="html-bibr">239</a>]; (<b>D</b>) DLD device for separating CTCs within blood stream [<a href="#B241-micromachines-15-00897" class="html-bibr">241</a>]; (<b>E</b>) mixing with magnetic actuated artificial cilia [<a href="#B242-micromachines-15-00897" class="html-bibr">242</a>]; (<b>F</b>) passive mixing with flexible baffles [<a href="#B243-micromachines-15-00897" class="html-bibr">243</a>].</p>
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<p>Bi-leaflet mechanical heart valve dynamics through FSI modelling with Smoothed Particle Hydrodynamics (SPH); (<b>A</b>) illustration of mechanical heart valve; (<b>B</b>) opening and closing position of valve; (<b>C</b>) illustration of smoothed particles for simulation; (<b>D</b>) inlet velocity profile to mimic the real pulse; (<b>E</b>) simulation results. Reproduced with permission from Laha et al. [<a href="#B259-micromachines-15-00897" class="html-bibr">259</a>].</p>
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<p>An artificial aortic heart valve. (<b>A</b>) Effect of asymmetry on valve closure (<b>right</b>) and comparison with a similar tex-valve (<b>left</b>); (<b>B</b>) illustration of test setup for FSI simulations; (<b>C</b>) simulation results. Reproduced with permission from Sodhani et al. [<a href="#B260-micromachines-15-00897" class="html-bibr">260</a>].</p>
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<p>Numerical investigation of an Ascending Thoracic Aortic Aneurysm (ATAA) through FSI simulations. (<b>A</b>) Mesh discretisation of patient-specific geometric ascending thoracic aorta model reconstructed from CT scans; (<b>B</b>) simulations results. (<b>i</b>) wall shear stress distribution over the domain, (<b>ii</b>) Velocity magnitude distribution over the domain, (<b>iii</b>) Displacement magnitude distribution over the domain. Reproduced with permission from Valente et al. [<a href="#B268-micromachines-15-00897" class="html-bibr">268</a>].</p>
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18 pages, 2740 KiB  
Entry
Displacement Micropump with Check Valves for Diabetes Care—The Challenge of Pumping Insulin at Negative Pressure
by Eric Chappel
Encyclopedia 2024, 4(2), 818-835; https://doi.org/10.3390/encyclopedia4020052 - 13 May 2024
Viewed by 3007
Definition
The displacement micropump with passive check valves is an attractive solution for precise insulin infusion in patients with type I diabetes. Unlike most insulin pumps that push insulin from a cartridge using a piston, a displacement micropump will first pull insulin from the [...] Read more.
The displacement micropump with passive check valves is an attractive solution for precise insulin infusion in patients with type I diabetes. Unlike most insulin pumps that push insulin from a cartridge using a piston, a displacement micropump will first pull insulin from the reservoir before infusing it into the patient. This dual sequence introduces new challenges in terms of insulin stability, notably if the reservoir is not pressurized. After an introduction to displacement micropumps and a brief review of the insulin degradation mechanism, micropump design rules are discussed in light of microfluidic theory. Full article
(This article belongs to the Section Medicine & Pharmacology)
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<p>Schematic views of the membrane of a displacement micropump with passive check valves during the supply phase (<b>top</b>) and the infusion phase (<b>bottom</b>) [<a href="#B59-encyclopedia-04-00052" class="html-bibr">59</a>].</p>
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<p>Schematic cross-section of a MEMS micropump made of an SOI wafer bonded to top and bottom wafers in silicon (in grey). The buried oxide of the SOI wafer is represented by the green layer while the pink rectangles are the anti-bonding pads. The direction of the flow is indicated by the orange arrow. A piezoelectric bender not represented here pushes and pulls the mesa of the pumping membrane via a flexible metal blade. Mechanical stops allow repeatable and accurate pump strokes of 200 nanoliters [<a href="#B40-encyclopedia-04-00052" class="html-bibr">40</a>].</p>
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<p>Top view of the MEMS micropump obtained using IR microscopy. Adapted from [<a href="#B59-encyclopedia-04-00052" class="html-bibr">59</a>]. The direction of the insulin flow is indicated by the yellow arrows.</p>
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<p>General electrical equivalent network of a displacement micropump with check valves and pressure sensors. The pressures in the reservoir and injection site are modeled by voltage sources. The flow generated during the actuation of the pumping membrane is modeled as a controlled current source. The different fluidic restrictors, including the valves, are represented by fixed or variable resistors, while the compliant elements are modeled by capacitors. Adapted from [<a href="#B23-encyclopedia-04-00052" class="html-bibr">23</a>].</p>
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<p>Principle of the bubble-point test of a hydrophilic filter.</p>
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<p>Capillary adhesion of a schematic annular valve (not to scale). The liquid is represented in blue.</p>
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3 pages, 599 KiB  
Abstract
Development of a Compact, Reliable, and Electrostatically Actuated Device for Microfluidic-Based Active Glasses
by Simon Kulifaj, Clément Chauvin, Antoine Bouvier, Solène Meinier, Fengzhi Gu, Jérôme Degouttes, Nicolas Terrier, Patrick Pittet and Bruno Berge
Proceedings 2024, 97(1), 22; https://doi.org/10.3390/proceedings2024097022 - 14 Mar 2024
Viewed by 515
Abstract
We present the development study of a reliable and low-power actuator for microfluidics-based active glasses. The adaptive part of the lens implements two liquids of a specific refractive index separated by a thin membrane, the modification of their relative volumes allowing adaptive optical [...] Read more.
We present the development study of a reliable and low-power actuator for microfluidics-based active glasses. The adaptive part of the lens implements two liquids of a specific refractive index separated by a thin membrane, the modification of their relative volumes allowing adaptive optical power corrections. The proposed actuator is connected to an adaptive lens by microchannels since it is intended to be installed in the temple of the glasses. The actuation is based on the electrostatic displacement of a thin film, which changes the relative volumes of two cavities filled with these liquids. The metalized film is placed slack with an “S-shape” between two electrodes biased with the actuation voltage. Very compact actuator prototypes have been developed and characterized. Power corrections ranging from +0D to +3D can be achieved via liquid volume displacement as low as 120 µL and with a power consumption of a few mW. The prototypes show good reliability without any significant change in their operation after more than 1 million actuations. For RD purposes, we have replaced some electrodes with transparent windows. With this setup, we show experimental results on the interplay between the performances and the film folding inside the actuator. Full article
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<p>Sectional view of new concept actuator.</p>
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<p>Evolution of the volume displaced by the actuator after 1 million cycles. A measurement is carried outapproximatively every 10,000 cycles (triangles). The total volume displaced remains stable at around 103 +/− 3 µL.</p>
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12 pages, 2983 KiB  
Article
A Light-Powered Micropump with Dynamic Collective Behavior for Reparation
by Yunyu Sun, Hao Wang, Jiwei Jiang, Hui Zhang, Limei Liu, Keying Zhang, Bo Song and Bin Dong
Nanomaterials 2024, 14(6), 517; https://doi.org/10.3390/nano14060517 - 14 Mar 2024
Viewed by 1074
Abstract
Inspired by the collective behaviors of active systems in nature, the collective behavior of micromotors has attracted more and more attention in recent years. However, little attention has been paid to the collective behavior of the immobilized micromotor, i.e., the micropump. In this [...] Read more.
Inspired by the collective behaviors of active systems in nature, the collective behavior of micromotors has attracted more and more attention in recent years. However, little attention has been paid to the collective behavior of the immobilized micromotor, i.e., the micropump. In this paper, a unique pentacene-based micropump is reported, which demonstrates dynamic collective behavior activated by white light irradiation. The light irradiation may generate the photochemical reactions between pentacene and water, leading to the electroosmotic flow. As a result, this micropump is capable of pumping the surrounding solution inward along the substrate surface based on the electroosmosis mechanism. Intriguingly, the inward pumping causes the agglomeration of the tracer particles on the surface of the micropump. In addition, the aggregation can migrate following the change in the light irradiation position between two adjacent micropumps. Based on the aggregating and migrating behaviors of this pentacene-based micropump, we have achieved the conductivity restoration of the cracked circuit. Full article
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<p>Fabrication and characterization of the pentacene-based micropump. (<b>a</b>) Schematic illustration showing the fabricating process of the micropump based on pentacene. (<b>b</b>) Schematic illustration and (<b>c</b>) scanning electron microscope (SEM) image of the micropump. (<b>d</b>) The EDX analysis of the micropump for carbon element. (<b>e</b>) Atomic force microscopy (AFM) image and (<b>f</b>) the section analysis showing the surface morphology and the thickness of the micropump. (<b>g</b>) Enlarged SEM image of the micropump. (<b>h</b>) Enlarged AFM image of the micropump. (<b>i</b>) The section analysis of the surface shown in (<b>g</b>). (<b>j</b>) UV–Vis–NIR spectrum of the pentacene.</p>
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<p>(<b>a</b>) Schematic illustration and (<b>b</b>) overlaid optical microscopic image showing the pumping behavior of the micropump. White balls: tracer particles. Blue arrows: the direction of pumping behavior. (<b>c</b>) The average velocity of tracer particles as a function of the distance from the border of the pentacene micropump. Light intensity: 0.6 W/cm<sup>2</sup>. (<b>d</b>) The average velocity of tracer particles under different light intensities. (<b>e</b>) The aggregating–dispersing recycles of tracers based on the same micropump. I and II represent the aggregation and dispersion states, respectively. Light intensity: 1.2 W/cm<sup>2</sup>.</p>
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<p>(<b>a</b>,<b>b</b>) Schematic illustration of mechanism of the light-activated pumping behavior. (<b>c</b>) The pH of the solution changes with the illuminating time (light intensity 1.2 W/cm<sup>2</sup>). (<b>d</b>) The velocity of the tracer particles decreases as the concentration of NaCl solution increases.</p>
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<p>Schematic (<b>a</b>) and overlaid image (<b>b</b>,<b>c</b>) showing the aggregating behaviors of tracer particles on the focus spot in a system consisting of two adjacent pentacene microstructures. (<b>d</b>–<b>f</b>) Schematic showing dynamic migration of the aggregation tuned by the light. (<b>g</b>–<b>i</b>) The corresponding optical microscopic images of migrating process. Light intensity: 1.2 W/cm<sup>2</sup>.</p>
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<p>(<b>a</b>) Schematic showing the application in light-controlled reparation of the cracked conductive path. (<b>b</b>,<b>c</b>) The optical microscopic images obtained from <a href="#app1-nanomaterials-14-00517" class="html-app">Video S6 in the Supporting Information</a> showing the dynamic repairing process. The red circles are the micropumps.</p>
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25 pages, 13487 KiB  
Article
Flow Analysis and Structural Optimization of Double-Chamber Parallel Flexible Valve Micropumps
by Fan Jiang, Jinfeng Wen and Teng Dong
ChemEngineering 2023, 7(6), 111; https://doi.org/10.3390/chemengineering7060111 - 16 Nov 2023
Viewed by 1649
Abstract
In the current study, a two-dimensional numerical study is carried out to investigate the performance of a novel Double-Chamber Parallel Flexible Valve micropump, which utilized the electrowetting-on-dielectrics (EWOD) effect to drive the microfluid flow. By observing the flow fields, the internal circulations are [...] Read more.
In the current study, a two-dimensional numerical study is carried out to investigate the performance of a novel Double-Chamber Parallel Flexible Valve micropump, which utilized the electrowetting-on-dielectrics (EWOD) effect to drive the microfluid flow. By observing the flow fields, the internal circulations are seen on both the left and right sides of the pump. The generation of the backflow is discussed as well by tracking the movement of the vortices. Only slight flow fluctuations are seen in the micropump. Based on the simulation results, the structural parameters including the width of the inlet and the outlet, the width of the pumping channel and the diverging angle in the micropump are analyzed, and the influence of these parameters on the pumping volume and the maximum pressure are discussed. Eventually, a group of optimal parameter combinations is given according to the simulation results to extend the operating potential of the micropump. Full article
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<p>The 2D structure (flow domain) of the double-chamber parallel flexible valve micropump.</p>
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<p>The dimensions of the microchannels.</p>
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<p>Contact angle and motion of liquid droplets, blue is KCL droplet, and red is silicon oil.</p>
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<p>The meshed geometry.</p>
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<p><b>A</b> Comparison of droplet moving velocity between the simulation and the experiments [<a href="#B17-ChemEngineering-07-00111" class="html-bibr">17</a>].</p>
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<p>Interface sharpness by varying grid resolution, blue is KCL droplet, and red is silicon oil.</p>
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<p>The pumping volume and flow rate in the original micropump.</p>
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<p>The simulated maximum pressure with COMSOL.</p>
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<p>The flow field inside the micropump while the KCL droplet is moving down (<b>a</b>) and up (<b>b</b>) in the pump chamber. The gray line is a streamline, and the red arrow is flowing direction.</p>
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<p>The magnified view of internal flow on the micropump inlet and outlet. The yellow dots indicate the core of the vortices at each time instant.</p>
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<p>The magnified view of the internal flow and the corresponding deformation of the flexible valves, blue is upper wall and flexible valve, and green is bottom wall and flexible valve.</p>
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<p>The velocity contours of the parallel EWOD flexible valve pump.</p>
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<p>The rectangular coordinate system at the inlet and outlet.</p>
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<p>The velocity distribution at the inlet (<b>a</b>,<b>b</b>) and outlet (<b>c</b>,<b>d</b>) of the micropump.</p>
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<p>The structural parameters of the micropump.</p>
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<p>The pumping volume and the maximum pressure in the micropump at different widths of inlet and outlet.</p>
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<p>The velocity distribution at different widths of the outlet, (<b>a</b>) is X-direction, and (<b>b</b>) is Y-direction.</p>
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<p>The relationship of pumping volume and maximum pressure with different microchannel widths.</p>
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<p>The vector velocity distribution at the outlet with different microchannel widths, (<b>a</b>) is X-direction, and (<b>b</b>) is Y-direction.</p>
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<p>The relationship of pumping volume and maximum pressure with different microchannel lengths.</p>
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<p>The relationship of pumping volume and maximum pressure with a different fillet radius.</p>
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<p>The vector velocity distribution at the outlet with a different fillet radius, (<b>a</b>) is X-direction, and (<b>b</b>) is Y-direction.</p>
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<p>The relationship of pumping volume and maximum pressure with different microchannel angles.</p>
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<p>The flow rate of the micropump with different microchannel angles.</p>
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<p>The relationship of pumping volume and maximum pressure with different flexible valve angles.</p>
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<p>The relationship of pumping volume and maximum pressure with different flexible valve width.</p>
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<p>The relationship of pumping volume and maximum pressure with different flexible valve lengths.</p>
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<p>The relationship of pumping volume and maximum pressure with different flexible valve material properties, (<b>a</b>) the effect of flexible valve density on the performance of micropumps, (<b>b</b>) the effect of flexible valve Young’s modulus on micropump performance, and (<b>c</b>) the effect of flexible valve Poisson’s ratio on micropump performance.</p>
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<p>The Pumping performance of in the optimized micropump, (<b>a</b>) is the pumping volume and flow rate, (<b>b</b>) is the maximum pressure.</p>
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4 pages, 392 KiB  
Editorial
Microfluidic Formulation for Biomedical Applications
by Kieu The Loan Trinh
Pharmaceuticals 2023, 16(11), 1587; https://doi.org/10.3390/ph16111587 - 9 Nov 2023
Cited by 2 | Viewed by 1089
Abstract
Microfluidic technology was recognized in the 1980s when the first micropumps and micro-valves were developed to manipulate fluids for biological applications [...] Full article
(This article belongs to the Special Issue Microfluidic Formulation for Biomedical Applications)
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<p>Microfluidic formulation for biomedical applications involving drug development, bacterial identification, real-time assessment of protein, and cocrystal engineering.</p>
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23 pages, 24821 KiB  
Article
Flow Ripple Reduction in Reciprocating Pumps by Multi-Phase Rectification
by Gürhan Özkayar, Zhilin Wang, Joost Lötters, Marcel Tichem and Murali Krishna Ghatkesar
Sensors 2023, 23(15), 6967; https://doi.org/10.3390/s23156967 - 5 Aug 2023
Cited by 1 | Viewed by 1693
Abstract
Reciprocating piezoelectric micropumps enable miniaturization in microfluidics for lab-on-a-chip applications such as organs-on-chips (OoC). However, achieving a steady flow when using these micropumps is a significant challenge because of flow ripples in the displaced liquid, especially at low frequencies or low flow rates [...] Read more.
Reciprocating piezoelectric micropumps enable miniaturization in microfluidics for lab-on-a-chip applications such as organs-on-chips (OoC). However, achieving a steady flow when using these micropumps is a significant challenge because of flow ripples in the displaced liquid, especially at low frequencies or low flow rates (<50 µL/min). Although dampers are widely used for reducing ripples in a flow, their efficiency depends on the driving frequency of the pump. Here, we investigated multi-phase rectification as an approach to minimize ripples at low flow rates by connecting piezoelectric micropumps in parallel. The efficiency in ripple reduction was evaluated with an increasing number (n) of pumps connected in parallel, each actuated by an alternating voltage waveform with a phase difference of 2π/n (called multi-phase rectification) at a chosen frequency. We introduce a fluidic ripple factor (RFfl.), which is the ratio of the root mean square (RMS) value of the fluctuations present in the rectified output to the average fluctuation-free value of the discharge flow, as a metric to express the quality of the flow. The fluidic ripple factor was reduced by more than 90% by using three-phase rectification when compared to one-phase rectification in the 2–60 μL/min flow rate range. Analytical equations to estimate the fluidic ripple factor for a chosen number of pumps connected in parallel are presented, and we experimentally confirmed up to four pumps. The analysis shown can be used to design a frequency-independent multi-phase fluid rectifier to the desired ripple level in a flow for reciprocating pumps. Full article
(This article belongs to the Special Issue The Development of Piezoelectric Sensors and Actuators)
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<p>Working principle of a piezoelectric diaphragm pump. (<b>a</b>) Reciprocating motion of a piezoelectric diaphragm pump (suction and discharge modes) having two passive check valves at the inlet and outlet. (<b>b</b>) Fluidic circuit symbol representation of the micropump (as a one-phase rectifier; the electrical equivalent is shown in <a href="#app2-sensors-23-06967" class="html-app">Appendix A</a>), and (<b>c</b>) output flow rate characteristics with phase.</p>
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<p>Schematic representation of a multi-phase rectifier (n micropumps in parallel with a phase shift), having check valves at the inlets and outlets.</p>
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<p>The theoretically calculated values of <math display="inline"><semantics><mrow><msub><mi>Q</mi><mrow><mi>D</mi><mi>C</mi></mrow></msub></mrow></semantics></math>, <math display="inline"><semantics><mrow><msub><mi>Q</mi><mrow><mi>R</mi><mi>M</mi><mi>S</mi></mrow></msub></mrow></semantics></math>, and fluidic ripple factor (<math display="inline"><semantics><mrow><mi>R</mi><msub><mi>F</mi><mrow><mi>f</mi><mi>l</mi><mo>.</mo></mrow></msub></mrow></semantics></math>) for up to nine-phase rectifiers are shown for a chosen <math display="inline"><semantics><mrow><msub><mi>Q</mi><mrow><mi>S</mi><mi>t</mi><mi>r</mi><mi>o</mi><mi>k</mi><mi>e</mi></mrow></msub></mrow></semantics></math> = 1 for every pump. The <math display="inline"><semantics><mrow><msub><mi>Q</mi><mrow><mi>D</mi><mi>C</mi></mrow></msub></mrow></semantics></math> and <math display="inline"><semantics><mrow><msub><mi>Q</mi><mrow><mi>R</mi><mi>M</mi><mi>S</mi></mrow></msub></mrow></semantics></math> values increase as the phase rectification increases. For a three-phase rectifier, the ripple factor value, <math display="inline"><semantics><mrow><mi>R</mi><msub><mi>F</mi><mrow><mi>f</mi><mi>l</mi><mo>.</mo></mrow></msub></mrow></semantics></math>, dramatically decreases to 3.4% of that of the one-phase rectifier. The <math display="inline"><semantics><mrow><mi>R</mi><msub><mi>F</mi><mrow><mi>f</mi><mi>l</mi><mo>.</mo></mrow></msub></mrow></semantics></math> value goes to 0.38% for a nine-phase rectifier. The <math display="inline"><semantics><mrow><mi>R</mi><msub><mi>F</mi><mrow><mi>f</mi><mi>l</mi><mo>.</mo></mrow></msub></mrow></semantics></math> values for higher-phase rectifiers are given in <a href="#sensors-23-06967-t002" class="html-table">Table 2</a> or can be calculated for any chosen number of phase rectifiers using the MATLAB code given in the <a href="#app1-sensors-23-06967" class="html-app">Supplementary Information</a>.</p>
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<p>Schematic of an experimental setup for multi-phase flow rectification. The inlet and outlet reservoirs were maintained at the same height for conducting the experiments. All pumps were kept at the same height as the inlet reservoir. The height of the outlet reservoir was raised only for the back-pressure experiments (the test setup is given in <a href="#app5-sensors-23-06967" class="html-app">Appendix D</a>). The sinusoidal signals and their phase shifts (PS) were generated in Arduino, shaped by a resistor-capacitor (RC) circuit, and amplified (Amp) 100× before connecting them to the micropumps. The setup was tested for one-phase, two-phase, three-phase, and four-phase rectifiers, respectively. The electrical connections of the components are shown in red, and the fluidic connections are shown in blue.</p>
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<p>The performance of a one-phase rectifier with increasing driving frequency for three different driving voltages is shown. (<b>a</b>) The flow rate values measured over time with increasing driving frequency for three different driving actuation amplitudes of a single-chamber mp6 micropump are plotted. The ripples are large at low frequencies when compared to high frequencies. Moreover, the acquired flow rates were also reduced by increasing the frequency. (<b>b</b>) The average flow rates and the corresponding electrical power consumption with the driving frequency of the pump for three operating voltages from the data of <a href="#sensors-23-06967-f005" class="html-fig">Figure 5</a>a are plotted. The error bars represent the standard deviation from the average flow rate. Low ripple factor flow rates can also be obtained by increasing the frequency of the micropump, but electrical power consumption increases exponentially above 300 Hz for 100 V of driving amplitude. Note that frequency (<span class="html-italic">x</span>-axis) is shown on a logarithmic scale.</p>
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<p>The influence of rectification on ripple reduction from one-phase to three-phases at a lower frequency range (0.25 to 10 Hz) is shown. The measurement durations are 20 s for each frequency. A one-phase rectifier uses one chamber of the mp6 pump, the two-phase rectifier uses a single chamber from two mp6 pumps connected in parallel, and similarly, a three-phase rectifier uses three mp6 pumps. Note that the flow rate also increases with the rectification level, as predicted and shown in <a href="#sensors-23-06967-f003" class="html-fig">Figure 3</a>.</p>
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<p>The fluidic ripple factors and ripple factor improvement with increasing phase rectification are calculated from the data in <a href="#sensors-23-06967-f006" class="html-fig">Figure 6</a> and were analyzed. (<b>a</b>) Fluidic ripple factors of one-, two-, three-, and four-phase rectifiers, respectively, are shown. (<b>b</b>) The percentage improvement of the fluidic ripple factors (<math display="inline"><semantics><mrow><mi>R</mi><msub><mi>F</mi><mrow><mi>f</mi><mi>l</mi></mrow></msub></mrow></semantics></math><sub>.</sub>) of the two-phase and three-phase rectifiers compared to the one-phase rectifier is shown. Three-phase rectification has the lowest ripples and an average improvement of 90.5% when compared to one-phase rectification in the frequency range 0.25–10 Hz.</p>
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<p>Comparison of the theoretical fluidic ripple factor and experimental average fluidic ripple factor measurements for up to a three-phase rectifier, with configurations of 100 V and 0.25 Hz. The error bars are the standard deviation obtained from five repeated experiments. It should be noted that the theoretical model does not include parameters, such as fluidic resistance, fluidic capacitance, pump membrane compliance, piezo hysteresis, and valve behavior, in the pump.</p>
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<p>The average flow rate with back pressure for one-phase, two-phase, and three-phase rectifier mechanisms with micropump(s) actuated at 100 V and 1 Hz operating conditions. The dotted line indicates that for a given average flow rate, the three-phase rectifier can withstand higher back pressure (P<sub>3</sub>) compared to two-phase (P<sub>2</sub>) and one-phase (P<sub>1</sub>) rectifiers. The values of P<sub>1</sub> and P<sub>2</sub> are lower than P<sub>3</sub> and are close together because there is no phase overlap for one-phase or two-phase rectifiers, whereas, for three-phase rectifiers, there is either a phase overlap indicating a back-pressure load distribution between pumps or a higher piezo stroke (see <a href="#sensors-23-06967-t001" class="html-table">Table 1</a>).</p>
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<p>The effect of the micro-metering valve for different rectifiers at very low flow rates. (<b>a</b>) A comparison of flow rate ripples for one-phase, two-phase, and three-phase rectifiers at low flow rates. (<b>b</b>) The fluidic ripple factor values of one-, two-, and three-phase rectifiers compared to the one-phase rectifier.</p>
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<p>A circuit representation of a micropump. (<b>a</b>) A fluidic circuit representation of a single micropump with a pumping chamber and two check valves on either side. (<b>b</b>) An electrical circuit equivalent representation of the micropump, with all capacitances and inductances neglected.</p>
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<p>The complete experimental setup used for testing the single- and multi-phase rectifications. The microfluidic setup consists of an inlet reservoir, micropumps, a flow restrictor, a flow sensor (connected to a monitor), a microfluidic chip, and a waste reservoir. The electrical setup consists of power sources, amplifiers, RC circuits, a microcontroller, a function generator, and oscilloscopes. A function generator was used to generate a wide range of frequencies for one-phase rectification. The Arduino microcontroller was used for the low-frequency tests for single- and multi-phase rectification. The computer was used to generate sine waves in Arduino software and adjust the frequency. A scissor jack and stage were used in the back-pressure experiments. A flow restrictor was used to check the performance of multi-phase rectification at very low flow rates.</p>
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<p>Average flow rate (depending on back pressure) graph for the three rectifier mechanisms with varying frequencies. By increasing the frequency, the capacity of the rectifiers to resist back pressure increased.</p>
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14 pages, 4302 KiB  
Article
Thermal Performance Optimization of Integrated Microchannel Cooling Plate for IGBT Power Module
by Hanyang Xu, Jiabo Huang, Wenchao Tian and Zhao Li
Micromachines 2023, 14(8), 1498; https://doi.org/10.3390/mi14081498 - 26 Jul 2023
Cited by 1 | Viewed by 1798
Abstract
In high-integration electronic components, the insulated-gate bipolar transistor (IGBT) power module has a high working temperature, which requires reasonable thermal analysis and a cooling process to improve the reliability of the IGBT module. This paper presents an investigation into the heat dissipation of [...] Read more.
In high-integration electronic components, the insulated-gate bipolar transistor (IGBT) power module has a high working temperature, which requires reasonable thermal analysis and a cooling process to improve the reliability of the IGBT module. This paper presents an investigation into the heat dissipation of the integrated microchannel cooling plate in the silicon carbide IGBT power module and reports the impact of the BL series micropump on the efficiency of the cooling plate. The IGBT power module was first simplified as an equivalent-mass block with a mass of 62.64 g, a volume of 15.27 cm3, a density of 4.10 g/cm3, and a specific heat capacity of 512.53 J/(kg·K), through an equivalent method. Then, the thermal performance of the microchannel cooling plate with a main channel and a secondary channel was analyzed and the design of experiment (DOE) method was used to provide three factors and three levels of orthogonal simulation experiments. The three factors included microchannel width, number of secondary inlets, and inlet diameter. The results show that the microchannel cooling plate significantly reduces the temperature of IGBT chips and, as the microchannel width, number of secondary inlets, and inlet diameter increase, the junction temperature of chips gradually decreases. The optimal structure of the cooling plate is a microchannel width of 0.58 mm, 13 secondary inlets, and an inlet diameter of 3.8 mm, and the chip-junction temperature of this structure is decreased from 677 °C to 77.7 °C. In addition, the BL series micropump was connected to the inlet of the cooling plate and the thermal performance of the microchannel cooling plate with a micropump was analyzed. The micropump increases the frictional resistance of fluid flow, resulting in an increase in chip-junction temperature to 110 °C. This work demonstrates the impact of micropumps on the heat dissipation of cooling plates and provides a foundation for the design of cooling plates for IGBT power modules. Full article
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<p>Schematic diagram of IGBT power module.</p>
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<p>Schematic diagram of temperature-field simulation results for IGBT power module; (<b>a</b>) is the temperature distribution results of the original module and (<b>b</b>) is the temperature distribution results of the equivalent module.</p>
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<p>Schematic diagram of the three-dimensional structure of the cooling plate.</p>
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<p>Schematic diagram of IGBT power module and cooling plate structure.</p>
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<p>Fluid schematic diagram of the cooling plate; (<b>a</b>) is the cloud chart of fluid velocity distribution and (<b>b</b>) is the cloud chart of fluid pressure distribution.</p>
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<p>Schematic diagram of the temperature results; (<b>a</b>) is the cloud chart of fluid temperature distribution and (<b>b</b>) is the cloud chart of chips temperature distribution.</p>
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<p>Schematic diagram of the relationship between three factors and chip-junction temperature; (<b>a</b>) is the width of the microchannel, (<b>b</b>) is the number of secondary inlets, and (<b>c</b>) is the diameter of the inlet.</p>
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<p>Fluid schematic diagram of the theoretical optimum model; (<b>a</b>) is the cloud chart of fluid velocity distribution and (<b>b</b>) is the cloud chart of fluid pressure distribution.</p>
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<p>Temperature schematic diagram of the theoretical optimum model; (<b>a</b>) is the cloud chart of fluid temperature distribution, (<b>b</b>) is the cloud chart of chip temperature distribution.</p>
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<p>The IGBT power module cooling plate with micropumps; (<b>a</b>) is the schematic diagram of the BL series micropump and (<b>b</b>) is the installation diagram of cooling plates and micropump.</p>
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<p>Fluid schematic diagram of the cooling plate model with a micropump; (<b>a</b>) is the cloud chart of velocity distribution and (<b>b</b>) is the cloud chart of fluid pressure distribution.</p>
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<p>Temperature schematic diagram of the cooling plate model with micropump; (<b>a</b>) is the cloud chart of fluid temperature distribution and (<b>b</b>) is the cloud chart of chip temperature distribution.</p>
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11 pages, 2390 KiB  
Article
A Miniaturized Archimedean Screw Pump for High-Viscosity Fluid Pumping in Microfluidics
by Sinan Gucluer
Micromachines 2023, 14(7), 1409; https://doi.org/10.3390/mi14071409 - 12 Jul 2023
Cited by 1 | Viewed by 1784
Abstract
Microfluidic devices have revolutionized the field of lab-on-a-chip by enabling precise manipulation of small fluid volumes for various biomedical applications. However, most existing microfluidic pumps struggle to handle high-viscosity fluids, limiting their applicability in certain areas that involve bioanalysis and on-chip sample processing. [...] Read more.
Microfluidic devices have revolutionized the field of lab-on-a-chip by enabling precise manipulation of small fluid volumes for various biomedical applications. However, most existing microfluidic pumps struggle to handle high-viscosity fluids, limiting their applicability in certain areas that involve bioanalysis and on-chip sample processing. In this paper, the design and fabrication of a miniaturized Archimedean screw pump for pumping high-viscosity fluids within microfluidic channels are presented. The pump was 3D-printed and operated vertically, allowing for continuous and directional fluid pumping. The pump’s capabilities were demonstrated by successfully pumping polyethylene glycol (PEG) solutions that are over 100 times more viscous than water using a basic mini-DC motor. Efficient fluid manipulation at low voltages was achieved by the pump, making it suitable for point-of-care and field applications. The flow rates of water were characterized, and the effect of different screw pitch lengths on the flow rate was investigated. Additionally, the pump’s capacity for pumping high-viscosity fluids was demonstrated by testing it with PEG solutions of increasing viscosity. The microfluidic pump’s simple fabrication and easy operation position it as a promising candidate for lab-on-a-chip applications involving high-viscosity fluids. Full article
(This article belongs to the Collection Lab-on-a-Chip)
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<p>The screw pump: (<b>a</b>) schematic representation; (<b>b</b>) actual picture of the screw pump.</p>
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<p>Detailed dimensions of the screw pump assembly.</p>
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<p>Dimensions and geometry of the screw: (<b>a</b>) schematic drawing of the screw; (<b>b</b>) washer dimensions; (<b>c</b>) actual picture of a screw with a pitch of 4 mm.</p>
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<p>(<b>a</b>–<b>c</b>) The water–particle mixture is shown to be directionally manipulated at a 0.5 V applied voltage. The red arrow tracks a large particle indicating the flow direction.</p>
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<p>Measured flow rates for water as a function of the applied voltage. Error bars represent the standard deviation of 20 measurements for each voltage value.</p>
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<p>Flow rate characterization for water as a function of the pitch length of the screw at 0.5 V. Error bars represent the standard deviation of 20 measurements for each pitch length.</p>
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<p>Pumping performance evaluation as a function of the viscosity at 3 V. PEG 700 and dilutions thereof were used as the fluids. Error bars represent the standard deviation of 20 measurements for each fluid.</p>
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14 pages, 5756 KiB  
Article
Design and Experiments of Electro-Hydrostatic Actuator for Wheel-Legged Robot with Fast Force Control Response
by Huipeng Zhao, Junjie Zhou, Sanxi Ma, Shanxiao Du, Hui Liu and Lijin Han
Machines 2023, 11(7), 685; https://doi.org/10.3390/machines11070685 - 29 Jun 2023
Cited by 6 | Viewed by 1847
Abstract
The wheel-legged robot combines the functions of wheeled vehicles and legged robots: high speed and high passability. However, the limited performance of existing joint actuators has always been the bottleneck in the actual applications of large wheel-legged robots. This paper proposed a highly [...] Read more.
The wheel-legged robot combines the functions of wheeled vehicles and legged robots: high speed and high passability. However, the limited performance of existing joint actuators has always been the bottleneck in the actual applications of large wheel-legged robots. This paper proposed a highly integrated electro-hydrostatic actuator (EHA) to enable high-dynamic performance in giant wheel-legged robots (>200 kg). A prototype with a high force-to-weight ratio was developed by integrating a micropump, a miniature spring accumulator, and a micro-symmetrical cylinder. The prototype achieves a large output force of more than 9400 N and a high force-to-weight ratio of more than 2518 N/kg. Compared with existing EHA-based robots, it has a higher force-to-weight ratio and can bear larger loads. A detailed EHA model was presented, and controllers were designed based on sliding mode control and PID methods to control the output position and force of the piston. The model’s accuracy is improved by identifying uncertain parameters such as friction and leakage coefficient. Finally, both simulations and experiments were carried out. The results verified the fast response of force control (step response within 50 ms, the force tracking control frequency about 6.7 Hz) and the developed EHA’s good potential for future large wheel-legged robots. Full article
(This article belongs to the Special Issue Advanced Control of Electro-Hydraulic Systems in Industrial Area)
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<p>Principle of EHA System.</p>
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<p>The structure joint with EHA.</p>
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<p>Mechanical structure of EHA.</p>
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<p>Control block diagram of pressure controller.</p>
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<p>Control block diagram of position controller.</p>
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<p>EHA prototype.</p>
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<p>Test bench.</p>
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<p>Experiment and identification results.</p>
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<p>Experimental and simulated step response of the pressure control system.(<b>a</b>) Step response of pressure 15 MPa; (<b>b</b>) motor current response with pressure 15 MPa; (<b>c</b>) step response of pressure 20 MPa; (<b>d</b>) motor current response with pressure 20 MPa; (<b>e</b>) step response of pressure 30 MPa; (<b>f</b>) motor current response with pressure 30 MPa.</p>
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<p>Experimental and simulated sinusoidal response of the pressure control system. (<b>a</b>) Sinusoidal response of pressure amplitude 20 MPa and frequency 6.7 Hz; (<b>b</b>) motor current response with pressure amplitude 20 MPa and frequency 6.7 Hz; (<b>c</b>) sinusoidal response of pressure amplitude 30 MPa and frequency 6.7 Hz; (<b>d</b>) motor current response with pressure amplitude 30 MPa and frequency 6.7 Hz.</p>
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<p>Experimental and simulated response of the position control system. (<b>a</b>) Step response of angular displacement from 50° to 120°; (<b>b</b>) motor speed response with angular displacement from 50° to 120°; (<b>c</b>) sinusoidal response of angular displacement from 50° to 120° and frequency 1 Hz; (<b>d</b>) motor speed response with angular displacement from 50° to 120° and frequency 1 Hz.</p>
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17 pages, 6409 KiB  
Article
Multistage Micropump System towards Vacuum Pressure
by Martin Richter, Daniel Anheuer, Axel Wille, Yuecel Congar and Martin Wackerle
Actuators 2023, 12(6), 227; https://doi.org/10.3390/act12060227 - 31 May 2023
Viewed by 1957
Abstract
Fraunhofer EMFT’s research and manufacturing portfolio includes piezoelectrically actuated silicon micro diaphragm pumps with passive flap valves. Research and development in the field of microfluidics have been dedicated for many years to the use of micropumps for generating positive and negative pressures, as [...] Read more.
Fraunhofer EMFT’s research and manufacturing portfolio includes piezoelectrically actuated silicon micro diaphragm pumps with passive flap valves. Research and development in the field of microfluidics have been dedicated for many years to the use of micropumps for generating positive and negative pressures, as well as delivering various media. However, for some applications, only small amounts of fluid need to be pumped, compressed, or evacuated, and until now, only macroscopic pumps with high power consumption have been able to achieve the necessary flow rate and pressure, especially for compressible media such as air. To address these requirements, one potential approach is to use a multistage of high-performing micropumps optimized to negative pressure. In this paper, we present several possible ways to cascade piezoelectric silicon micropumps with passive flap valves to achieve these stringent requirements. Initially, simulations are conducted to generate negative pressures with different cascading methods. The first multistage option assumes pressure equalization over the piezo-actuator by the upstream pump, while for the second case, the actuator diaphragm operates against atmospheric pressure. Subsequently, measurement results for the generation of negative gas pressures down to −82.1 kPa relative to atmospheric pressure (19.2 kPa absolute) with a multistage of three micropumps are presented. This research enables further miniaturization of many applications with high-performance requirements for micropumps, achievable with these multistage systems. Full article
(This article belongs to the Special Issue Cooperative Microactuator Devices and Systems)
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<p>Schematic cross section of micropumps with reduced dead volume <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>V</mi> </mrow> <mrow> <mn>0</mn> </mrow> </msub> </mrow> </semantics></math> due to an electric pretension of the piezo during the gluing process. The dead volume <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>V</mi> </mrow> <mrow> <mn>0</mn> </mrow> </msub> </mrow> </semantics></math> (green) is defined as that volume, which remains in the pump chamber, if the actuator is in its lowest position.</p>
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<p>Top and bottom view of the <math display="inline"><semantics> <mrow> <mn>7</mn> <mo>×</mo> <mn>7</mn> <mo>×</mo> <mn>0.7</mn> <mo> </mo> <msup> <mrow> <mi mathvariant="normal">m</mi> <mi mathvariant="normal">m</mi> </mrow> <mn>3</mn> </msup> </mrow> </semantics></math> silicon micropump chip with mounted PZT and visible inlet and outlet ports.</p>
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<p>Cross section of the micropump with pretensed diaphragm explaining relevant design parameters. <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>h</mi> </mrow> <mrow> <mi>p</mi> <mi>k</mi> </mrow> </msub> </mrow> </semantics></math> is the pump chamber height, <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>T</mi> </mrow> <mrow> <mi>d</mi> </mrow> </msub> </mrow> </semantics></math> is the diaphragm thickness, <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>T</mi> </mrow> <mrow> <mi>p</mi> </mrow> </msub> </mrow> </semantics></math> is the piezo actuator thickness, <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>R</mi> </mrow> <mrow> <mi>p</mi> </mrow> </msub> </mrow> </semantics></math> is the piezo actuator radius, and <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>R</mi> </mrow> <mrow> <mi>d</mi> </mrow> </msub> </mrow> </semantics></math> is the diaphragm radius.</p>
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<p>SEM image of silicon valve sealing lip (width <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>b</mi> </mrow> <mrow> <mi>s</mi> <mi>e</mi> <mi>a</mi> <mi>t</mi> </mrow> </msub> <mo>=</mo> <mn>3</mn> <mo> </mo> <mi>µ</mi> <mi mathvariant="normal">m</mi> </mrow> </semantics></math>) to reduce surface contact area with the silicon flap in order to reduce sticking. In the right bottom corner, there is the opening. At the edge of the valve seat the compensation structures to protect convex corners during KOH etching are shown.</p>
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<p>p-V diagram of the pump cycle of a micropump operating at atmosphere pressure <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>p</mi> </mrow> <mrow> <mn>0</mn> </mrow> </msub> </mrow> </semantics></math> pumping gas.</p>
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<p>Different methods of cascading micropumps with 3 stages each to achieve vacuum pressure in the blue framed chamber compared to atmosphere pressure <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>p</mi> </mrow> <mrow> <mn>0</mn> </mrow> </msub> </mrow> </semantics></math>. In the just serial connected case (case 1), the actuators of every stage are working against atmospheric pressure. Pressure balanced outlet (case 2a) shows a housing on top of the actuator connected to the micropump outlet to a achieve a pressure balance between outlet and actuator. In the pressure balanced inlet (case 2b), the housing is connected to the micropump inlet of each stage.</p>
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<p>Pump cycles of 3 consecutive stages for serial connection of micropumps, just serial connected without pressure compensation.</p>
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<p>Pressure-balanced configuration of a multistage of three micropumps to achieve negative pressure.</p>
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<p>Simulation result of a multistage with three pressure balanced silicon micropumps. All micropumps are identical in design, and have the same stroke volume and dead volume.</p>
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<p>Micropump module in stackable housing with silicone sealing (<b>right</b>) and stack of three cascaded micropump modules including connectors to pressure sensors (<b>left</b>).</p>
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<p>Different setups used in this study for single-pump tests of micropumps A12, B22, and D32 and multistage tests with two and three micropumps.</p>
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<p>Static actuator stroke of the selected three micropumps (A12, B22, D32). Actuator dimensions are depicted in <a href="#actuators-12-00227-t001" class="html-table">Table 1</a>. (PZT from PI Ceramics, type PI 151).</p>
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<p>Measurement results of <math display="inline"><semantics> <mrow> <msub> <mrow> <mi>p</mi> </mrow> <mrow> <mrow> <mrow> <mi mathvariant="italic">min</mi> <mo>,</mo> </mrow> <mrow> <mi>g</mi> <mi>a</mi> <mi>s</mi> </mrow> </mrow> </mrow> </msub> </mrow> </semantics></math> from the selected three micropumps (A12, B22, D32).</p>
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<p>Time- and pressure-dependent cascaded micropumps. Two cascaded micropumps (B22, D32) achieve an absolute pressure of <math display="inline"><semantics> <mrow> <mn>28.3</mn> <mo> </mo> <mi mathvariant="normal">k</mi> <mi mathvariant="normal">P</mi> <mi mathvariant="normal">a</mi> </mrow> </semantics></math>.</p>
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<p>Minimum air inlet pressure measurement result in dependence of time with a multistage of three micropumps. D32 in stage 1, B22 in stage 2, and A12 for stage 3 achieved an absolute pressure of <math display="inline"><semantics> <mrow> <mn>19.2</mn> <mo> </mo> <mi mathvariant="normal">k</mi> <mi mathvariant="normal">P</mi> <mi mathvariant="normal">a</mi> </mrow> </semantics></math> in approximately <math display="inline"><semantics> <mrow> <mn>200</mn> <mo> </mo> <mi mathvariant="normal">s</mi> </mrow> </semantics></math>.</p>
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17 pages, 3750 KiB  
Article
A Smart Active Phase-Change Micropump Based on CMOS-MEMS Technology
by Wenzui Jin, Yimin Guan, Qiushi Wang, Peng Huang, Qin Zhou, Kun Wang and Demeng Liu
Sensors 2023, 23(11), 5207; https://doi.org/10.3390/s23115207 - 30 May 2023
Viewed by 1308
Abstract
The rational integration of many microfluidic chips and micropumps remains challenging. Due to the integration of the control system and sensors in active micropumps, they have unique advantages over passive micropumps when integrated into microfluidic chips. An active phase-change micropump based on complementary [...] Read more.
The rational integration of many microfluidic chips and micropumps remains challenging. Due to the integration of the control system and sensors in active micropumps, they have unique advantages over passive micropumps when integrated into microfluidic chips. An active phase-change micropump based on complementary metal–oxide–semiconductor–microelectromechanical system (CMOS-MEMS) technology was fabricated and studied theoretically and experimentally. The micropump structure is simple and consists of a microchannel, a series of heater elements along the microchannel, an on-chip control system, and sensors. A simplified model was established to analyze the pumping effect of the traveling phase transition in the microchannel. The relationship between pumping conditions and flow rate was examined. Based on the experimental results, the maximum flow rate of the active phase-change micropump at room temperature is 22 µL/min, and long-term stable operation can be achieved by optimizing heating conditions. Full article
(This article belongs to the Section Sensing and Imaging)
Show Figures

Figure 1

Figure 1
<p>Illustration of the pumping mechanism.</p>
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<p>Pressure distribution in flow through a microchannel.</p>
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<p>(<b>a</b>) Control logic sequence diagram and (<b>b</b>) the driving circuit of a single heater.</p>
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<p>Topology of temperature sensors.</p>
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<p>(<b>a</b>) Optical photo of the micropump (scale bar: 1 mm); (<b>b</b>) an amplified photo of the microchannel (scale bar: 100 µm); and (<b>c</b>) an amplified photo of the heater (scale bar: 20 µm).</p>
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<p>Fabrication of the micropump: (<b>a</b>) a chip fabricated using CMOS processing; (<b>b</b>) a chip with the first layer of dry film attached; (<b>c</b>) chip after exposure; (<b>d</b>) Chip after deep reactive ion etching; (<b>e</b>) a chip with the second layer of dry film attached.</p>
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<p>Experimental apparatus.</p>
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<p>Micropump control signal timing.</p>
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<p>Bubble nucleation simulation: (<b>a</b>) the driving waveform imposed on the heater and (<b>b</b>) the temperature of the heater surface.</p>
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<p>Bubble nucleation simulation: (<b>a</b>) the driving waveform imposed on the heater and (<b>b</b>) the temperature of the heater surface.</p>
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<p>(<b>a</b>) The effects of printing frequency on the average flow rate and (<b>b</b>) the relationship between printing frequency and temperature.</p>
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<p>(<b>a</b>) Bubbles at the inlet (scale bar: 0.1 mm); (<b>b</b>) bubbles in the microchannel (scale bar: 43 µm); and (<b>c</b>) bubbles at the outlet (scale bar: 0.1 mm).</p>
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<p>Thermal effect simulation: (<b>a</b>) the driving waveform imposed on the heater and (<b>b</b>) the temperature of the silicon.</p>
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<p>(<b>a</b>) The effects of TH on average flow rate; (<b>b</b>) the relationship between TH and temperature; (<b>c</b>) the effects of TD on average flow rate; and (<b>d</b>) the relationship between TD and temperature.</p>
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<p>(<b>a</b>) Variation in flow rate over time and (<b>b</b>) variation in temperature over time.</p>
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<p>(<b>a</b>) Variation in flow rate over time and (<b>b</b>) variation in temperature over time.</p>
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