磁控微流控芯片的研究现状及应用

微流控芯片作为一种现代分析方法,近年来得到迅速发展。而磁控微流控芯片是在微流控芯片中引入磁场调控,通过引入磁场丰富了微流控芯片的操控手段,同时结合了磁性材料的优势,使之成为微流控芯片研究的重要组成部分之一。本文重点介绍磁控微流控芯片的研究现状及应用。     

微流控芯片电泳的研究进展

该文综述了微流控芯片电泳的制备、结构和应用,比较了不同材料微流控芯片电泳的制备机理、表面改性和性能特点,归纳和总结了不同结构微流控芯片电泳的进样、分离和检测系统以及不同类型微流控芯片电泳在荧光物质、金属离子、糖、药物、核酸、DNA、氨基酸、多肽和蛋白质分析中的应用,并对微流控芯片电泳的未来发展方向做了展望.     

微流控系统在生化分析领域的新应用

微流控芯片是近年来新兴的研究领域,它由微米级别的微通道及辅助器件构成,并且有着低试剂消耗量、响应时间短、高精度、高灵敏度、高集成度和独特的微观物理现象等特性。微流控芯片的独特优势为生物样品的处理与分析、生物模拟、药物传递和多组分分析等领域提供了前所未有的机会。为获得理想、完善的微流控平台,还需进一步挖掘微流控芯片的潜在应用。本文回顾了微流控芯片在生化分析领域中的新应用,分析了其优劣势与存在的挑战,并预测了微流控芯片未来可能的发展趋势,指出了微流控芯片"走出实验室"投入实际应用的可能。     

微流控芯片上的免疫分析

近20年来,随着微流控芯片加工技术的不断发展,微流控分析已从一个概念发展为当前世界上最前沿的科技领域之一,微流控芯片上免疫分析的方法研究也取得重要进展。这些芯片包含传输流体的微通道和免疫分析程序中部分或全部的必要组件。微流控技术用于免疫分析在减少试剂用量、缩短分析时间、自动化等方面提高了分析性能。本文综述了微流控芯片上免疫分析的发展、分类,并评述了各类微流控免疫分析芯片的性能及优缺点。     

基于流体动力单细胞高效捕获的微流控芯片结构研究进展

单细胞分析对于重大疾病的早期诊断及治疗、药物筛选和生理病理过程的研究具有重要意义。微流控芯片能够精确控制单细胞的微环境,实时监测单细胞的行为,已成为单细胞分析的强大工具。单细胞捕获是单细胞分析的重要步骤。目前已报道了多种微流控芯片用于单细胞捕获的方法,其中基于流体动力的微流控芯片单细胞捕获方法具有操作方便、单细胞捕获效率高等优点,受到研究人员的广泛关注及使用。为了全面了解基于流体动力的微流控芯片单细胞捕获方法的研究现状,掌握单细胞高效捕获的微流控芯片结构设计,实现单细胞精准快速分析,本文综述了基于流体动力的单细胞高效捕获（>70%）原理及微流控芯片结构,根据结构设计不同分为微井结构、微柱结构和旁路通道结构,介绍了单细胞高效捕获的微流控芯片优化过程,总结了微流控芯片的材质、结构特点及单细胞捕获效率等,对不同单细胞捕获结构的优势及不足进行了分析。最后,对基于流体动力的微流控芯片单细胞捕获方法的发展趋势进行了展望。     

微流控芯片检测技术进展

介绍了目前微流控芯片应用的3种主要检测手段:质谱检测器、电化学检测器和光学检测器。微流控芯片是微全分析系统(μ-TAS)中最活跃的领域和发展前沿。人们在微流控芯片的研究中已经取得了很大的进展,研制出了多种微型化、集成化的芯片,而与微流控芯片配套的高灵敏度微型检测系统更是研制的热点。     

一种微流控芯片中大体积进样方法及专用芯片

本发明涉及微流控芯片系统的进样方法。在使用固定相的微流控芯片系统中,于芯片分离通道与流动相人口之间设置两个或两个以上的分流通道。通过控制其中流体的切换和截止,实现对微流控芯片系统的大体积进样。该方法适合于微流控芯片中电色谱、加压电色谱和液相色谱模式下的大体积进样。该方法的优点为：可实现微流控芯片中大体积样品的上样;克服了系统中的梯度延迟效应,     

微流控芯片电泳技术在临床检测中的新进展

微流控芯片电泳技术作为一种消耗少、速度快、效率高的分析技术,可同时实现便携化、集成化、高通量,在临床检测中发挥着重要作用。该文综述了近年来微流控芯片电泳技术在临床应用方面的研究进展,主要包括微流控芯片电泳技术在小分子、氨基酸、蛋白质、核酸、细胞等方面的应用近况。同时,介绍了一种崭露头角的基于大管电泳技术的大通道电泳微流控芯片技术,最后对微流控芯片电泳技术实现临床分析进行了展望。     

3D打印微流控芯片技术研究进展

近年来,微流控技术在生命科学和医学诊断等领域得到广泛的应用,显示出了其在检测速度、精度以及试剂损耗等方面相比传统方法的显著优势.然而,使用从半导体加工技术继承而来的微加工技术制作微流控芯片具有比较高的资金和技术门槛,在一定程度上阻碍了微流控技术的推广和应用.近年来随着3D打印技术的兴起,越来越多的研究者尝试使用3D打印技术加工微流控芯片.相比于传统的微加工技术,3D打印微流控芯片技术显示出了其设计加工快速、材料适应性广、成本低廉等优势.本文针对近年来国内外在3D打印微流控芯片领域的最新进展进行了综述,着重介绍了采用微立体光刻、熔融沉积成型以及喷墨打印等3D打印技术加工制作微流控芯片的方法,以及这些微流控芯片在分析化学、生命科学、医学诊断等领域的应用,并对3D打印微流控芯片技术未来的发展进行了展望.     

基于微流控芯片电泳的生物分子间相互作用研究*

用合适的手段表征生物分子的相互作用对于深刻理解生命过程的本质以及进行医药开发都具有重要意义。将微流控芯片和毛细管电泳相结合的微流控芯片电泳技术具有快速、高效、高通量、样品用量少和易于整合等诸多优势。本文对近年来进行生物分子间相互作用结合常数测定以及结合动力学研究的微流控芯片电泳分离模式、分析方法和芯片检测方法分别做了介绍;简单对比了微流控芯片技术和微阵列生物芯片生物分子间相互作用研究技术;最后分析了微流控芯片技术目前的不足,并对其未来的发展进行了展望。     

Open-access and multi-directional electroosmotic flow chip for positioning heterotypic cells

We propose a novel method of cell positioning using electroosmotic flow (EOF) to analyze cell-cell interactions. The EOF chip has an open-to-air configuration, is equipped with four electrodes to induce multi-directional EOF, and allows access of tools for liquid handling and of physical probes for cell measurements. Evaluation of the flow within this chip indicated that it controlled hydrodynamic transport of cells, in terms of both speed and direction. We also evaluated cell viability after EOF application and determined appropriate conditions for cell positioning. Two cells were successively positioned in pocket-like microstructures, one in each micropocket, by controlling the EOF direction. As an experimental demonstration, we observed contact interactions between two individual cells through gap junction channels. The EOF chip should provide ways to elucidate various cell-cell interactions between heterotypic cells.     

Chitosan microfiber fabrication using microfluidic chips of different sheath channel angles and its application on cell culture

In this study, we successfully produced the chitosan microfibers using the proposed various angles of microfluidic chip, which was also been simulated. By controlling the core and sheath flow rates, we were able to generate laminar flow of different diameters from 15 μm to 40 μm. And the diameter of chitosan microfiber was measured from 20 μm to 50 μm. The microchannel of angle 30° could produce chitosan laminar flow of a smaller diameter than the angle 60° and angle 45° at the fixed flow rates. Finally, the chitosan microfiber was chosen as scaffold and the schwann cell and fibroblast cell with chitosan microfibers were used for cell culture to test effect in tissue engineering application.     

Microfluidic pool structure for cell docking and rapid mixing

A microfluidic pool structure for cell docking and rapid mixing is described. The pool structure is defined as a microchamber on one structural layer of a bilayer chip and connects with two or more individual microchannels on the other structural layer. In contrast to the turbulent flow in a macroscale pool, laminar streams enter and exit this microfluidic pool structure with definite and controllable direction that may be influenced by the location and geometry of the pool. A simple microfluidic model was used to validate this hypothesis. In this model, a microscale pool structure was made on the lower layer of a chip and connected with three parallel microchannels in the upper layer. Simulation and experimental results indicated that the flow profile within the pool structure was determined by its geometry and location. This could be used as a flow control method and it was simpler than designs based on microvalve, hydraulic pressure, or electrokinetic force, and has some important applications. For example, controllable streams within this structure were used to immobilize biological cells along the microchannel walls. When different solution streams flowed through the pool, rapid diffusion of analytes occurred for short diffusion distance between vertical flow laminas. Furthermore, desired dilution (mixing) ratio could be obtained by controlling the geometry of the microfluidic pool.     

A fluorogenic assay using pressure-driven flow on a microchip.

A fluorogenic assay for human T-cell phosphatase (TCPTP) was conducted on an etched glass microchip using pressure driven flow. The TCPTP enzyme catalyzes the removal of a phosphate group from 6,8-difluoro-4-methylumbelliferyl/phosphate (DiFMUP) to produce the fluorogenic product 6,8-difluoro-4-methylumbelliferone (DiFMU). Enzyme assays with real-time on-chip dilution were performed in both low-viscosity (1 cP) buffer and an enzyme solution containing 50% glycerol (6 cP). Single side channels connect a series of reagent wells to a main channel where the fluorescent product of the enzyme reaction passes the detector region. Flow regulation of mixed viscosity fluids requires a pressure control on each arm of the chip contributing to the overall flow. An 8-channel pressure controller was built to regulate the air pressure above all wells feeding channels of the chip, thereby controlling the dilution ratios of buffer, substrate and enzyme. Well pressures maintained a constant concentration of enzyme in the detector channel while adjusting the flow contribution of substrate and buffer. The substrate concentration was stepped over two orders of magnitude while verifying fluid dilutions using marker dyes. The kinetic parameters, Km, Vmax, and Kcat, showed good agreement with the values determined using a standard well plate and fluorometer.     

Multistage Microfluidic Platform for the Continuous Synthesis of III–V Core/Shell Quantum Dots

We present a fully continuous chip microreactor‐based multistage platform for the synthesis of quantum dots with heterostructures. The use of custom‐designed chip reactors enables precise control of heating profiles and flow distribution across the microfluidic channels while conducting multistep reactions. The platform can be easily reconfigured by reconnecting the differently designed chip reactors allowing for screening of various reaction parameters during the synthesis of nanocrystals. III–V core/shell quantum dots are chosen as model reaction systems, including InP/ZnS, InP/ZnSe, InP/CdS and InAs/InP, which are prepared in flow using a maximum of six chip reactors in series.     

Microfluidic chip accomplishing self-fluid replacement using only capillary force and its bioanalytical application

A polymer microfluidic chip accomplishing automated sample flow and replacement without external controls and an application of the chip for bioanalytical reaction were described. All the fluidic operations in the chip were achieved by only natural capillary flow in a time-planned sequence. For the control of the capillary flow, the geometry of the channels and chambers in the chip was designed based on theoretical considerations and numerical simulations. The microfluidic chip was made by using polymer replication techniques, which were suitable for fast and cheap fabrication. The test for a biochemical analysis, employing an enzyme (HRP)-catalyzed precipitation reaction, exhibited a good performance using the developed chip. The presented microfluidic method would be applicable to biochemical lab-on-a-chips with integrated fluid replacement steps, such as affinity elution and solution exchange during biosensor signaling.     

The mechanism of the self-assembly of associating DNA molecules under shear flow: Brownian dynamics simulation

A shear flow induces the assembly of DNAs with the sticky spots. In order to strictly interpret the mechanism of shear-induced DNA assembly, Brownian dynamics simulations with the bead-spring model were carried out for these molecules at various ranges of the Weissenberg numbers (We). We calculate a formation time and analyze the radial distribution function of end beads and the probability distribution of fractional extension at the formation time to understand the mechanism of shear-induced assembly. At low Weissenberg number the formation time, which is defined as an elapsed time until a multimer forms for the first time, decreases rapidly, reaching a plateau at We = 1000. A shear flow changes the radial distribution of end beads, which is almost the same regardless of the Weissenberg number. A shear flow deforms and stretches the molecules and generates different distributions between end beads with a stickly spot. The fractional extension progresses rapidly in shear flow from a Gaussian-like distribution to a uniform distribution. The progress of the distribution of fractional extension increases the possibility of meeting of end beads. In shear flow, the inducement of the assembly mainly results from the progress of the probability distribution of fractional extension. We also calculate properties such as the radius of gyration, stretch, and so on. As the Weissenberg number increases, the radius of gyration at the formation time also increases rapidly, reaching a plateau at We = 1000.     

Analysis of shear-induced and extensional-induced associating polymer assemblies: Brownian dynamics simulation

In order to examine the difference between shear-induced and extensional-induced associating polymer assemblies at the molecular level, Brownian dynamics simulations with the bead-spring model were carried out for model DNA molecules with sticky spots. The radial distribution of molecules overestimates from that in the absence of flow and increases with increasing Weissenberg number in extensional flow, but slightly underestimates without regard to shear rate in shear flow. The fractional extension progresses more rapidly in extensional flow than in shear flow and the distribution of fractional extension at the formation time has a relatively sharper peak and narrower spectrum in extensional flow than in shear flow. In shear flow, the inducement of the assembly mainly results from the progress of the probability distribution of fractional extension. However, in extensional flow, the assembly is induced by both the progress of the probability distribution and increasing the values of the radial distribution.     

Controlling the magnetic field distribution on the micrometer scale and generation of magnetic bead patterns for microfluidic applications

As is well known, controlling the local magnetic field distribution on the micrometer scale in a microfluidic chip is significant and has many applications in bioanalysis based on magnetic beads. However, it is a challenge to tailor the magnetic field introduced by external permanent magnets or electromagnets on the micrometer scale. Here, we demonstrated a simple approach to controlling the local magnetic field distribution on the micrometer scale in a microfluidic chip by nickel patterns encapsulated in a thin poly(dimethylsiloxane) (PDMS) film under the fluid channel. With the precisely controlled magnetic field, magnetic bead patterns were convenient to generate. Moreover, two kinds of fluorescent magnetic beads were patterned in the microfluidic channel, which demonstrated that it was possible to generate different functional magnetic bead patterns in situ, and could be used for the detection of multiple targets. In addition, this method was applied to generate cancer cell patterns.     

Dynamics of heat transport in CNTs based Darcy saturated flow: Modeling through fractional simulations

Nanofluids have a vital role in many industries due to their novelty of heat transfer. Various mathematical techniques are required to simulate such problems. It can seem that traditional partial differential equations are incapable of analyzing and investigating the physical behavior of flow parameters affected by memory effects. This research communicates the implementation of the most interesting analytical method namely Prabhakar fractional derivative regarding the thermal flow of Casson fluid with single and multiwall carbon-nanotubes due to an inclined plate. The water and blood are considered as base particles. slip and Newtonian heating impacts for the thermal flow are also considered. The fractional modal of leading PDE's is attained by Prabhakar fractional derivative with various limiting cases. The generalized solution for the thermal and velocity field is simulated via the Laplace transformation method. The thermal expressions are modeled via Fourier expressions. Graphs are used to illustrate the influence and behaviour of key physical and fractional characteristics. The finding is that the temperature and velocity profiles of SWCNTs are more prominent than those of MWCNTs. Changing the fractional parameter values results in a greater rise in the velocity gradient for blood-based nanofluid than for water-based nanofluid.