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Review
. 2020 Jan 7;92(1):105-131.
doi: 10.1021/acs.analchem.9b05357. Epub 2019 Dec 20.

Cell Separations and Sorting

Malgorzata A Witek  1   2   3 , Ian M Freed  1   2 , Steven A Soper  1   2   4   5
Affiliations
Review

Cell Separations and Sorting

Malgorzata A Witek et al. Anal Chem. .
No abstract available

PubMed Disclaimer

Conflict of interest statement

Notes

The authors declare the following competing financial interest(s): S.A.S. holds equity shares in BioFluidica, Inc., a company that holds commercialization rights to CTC isolation technology presented herein. M.A.W. declares a conflict of interest as a spouse of a BioFluidica, Inc. employee. I.M.F. declares no conflict on interest.

Figures

Figure 1.
Figure 1.
Cell affinity-isolation methods. (A) Schematic of the dual-immunopatterned (DIP) device composed of an anti-EpCAM antibody-immobilized layer and an anti-63B6 antibody-immobilized layer. (a) Device concept and working mechanism and (b) structure of the device. Reprinted from Sens. Actuators, B, Vol. 260, Kang, Y.-T., Kim, Y. J., Bu, J., Chen, S., Cho, Y., Lee, Hyun M., Ryu, C. J., Lim, Y., Han, S.-W. Epithelial and mesenchymal circulating tumor cell isolation and discrimination using dual-immunopatterned device with newly developed anti-63B6 and anti-EpCAM, pp 320–330 (ref 37). Copyright 2018, with permission from Elsevier. (B, C) Design of a ligand decorated cell membrane mimetic surface for blood cell repellence and tumor cell capture. Reproduced from Li, T.; Li, N.; Ma, Y.; Bai, Y.-J.; Xing, C.-M.; Gong, Y.-K. J. Mater. Chem. B 2019, 7, 6087–6098 (ref 39), with permission of The Royal Society of Chemistry. (D) Capture strategy using Carpet Chip. Schematic of the CTC Carpet Chips connected in series. Rare CTCs were captured simultaneously from the peripheral blood of pancreatic cancer patients by using anti-EpCAM and anti-CD133 antibodies in two different chips. Reproduced from Profiling Heterogeneous Circulating Tumor Cells (CTC) Populations in Pancreatic Cancer Using a Serial Microfluidic CTC Carpet Chip, Zeinali, M.; Murlidhar, V.; Fouladdel, S.; Shao, S.; Zhao, L.; Cameron, H.; Bankhead, A., III; Shi, J.; Cuneo, K. C.; Sahai, V.; Azizi, E.; Wicha, M. S.; Hafner, M.; Simeone, D. M.; Nagrath, S., Adv. Biosyst., Vol. 2, Issue 12 (ref 41). Copyright 2018 Wiley. (E) CTC Carpet Chip optimization with cell lines showing: (a) capture efficiency of cell lines with various levels of EpCAM expression, (b) an image showing dual CTC Carpet Chip, (c) capture efficiency of cancer cells spiked into blood with or without antibodies in the dual chips, (d) SEM image of the chip with captured cancer cells, and (e) confocal image of a CK+ cancer cells. Reproduced from Profiling Heterogeneous Circulating Tumor Cells (CTC) Populations in Pancreatic Cancer Using a Serial Microfluidic CTC Carpet Chip, Zeinali, M.; Murlidhar, V.; Fouladdel, S.; Shao, S.; Zhao, L.; Cameron, H.; Bankhead, A., III; Shi, J.; Cuneo, K. C.; Sahai, V.; Azizi, E.; Wicha, M. S.; Hafner, M.; Simeone, D. M.; Nagrath, S., Adv. Biosyst., Vol. 2, Issue 12 (ref 41). Copyright 2018 Wiley. (F) Circulating Plasma Cells (CPC) selection device: (a) schematic of the CPC selection device, (b) SEM image of the sinusoidal channels fabricated in a thermoplastic, (c) image of DAPI stained affinity-selected RPMI-8226 cells, and (d) schematic of the CPCs selection process with anti-CD138 antibodies enzymatically cleaved following isolations thereby releasing intact cells. Reprinted from Isolation of Circulating Plasma Cells From Blood of Patients Diagnosed with Clonal Plasma Cell Disorders using Cell Selection Microfluidics, Integrative Biology, Vol. 10, Issue 2 (ref 42). Copyright 2018 Oxford University Press.
Figure 2.
Figure 2.
Acoustofluidic and acoustophoretic methods for cell sorting. (A) Sorting of PC3 cancer cells from WBCs. Following acoustic field activation, cancer cells are pushed toward the bottom collection outlet while the majority of the WBCs continue flowing to the waste outlet. Reproduced from Circulating Tumor Cell Phenotyping via High-Throughput Acoustic Separation, Wu, M.; Huang, P.-H.; Zhang, R.; Mao, Z.; Chen, C.; Kemeny, G.; Li, P.; Lee, A. V.; Gyanchandani, R.; Armstrong, A. J.; Dao, M.; Suresh, S.; Huang, T. J. Small, Vol. 14, Issue 32 (ref 51). Copyright 2018 Wiley. (B) 3D acoustofluidic tweezers (3D-AFT) sorting device. Particles are sorted to multiple outlets under the combined effects of acoustics and hydrodynamics. Reproduced from Wu, M.; Chen, K.; Yang, S.; Wang, Z.; Huang, P.-H.; Mai, J.; Li, Z.-Y.; Huang, T. J. Lab Chip 2018, 18, 3003–3010 (ref 52), with permission of The Royal Society of Chemistry. (C) Schematic of the acoustic flow cytometry system: (a) microfluidic device with collinearly aligned US transducer and laser focusing optical objective, (b) hydrodynamic 3D flow focusing in the microfluidic device, (c) magnified view of a collinearly aligned transducer and laser beam interacting with a particle and producing backscatter and PA waves, and (d) an experimental setup with the laser focused on the interrogation zone. Reproduced with permission from Gnyawali, V.; Strohm, E. M.; Wang, J.-Z.; Tsai, S. S. H.; Kolios, M. C.Sci Rep 2019, 9, 1585 (ref 53). Copyright 2019, Springer Nature. (D) Schematic of a multistage device for tumor cell isolation. The blood cells and tumor cells are collected from outlet A and outlet B. Reprinted from Sens. Actuators, B, Vol. 258, Wang, K., Zhou, W., Lin, Z., Cai, F., Li, F., Wu, J., Meng, L., Niu, L., Zheng, H., Sorting of tumor cells in a microfluidic device by multistage surface acoustic waves, pp 1174–1183 (ref 54) Copyright 2018, with permission from Elsevier. (E) Optical imaging indicated the positions of the regions (I–IV) for monitoring the distribution and trajectory of samples within the standing surface acoustic waves and traveling surface acoustic wave fields. Top right, finger pairs of the circular interdigital transducers; and bottom right, interdigital transducers on the substrate. Reprinted from Sens. Actuators, B, Vol. 258, Wang, K., Zhou, W., Lin, Z., Cai, F., Li, F., Wu, J., Meng, L., Niu, L., Zheng, H., Sorting of tumor cells in a microfluidic device by multistage surface acoustic waves, pp 1174–1183 (ref 54) Copyright 2018, with permission from Elsevier. (F) CTCs sorting from PBMCs, when CTCs are of higher (a) and lower (b) acoustic impedance than that of PBMCs. Reproduced from Karthick, S.; Pradeep, P. N.; Kanchana, P.; Sen, A. K. Lab Chip 2018, 18, 3802–3813 (ref 55), with permission of the Royal Society of Chemistry.
Figure 3.
Figure 3.
(A) DLD device. (a) Cascading design with four active regions and five outlets for high-resolution size-based cell sorting. (b) Device design considerations to improve sorting resolution including a wide theoretical cell fractioning unit with wide and long post arrays to introduce sorting corrections through redundancy, and buffer flow along outer walls to eliminate edge effects. Outlet resistances were COMSOL modeled to ensure vertical flow. (c) Evaluation of different pillar shapes in binary DLD devices and the effects of triangular and tumbling structures. Reproduced from Gomis, S.; Labib, M.; Coles, B. L. K.; van der Kooy, D.; Sargent, E. H.; Kelley, S. O. ACS Appl. Mater. Interfaces 2018, 10, 34811–34816 (ref 81). Copyright 2018 American Chemical Society. (B) Diagram of the three different DLD device designs. Design 1: hydrodynamically focused particles form a single flow stream. Design 2: all particles move toward the outer channel wall followed by change in the direction of the micropillar array that results in displacement of only larger particles. Design 3: combined principles used in designs 1 and 2. Reproduced from Xavier, M.; Holm, S. H.; Beech, J. P.; Spencer, D.; Tegenfeldt, J. O.; Oreffo, R. O. C.; Morgan, H. Lab Chip 2019, 19, 513–523 (ref 82), with permission of The Royal Society of Chemistry. (C) (a) Schematic of a controlled incremental filtration device and (b) an assembled microfluidic module with 12 multiplexed devices. Reprinted from Cytotherapy, Vol. 21, Strachan, B. C., Xia, H. U. I., Vörös, E., Gifford, S. C., Shevkoplyas, S. S., Improved expansion of T cells in culture when isolated with an equipment-free, high-throughput, flow-through microfluidic module versus traditional density gradient centrifugation, pp 234–245 (ref 83). Copyright 2019, with permission from Elsevier. (D) Schematic of the CIF design with slanted posts and the direction of flow from top to bottom. Reprinted from Cytotherapy, Vol. 21, Strachan, B. C., Xia, H. U. I., Vörös, E., Gifford, S. C., Shevkoplyas, S. S., Improved expansion of T cells in culture when isolated with an equipment-free, high-throughput, flow-through microfluidic module versus traditional density gradient centrifugation, pp 234–245 (ref 83). Copyright 2019, with permission from Elsevier. (E) CIF can operate in two ways: (a) hanging a bag with the input sample >5 ft above the module or (b) by compression of the sample bag with an infusion cuff. Reprinted from Cytotherapy, Vol. 21, Strachan, B. C., Xia, H. U. I., Vörös, E., Gifford, S. C., Shevkoplyas, S. S., Improved expansion of T cells in culture when isolated with an equipment-free, high-throughput, flow-through microfluidic module versus traditional density gradient centrifugation, pp. 234–245 (ref 83). Copyright 2019, with permission from Elsevier. (F) Schematic and (G) image of the inertial focusing-enhanced microfluidic system for cell processing. In this device, sorting of rare cells is accomplished by negative selection of prelabeled WBCs with immunomagnetic beads. First, the DLD device separates nucleated cells from RBC, platelets, and unbound magnetic beads. In the next step, the cells are accelerated through an inertial focusing device. The aligned tagged cells pass through a magnetic field where they are pushed toward the center of the channel. Remaining untagged cells are refocused in a second inertial focusing device and then entered a different region of the magnetic field leading to the removal of all labeled cells. Reproduced from Fachin, F.; Spuhler, P.; Martel-Foley, J. M.; Edd, J. F.; Barber, T. A.; Walsh, J.; Karabacak, M.; Pai, V.; Yu, M.; Smith, K.; Hwang, H.; Yang, J.; Shah, S.; Yarmush, R.; Sequist, L. V.; Stott, S. L.; Maheswaran, S.; Haber, D. A.; Kapur, R.; Toner, M. Sci. Rep., 2017, 7, 1–11 (ref 84). Copyright 2017 Springer Nature.
Figure 4.
Figure 4.
(A) Mechatronic system (a) used to control cell ratcheting across the device. (b) Paramagnetic pillars patterned on a glass slide and (c) a flow cell. (d) The 1 μm particles moved across the ratchet and achieved a “critical pitch” at 40 μm pillar pitch. Reproduced from Murray, C.; Miwa, H.; Dhar, M.; Park, D. E.; Pao, E.; Martinez, J.; Kaanumale, S.; Loghin, E.; Graf, J.; Rhaddassi, K.; Kwok, W. W.; Hafler, D.; Puleo, C.; Di Carlo, D. Lab Chip 2018, 18, 2396–2409 (ref 30), with permission of The Royal Society of Chemistry. (B) Microfluidic device for MATE-seq. (a) The device integrated a DLD array and a droplet generator with inputs for barcoded cells-free pNPs mixture, buffer, oil, and lysis/RT-PCR mix, and outputs for the water-in-oil droplets and waste. (b) The barcoded cells and free pNPs were flowed in parallel with RT-PCR buffer (no mixing). (c) The barcoded cells after DLD were displaced toward the droplet generator (free pNPs removed). (d) Barcoded cells were encapsulated in droplets with lysis and RT-PCR mix. Reproduced from Ng, A. H. C.; Peng, S.; Xu, A. M.; Noh, W. J.; Guo, K.; Bethune, M. T.; Chour, W.; Choi, J.; Yang, S.; Baltimore, D.; Heath, J. R. Lab Chip 2019, 19, 3011–3021 (ref 17), with permission of The Royal Society of Chemistry. (C) Microfluidic utilizing giant magnetoresistance (GMR) integrated sensors. (a) Chip with microfluidic channel and storage chambers; (b) micrograph of the separation area inside the channel showing also the parallel conducting microstructures and the tapered conductors for the isolation of cells; and (c) micrograph of a chamber and quantification area including the GMR sensor, the conducting microstructure on top of the sensor for the attraction and magnetization of the MPs, and parallel conducting microstructures for manipulation of the magnetically labeled cancer cells. Reprinted from Sens. Actuators, B, Vol. 241, Kokkinis, G., Cardoso, S., Keplinger, F., Giouroudi, I., Microfluidic platform with integrated GMR sensors for quantification of cancer cells, pp 438–445 (ref 88). Copyright 2017, with permission from Elsevier. (D) Schematic of microparticle distribution within the microfluidic using dual-neodymium magnet-based negative magnetophoresis. Reprinted from Kye, H. G.; Park, B. S.; Lee, J. M.; Song, M. G.; Song, H. G.; Ahrberg, C. D.; Chung, B. G. Sci. Rep. 2019, p 9502 (ref 89). Copyright 2019 Springer Nature. (E) Magnetizable micropipette tip for MACS, so-called “MACS-Tip” and standard operating procedure. Reprinted from Sens. Actuators, B, Vol. 272 Oh, S., Jung, Su H., Seo, H.,Min, M., Kim, B., Hahn, Y., Kang, J. H., Choi, S., Magnetic activated cell sorting (MACS) pipet tip for immunomagnetic bacteria separation, pp 324–330 (ref 24). Copyright 2018, with permission from Elsevier.
Figure 5.
Figure 5.
(A) Schematic of a microfluidic cell sorter: (a) schematic of optical detection setup, (b) micrograph of sorter chip with jet flow generation chamber and microheaters, (c) illustration of the sorting method, red cells of interest were sorted with an upper jet flow generator into a lower outlet channel and green cells flowed to the waste, and (d) SEM of microheaters. Reproduced from de Wijs, K.; Liu, C.; Dusa, A.; Vercruysse, D.; Majeed, B.; Tezcan, D. S.; Blaszkiewicz, K.; Loo, J.; Lagae, L. Lab Chip 2017, 17, 1287–1296 (ref 94), with permission of The Royal Society of Chemistry. (B) Spark-generated microbubble cell sorter: (a) microfluidic for 3D hydrodynamic focusing and sorting. When a target sample passed through the laser spot, a spark discharge was triggered, and the cavitation microbubble deflected the identified sample into the collection channel, (b) photograph of the device, and (c) chip was composed of middle part made of stainless steel and the others were glass. Reproduced from Spark-generated microbubble cell sorter for microfluidic flow cytometry, Zhao, J.; You, Z., Cytometry A, 93, pp 222–231 (ref 95). Copyright 2018 Wiley. (C) Microfluidic sperm sorter: (a) photograph of the device made of PDMS and glass, (b) chambers A for sorting medium, B for semen seeding, and C for sperm collection, (c) medium flowing out from chamber A was supplied into chambers B and C, (d) microchannel network showing the junction area (red square). The 14 microchannels formed a laminar flow distribution into a crescent-shaped diffuser enabling more motile spermatozoa to swim into this zone and travel the distance along the multiple microchannels. Reproduced from Nagata, M. P. B.; Endo, K.; Ogata, K.; Yamanaka, K.; Egashira, J.; Katafuchi, N.; Yamanouchi, T.; Matsuda, H.; Goto, Y.; Sakatani, M.; Hojo, T.; Nishizono, H.; Yotsushima, K.; Takenouchi, N.; Hashiyada, Y.; Yamashita, K. Proc. Natl. Acad. Sci. U.S.A., 115, pp E3087–E3096 (ref 98). Copyright 2018 National Academy of Sciences. (D) Microfluidic sorter for animal longitudinal CTC studies: (a) pump withdraws blood from an artery of a mouse and directs blood into a chip. CTC-depleted blood returns to the jugular vein of the mouse via a second cannula. (b) Top-view image of the microfluidic chip with valve actuation lines, (c) fluorescent CTC emits two pulses of light detected by a PMT. Computer-controlled pneumatic valves redirect fluorescent CTCs to a collection tube. A low-pass filter was applied to the raw data for identifying true peaks. (d) CTC sorting in real time, (e) enrichment of CTCs by a secondary sorting chip designed with a parallel channel to flush CTCs into wells containing lysis buffer. Reproduced from Hamza, B.; Ng, S. R.; Prakadan, S. M.; Delgado, F. F.; Chin, C. R.; King, E. M.; Yang, L. F.; Davidson, S. M.; DeGouveia, K. L.; Cermak, N.; Navia, A. W.; Winter, P. S.; Drake, R. S.; Tammela, T.; Li, C. M.-C.; Papagiannakopoulos, T.; Gupta, A. J.; Shaw Bagnall, J.; Knudsen, S. M.; Vander Heiden, M. G. et al. Proc. Natl. Acad. Sci. U.S.A. 116, pp 2232–2236 (ref 100). Copyright 2019 National Academy of Sciences.
Figure 6.
Figure 6.
(A) Diamagnetic droplet microfluidic: (a) sorting of cell-containing droplets from empty droplets, (b) size distinction between a particle-encapsulating droplet and empty droplets, (c) region of high magnetic field gradient with droplets deflected based on their size, (d) sorting of droplets into different reservoirs. Reproduced from Navi, M.; Abbasi, N.; Jeyhani, M.; Gnyawali, V.; Tsai, S. S. H. Lab Chip 2018, 18, 3361–3370 (ref 115), with permission of The Royal Society of Chemistry. (B) Fluorescence-activated droplet sorting (FADS) system: (a) micrograph of the acoustic sorting system and the view of the sorting region. Reproduced from Li, P.; Ma, Z.; Zhou, Y.; Collins, D. J.; Wang, Z.; Ai, Y. Anal. Chem. 2019, 91, 9970–9977 (ref 116). Copyright 2019 American Chemical Society. (C) Schematic of a single-cell RT-PCR device integrating lysis and reagent addition. The device produced droplets ready for amplification. Cells were encapsulated with lysis buffer (a) and content mixed (b). Excess oil removed from the emulsion (c), and droplets packed for the incubation for a controlled time (d). Droplets with lysed-cells were merged with droplets containing PCR buffer for amplification (e). Cells expressing the target mRNA (f), yielded fluorescent TaqMan-positive signal (g). Reproduced from Kim, S. C.; Clark, I. C.; Shahi, P.; Abate, A. R. Anal. Chem. 2018, 90, 1273–1279 (ref 117). Copyright 2018 American Chemical Society. (D) Schematics of single-cell RT-LAMP assay using Sort N’ Merge platform: (a) droplets containing RT-LAMP reactants were generated, (b) droplets containing single-cell and lysis buffer were generated and sorted into the storage device, (c) paired droplets were merged by electrohydrodynamic forces. RT-LAMP reaction performed followed by imaging-based fluorescence measurements, (d) content of the droplets, and (e) principle of RT-LAMP reactions. Reproduced from Chung, M. T.; Kurabayashi, K.; Cai, D. Lab Chip 2019, 19, 2425–2434 (ref 118) with permission of The Royal Society of Chemistry. (E) Droplet based platform for the screening of specific TCR T cells: (a) only specific TCR T cells are activated upon recognition of their cognate antigen, triggering the expression of eGFP and (b) schematic of the workflow. Droplets containing activated T cells were sorted for downstream molecular analysis. Reproduced from Segaliny, A. I.; Li, G.; Kong, L.; Ren, C.; Chen, X.; Wang, J. K.; Baltimore, D.; Wu, G.; Zhao, W. Lab Chip 2018, 18, 3733–3749 (ref 119), with permission of The Royal Society of Chemistry. (F) Integrated digital-droplet microfluidic device and (a) view of multilayer construct of the device and (b) image of the device and the schema of operations. Reproduced from Ahmadi, F.; Samlali, K.; Vo, P. Q. N.; Shih, S. C. C. Lab Chip 2019, 19, 524–535 (ref 120), with permission of The Royal Society of Chemistry. (G) Digital detection of lambda DNA with three different concentrations of templates. Reproduced from Li, X.; Zhang, D.; Zhang, H.; Guan, Z.; Song, Y.; Liu, R.; Zhu, Z.; Yang, C. Anal. Chem. 2018, 90, 2570–2577 (ref 121). Copyright 2018 American Chemical Society.
Figure 7.
Figure 7.
(A) Wedge-shaped microfuidic chip: (a) overview and (b) dimensions of the microfuidic chip and (c) schematic diagram of CTC isolation using a wedge-shaped microchamber. Reproduced from Yang, C.; Zhang, N.; Wang, S.; Shi, D.; Zhang, C.; Liu, K.; Xiong, B. J. Transl. Med. 2018, 16, p 139 (ref 132). Copyright 2018 Springer Nature. (B) Microfluidic filter device: (a) schematic of device with two microporous membranes and (b) exploded view showing design of the chip with seven layers, including channel, vias, and two layers to seal the top and bottom of the device. Reproduced from Qiu, X.; Lombardo, J. A.; Westerhof, T. M.; Pennell, M.; Ng, A.; Alshetaiwi, H.; Luna, B. M.; Nelson, E. L.; Kessenbrock, K.; Hui, E. E.; Haun, J. B. Lab Chip 2018, 18, 2776–2786 (ref 133), with permission of The Royal Society of Chemistry. (C) “Confining” device: (a) microscopic image of the flow region containing two series of confining microchannels. The fluid flow is indicated by white arrows. (b) Concept of the elasticity-based cell classification; the position of a microbead inside the microchannels reflected its elasticity. Reproduced from Ren, J.; Li, J.; Li, Y.; Xiao, P.; Liu, Y.; Tsang, C. M.; Tsao, S. W.; Lau, D.; Chan, K. W. Y.; Lam, R. H. W. ACS Biomater. Sci. Eng. 2019, 5, 3889–3898 (ref 134). Copyright 2019 American Chemical Society. (D) Dual depth, lattice-shaped channel network for (a) particle sorting, (b) transport of particles in the lattice region, and (c, d) particle movement between shallow and deep channels and into the main channels. Reproduced from Yanai, T.; Ouchi, T.; Yamada, M.; Seki, M. Micromachines (Basel) 2019, 10 ( 6), 425 (ref 135). Coyright 2019 The authors. (E) Pump-free cell trapping device bonded to a glass coverslip. Reproduced from Weng, L.; Ellett, F.; Edd, J.; Wong, K. H. K.; Uygun, K.; Irimia, D.; Stott, S. L.; Toner, M. Lab Chip 2017, 17, 4077–4088 (ref 136), with permission of The Royal Society of Chemistry. (F) Diagram showing the strategy for cell sorting based on the HDF scheme. Reproduced from Ozawa, R.; Iwadate, H.; Toyoda, H.; Yamada, M.; Seki, M. Lab Chip 2019, 19, 1828–1837 (ref 137), with permission of The Royal Society of Chemistry.
Figure 8.
Figure 8.
(A) Device utilizing DEP and hydrodynamic drag forces for cell sorting: (a) schematic of the concept of railing target cells (green) along a track (electrode) under pDEP and hydrodynamic drag and (b) fluorescence images of the tracks and the outlets during cell sorting. HCT116 cells (green) are sorted from 10 μm polystyrene beads (red). Reproduced from Xing, X.; Ng, C. N.; Chau, M. L.; Yobas, L. Lab Chip 2018, 18, 3760–3769 (ref 147), with permission of The Royal Society of Chemistry. (B) SEM images (a) of the device’s flow chamber and (b) a close-up view. Reproduced from Xing, X.; Ng, C. N.; Chau, M. L.; Yobas, L. Lab Chip 2018, 18, 3760–3769 (ref 147), with permission of The Royal Society of Chemistry. (C) Time-lapse images of yeast cells (a) rotational motions at the center of wireless electrodes (A = 5 V, f = 50 kHz). (b) Rotational motions at the center of wireless electrodes and in the center area where floating electrodes were absent (A = 5 V, f = 500 kHz). (c) Clockwise rotation on their axes and propulsion around the wireless electrode edges (A = 5 V, f = 5 MHz). (d) Counterclockwise rotation on their axes and propulsion around wireless electrode edges (A = 5 V, f = 40 MHz). Reproduced from Wu, Y.; Ren, Y.; Tao, Y.; Hou, L.; Jiang, H. Anal. Chem. 2018, 90, 11461–11469 (ref 148). Copyright 2018 American Chemical Society.
Figure 9.
Figure 9.
(A) Dean flow fractionation device: (a) workflow for leukocyte impedance phenotyping for sample preprocessing, DFF leukocyte sorting, and impedance profiling, (b) image of the microfluidic chips, (c) optical image of single cells flowing through the electrodes in the detection region, and (d) measurement of multiple events from single cells. Reprinted from Biosens. Bioelectron., Vol. 118, Petchakup, C.; Tay, H. M.; Yeap, W. H.; Dalan, R.; Wong, S. C.; Li, K. H. H.; Hou, H. W. Label-free leukocyte sorting and impedance-based profiling for diabetes testing, pp 195–203 (ref 155). Copyright 2018, with permission from Elsevier. (B) Impedance profiling of different blood cell samples: (a) density scatter plot of cell size (|ZLF|, V) versus opacity of diluted whole blood, PBMCs, DFF-sorted monocytes, DFF-sorted lymphocytes, and DFF-sorted neutrophils and (b) frequency distribution of different leukocyte subtypes. Reprinted from Biosens. Bioelectron., Vol. 118, Petchakup, C.; Tay, H. M.; Yeap, W. H.; Dalan, R.; Wong, S. C.; Li, K. H. H.; Hou, H. W. Label-free leukocyte sorting and impedance-based profiling for diabetes testing, pp 195–203 (ref 155). Copyright 2018, with permission from Elsevier. (C) Sensing area showing a simple analytical expression for the lateral position measurement of the flowing particles (derived from the electrical signal, positions of the flowing particles, electrodes, and microchannel). Reproduced from Yang, D.; Ai, Y. Lab Chip 2019, 19, 3609–3617 (ref 156), with permission of The Royal Society of Chemistry. (D) Schematic of a microfluidic impedance cytometer showing impedance and fluorescence detection sections. The fluorescence from cells was measured simultaneously with impedance allowing direct correlation of electrical and fluorescent properties of single cells. Reproduced from Honrado, C.; Ciuffreda, L.; Spencer, D.; Ranford-Cartwright, L.; Morgan, H. J. R. Soc. Interface 2018, 15, 20180416 (ref 33), with permission of The Royal Society of Chemistry.
Figure 10.
Figure 10.
(A) Microfluidic chip for CTC isolation and whole genome amplification: (a) chip consisted of 3 layers, the valve control channel, the sample processing channel, and glass substrate, (b) photograph and (c) an SEM of the blood-filtering segment, (d) enrichment segment, and (e) staining segment. (f) Photograph and SEM image of a subchannel, cell-processing chambers. (g–i) Operation of a tristate valve. Reproduced from Li, R.; Jia, F.; Zhang, W.; Shi, F.; Fang, Z.; Zhao, H.; Hu, Z.; Wei, Z. Lab Chip 2019, 19, 3168–3178 (ref 157), with permission of The Royal Society of Chemistry. (B) Integrated microfluidic Dean-flow fractionation device: (a) design of the device, (b) principle of operation of flow regulatory chip showing membrane deformation when fluidic pressures in the control channels were increased to push two elastic membranes toward the fluidic channel, and (c) principle of cell sorting. Reproduced from Zhang, X.; Zhu, Z.; Xiang, N.; Long, F.; Ni, Z. Anal. Chem. 2018, 90, 4212–4220 (ref 158). Copyright 2018 American Chemical Society. (C) GAMA device: (a) view of the microfluidic device and an infusion apparatus connected to the input port, (b) valveless 10-channel device, a product from each channel is separately collected, (c) micrograph of the cell capture region, (d) 10-channel devices bonded to a glass silica wafer, (e) image of an intact and (f) lysed single cell, and fluorescence observed from YOYO-1 stained genomic DNA. Reproduced from Tian, H. C.; Benitez, J. J.; Craighead, H. G. PLoS One 2018, 13, e0191520 (ref 14) with permission from PLOS.
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References

    1. Jameson JL; Longo DL N. Engl. J. Med 2015, 372, 2229–2234. - PubMed
    1. Macias M; Alegre E; Diaz-Lagares A; Patino A; Perez-Gracia JL; Sanmamed M; Lopez-Lopez R; Varo N; Gonzalez A In Advances in Clinical Chemistry, Vol. 83; Makowski GS; Elsevier, 2018; pp 73–119. - PubMed
    1. Jeffrey SS; Toner M Lab Chip 2019, 19, 548. - PubMed
    1. Bedard PL; Hansen AR; Ratain MJ; Siu LL Nature 2013, 501, 355. - PMC - PubMed
    1. Brooks JD Genome Res. 2012, 22, 183–187. - PMC - PubMed

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