Various biological processes

Abstraction

Mechanical forces, including tenseness, compaction, fluid shear emphasis, hydrostatic force per unit area and gravitation, play an progressively recognize function in the ordinance of assorted biological procedures at the molecular and cellular degree. They influence extracellular matrix ( ECM ) cistron look, ECM protein synthesis, adhesion, migration and cell fate indispensable in care of tissue homeostasis, production of inflammatory go-betweens of many burden sensitive cells such as fibroblasts, chondrocytes, bone-forming cells, endothelial cells and smooth musculus cells. The cell grip forces ( CTFs ) generated by cells themselves besides influences the assortment of biological procedures such as lesion healing, angiogenesis and metastasis. In this reappraisal, we discuss emerging bioengineered tools facilitated by microscale engineerings for analyzing the functions of mechanical forces in cell biological science. In mechanobiology experimental techniques, we discuss about microelectromechanical system ( MEMS ) based attacks for cell mechanobiology and microengineered platforms used in vivo for look intoing cellular procedure in normal and pathophysiological contexts.

1. Introduction

Aim

Scope

2. LITERATURE REVIEW

All life beings are composed of one or more cells which are the basic structural and functional units to exhibit the belongings of life. Harmonizing to their size and types of internal constructions, we can separate the cells as 2 Classs.

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  1. Prokaryotic cell
  2. Eukaryotic cell

2.1. Prokaryotic cell

The procaryotic cells are represented by all of the assorted signifiers of bacteriums. They have no chiseled karyon and membrane-bound cell organs and are composed of a individual DNA circle. Their forms and sizes are from infinitesimal domains, cylinders and coiling togss to flagellated rods and filiform ironss.

2.2. Eukaryotic Cell

All other types of beings ( protists, Fungis, works and animate beings ) are composed of structurally more complex Eukaryotic cells and the size of eucaryotic cells ( & gt ; 10 & A ; micro ; m ) are by and large much larger than that of procaryotic cells ( & A ; lt ; 10 & A ; micro ; m ) . Therefore, they require internal membrane-bound cell organs to transport out metamorphosis and conveyance mechanism. It is surrounded by a plasma membrane which allows the foods to come in and waste merchandises to go forth. The plasma membrane is formed from phospholipid bilayer of polar hydrophilic caputs and non-polar hydrophobic dress suits. It serves as a barrier for life and inanimate parts of a cell and plays an of import function in modulating cellular map [ 1 ] .

2.3. Load-Sensitive Cells

There are many types of mechanical lading environment of cells and tissues in a human organic structure. Cells experience assorted mechanical stimulations and peculiarly of import in cardiovascular and musculoskeletal systems. Fibroblasts in the tegument, lungs, bosom, sinews and ligaments, chondrocytes in gristle, bone-forming cells in bone marrow, endothelial cells in blood vas and vascular smooth musculus cells are all types of cells subjected to big mechanical forces.

First of all, fibroblasts in the tegument are resisted to tenseness, compaction and shear. The fibroblasts which dominate the sinews and ligaments perform many critical maps during development and after adulthood [ 2 ] . Its map is to form and keep the connective tissues during development and fix lesions during lesion mending [ 3 ] .

The chondrocytes which found in another type of supporting tissue, articular gristle, proliferate and differentiate in multiple phases in making the extracellular matrix ( ECM ) [ 4 ] . The two major supermolecules such as Type II collagen and big aggregating proteoglycan, aggrecan, are synthesized by chondrocytes at the proliferating phase. The type II collagen filaments allow the aiticular gristle in defying the shear emphasis and compressive emphasis [ 5 ] .

We know that the bone bears tenseness, compaction and tortuosity in vivo. The bone cells such as bone-forming cells are derived from mesechymal cells found in bone marrow and are subjected to diverse the mechanical forces [ 6 ] .

Endothelial cellswhich form the interior liner of blood vas are influenced by two distinguishable haemodynamic tonss.

  • Cyclic strain due to vessel wall distention and
  • Shear emphasis due to frictional forces applied by blood flow.

To keep the vas wall and circulatory map, the structural and functional unity of these cells are really of import [ 7 ] and it may lend to pathogenesis of vascular disease, coronary artery disease [ 8 ] .

The smooth musculus cells ( SMCs ) are another type of vascular cells and are subjected to compaction, shear and cyclic stretch due to pulsatile blood force per unit area. Its proliferation may lend to pathogenesis of several vascular diseases such as coronary artery disease and high blood pressure [ 9 ] .

Therefore, these cells are applied by matching mechanical forces in assorted types of in vitro systems [ 10 ] . The advantage of these systems is that the lading magnitude and frequence can be controlled easy and besides the mechanical belongingss of substrates ( stiffness ) and their surface chemical science can be modified easy.

The cells can be stretched either uniaxially or biaxially. When stretching the cells in uniaxial way, the substrate will be lengthened along this way and will be compressed in its perpendicular way. This type of stretching is suited for sinews and ligaments in mechanical burden of cells. When stretching the cells in biaxal waies, the stretching can be either in equibiaxial stretching or nonequibiaxial stretching. The substrate strains are same in all waies in equibiaxial stretching, and are different in nonequibiaxial stretching. This type of stretching is suited for cuticular fibroblasts [ 11 ] .

There is restriction in uniaxial stretching system. When the cells are subjected to cyclic uniaxial stretching, they orient off from stretching way and tend to reorient toward a way with minimum substrate distortion [ 12 ] .

The microgrooved substrates are used in cell alliance to get the better of this cell reorientation job [ 13 ] . Fibroblasts on these microgrooved substrates are aligned with microgrooves and keep its extended form.

The cells remain align in microgrooves whether it is stretching or non. In an experimental theoretical account including collagen gel matrix, the cell deform this matrix because they produce the grip force and are subjected to external mechanical stretching at the same clip. It is widely used in functional technology tissues concepts and in bio-scaffolding stuffs with high mechanical strength to implant the cells cause of its low mechanical strength for mechanical stretching [ 14 ] .

3. MICROMANIPULATION TECHNIQUES

We investigate how the cells sense and respond to mechanical emphasis depend on techniques and these probes are subjected to use controlled mechanical forces to populating cells and to mensurate the alterations in cellular distortion and change of molecular events. Micromanipulation techniques manipulate and step the mechanical belongingss of cells, nucleus, cell membrane and cytoskeleton utilizing mechanical, optical and magnetic agencies via a combined usage of microscopic intracellular signalling and molecular cell biological science techniques.

3.1. Micropipette Aspiration

We can mensurate the mechanical belongingss of a individual cell by using a known mechanical force or emphasis to deform the cell. The cell must be deformed by this force and its distortion must be measured. Micropipette aspiration is a classical technique for mensurating the mechanical belongingss of single cell such as elastic modulus and viscousness. In this technique, a low magnitude, negative force per unit area is applied to deform the cell and so the cell is elongated. This stretching part of the cell is introduced into micropipette.

A glass micropipette holding internal diameter of 1-5 & A ; micro ; m is used for distortion a cell and the vacuity is applied through the micropipette to the cell. The length of aspiration is varied with applied force. The all right force per unit area stairss measured with a preciseness force per unit area detector are created by an adjustable fluid reservoir. From experimental patterning positions, we can sort the cells as solid and liquid harmonizing to their response to threshold or critical force per unit area [ 15 ] . For the cells like liquid behavior ( e.g. , Neutrophils ) , if the force per unit area is applied above threshold or critical degree, it can do the complete cell aspiration into the glass micropipette. However, for the cells like solid behavior ( e.g. , fibroblasts, chondrocytes, endothelial cells ) , they enter merely a finite distance into micropipette even if the applied force per unit area exceeds above the threshold or critical degree. The cell can be lysed with the application of a sufficiently high force per unit area [ 16 ] [ 17 ] .

Experimentally mensurate the applied negative force per unit area? P and the ensuing aspiration length L to characterize the both liquid-like and solid-like cells. To characterize the liquid-like cell, it requires mensurating the radius of cell contour outside the micropipette ( Rc ) [ 18 ] .

The applied force per unit areas for aspiration are typically on the order of 1pN & A ; micro ; m-2=1Pa for soft cells and 1nN & A ; micro ; m-2 = 1kPa for stiff cells. For distortion, the soft cells required the force on the order of 10-100pN and the stiff cells required several nanonewtons. The cardinal experimental factors which determine the cogency of mechanical word picture consequences are the truth of applied force per unit area, the truth of cellular geometrical parametric quantity measurings, the synchronism of applied force per unit area and ensuing geometrical alterations of cell [ 19 ] .

We can besides utilize the micropipette aspiration technique for time-lapse surveies to understand molecular maps. A cell aspirated tardily in cytokinesis is accumulated green fluorescent protein ( GFP ) -myosin II to both the pipette terminal and the furrow [ 25 ] .

For proving the strength of specific ligand-receptor bindings, how the two micropipettes are employed was shown in extension of the technique. A micropipette immobilized a microbead coated with a particular antibody which was placed in contact with a cell. The 2nd micropipette was used to draw the cell from the coated microbead by increasing the applied force per unit area difference. It determines the output strength of the ligand-receptor interaction [ 26 ] .

3.2. Laser Traping

For pin downing the little objects within a defined part, there are many types of optical maser traps to pin down different types of atoms. The most common type is the optical pincers or optical maser pincers utilizing optical maser beams. When the local stretching or bending forces is applied to the atom by the cell, the microparticles can be attached to a cell membrane. This force is relative to the optical maser power required to restrain the atom. Therefore, we can pull strings the cell and step the stiffness of cell. The optical maser traps generate the scope of forces, 0.1-1 nN.

Optical caparison is a suited technique for use and mechanical word picture of suspended cells. Assorted unrecorded entities which have been studied by optical maser pincers are viruses and bacteriums [ 27, 28 ] , ruddy blood cells [ 29, 30 ] , natural slayer cells [ 31 ] and outer hair cells [ 32 ] . The so many articles which have besides been investigated by optical maser pincers are sidelong motions of membrane glycoprotein [ 33 ] , neural growing cones [ 34 ] , adhesion of chondrocytes [ 35 ] , intracellular snap of neutrophils [ 36 ] and intracellular cell organ conveyance in elephantine ameba [ 37 ] .

The two microbeads coated with adhesive ligands or antibodies are attached to a cell in diametral resistance to each other to adhere to specific receptors. The microbeads act as grips or clasps for displacing the cell membrane. The surface of a glass slide is fixed with one of the beads and the steady or time-varying stretching force is generated by the comparative motion of other bead. The emphasis applications can be extremely selective and localised because the microbeads are coated with ligands or antibodies on its surface.

Although we have published that the optical maser pincers is really effectual in cell mechanobiology, the cells may be induced unwanted harmful effects by long exposure of cells or utilizing a high powered optical maser [ 38, 39 ] . These unwanted effects have been suggested to ensue from photochemical and thermic reactions [ 40, 41 ] . To minimise the grade of exposure harm, the near-infrared optical maser is normally used because there is a wavelength dependance of the soaking up of optical maser [ 27 ] . However, the cell harm can be still caused by high photon flux denseness via two photon or multi-photon soaking up mechanisms [ 42 ] . Therefore, we need to take attention to minimise visible radiation induced cell harm and to decently construe experimental consequences.

Among several fluctuations of optical maser pincers, if a weakly focused laser beam is used as an optical channel, counsel and deposition of populating cells can be achieved with a high spacial declaration [ 43 ] . If the waies of two non-focused optical maser beams are opposite each other, a cell placed in between these beams would see surface forces stretching along the axis and the net force would be zero. The stretching force defined by the beams depends on the size and type of the cell, the brooding index, and the optical maser power. Based on this rule, a device, termed as an optical stretcher, has been used to mensurate the viscoelastic belongingss of several cell types [ 39 ] . It has proved that a whole cell was stretched by double optical pincers [ 44 ] . In optical stretcher, the non-focused light beams are used to minimise the possible visible radiation induced harm to the cells and the bead fond regards are non required.

By physically dividing the original optical maser beam or by time-sharing the optical maser beam with a mechano-optical or acousto-optical mechanism to debar the optical maser beam, multiple optical maser traps can be generated at the same time [ 45 ] . In this technique, assorted manners of emphasis ( e.g. , tensile, biaxal and bending ) are allowed to be applied on the cell. The arrays of optical maser emitted from perpendicular pit surface have besides been applied for optical caparison and active use of multiple cells and microbeads at the same time [ 46 ] .

Improvements continue to polish and spread out the capablenesss of optical maser pincers [ 47 ] . For case, optoelectronic pincers which utilize direct optical images to make light-addressable electrokinetic forces were demonstrated for massively parallel use of cells [ 48 ] . Based on localised surface Plasmon resonance excited by polarized visible radiation, research workers have verified a manner to pull strings and revolve biological cells [ 49 ] . In add-on, laser-tracking microrheology ( LTM ) can mensurate the mechanical belongingss within unrecorded cells [ 50, 51 ] . In laser-tracking microrheology ( LTM ) , low-power optical maser beam with a high spatiotemporal declaration tracks a investigation atom ( e.g. , a granule ) . The mechanical belongingss of the subcellular sphere or other complex viscoelastic stuffs are exposed by Brownian gesture of the atom to let measurings of local alterations in cell viscoelasticity. The mechano-activated signalling molecules, such as Src, were visualized and quantified with high temporal and spacial declarations in combination of fluorescent resonance energy transportation imaging techniques ( FRET ) [ 52 ] .

3.3. Magnetic Probes

Magnetic Fieldss are normally generated by electromagnets which are more easy controlled and permit the coevals of time-varying force Fieldss [ 54 ] . Single-pole electromagnets with a crisp tip generate a strong electric field gradient near the tip part. It is a map of the distance between the atom and tip of the electromagnet applied by the force to each magnetic bead. To bring forth a changeless magnetic field gradient, a brace of electromagnets can be used. The scope of force measurings generated by magnetic pincers with pole braces ( 0.1-10 pN ) is lower than the force by optical maser traps ( 0.1-1 nN ) . It has besides been reported that the forces up to 104 pN on a 4.5 & A ; micro ; thousand atom is in the part ( 10-100 & A ; micro ; m ) near the tip of a single-pole electromagnet [ 55 ] . Multiple brace of electromagnetic poles are required to command multiple waies and rotary motions of atoms at the same clip.

Similar in optical maser caparison, ligand coated magnetic beads are used to acquire examining specific cellular constituents [ 54, 55, 56 ] . The manners of working are magnetic gradient [ 55 ] and magnetic distortion cytometry ( MTC ) [ 57 ] . The MTC device can be farther utilised to capture and quantify rapid mechanochemical signalling activities in life cells when combined with FRET techniques [ 58 ] .

4. MICROELECTROMECHANICAL SYSTEMS ( MEMS ) TOOLS

MicroElectroMechanical System ( MEMS ) engineering is the integrating of mechanical elements, really little detectors and actuators, and electronics on a common Si substrate utilizing microfabrication engineerings. While the electronic devices are fabricated utilizing integrated circuit ( e.g. , CMOS, BICMOS processes ) , the micromechanical devices are fabricated utilizing micromachining procedures. MEMS engineering enables the creative activity of bantam machines which can work with microelectronics. The sizes of MEMS-based tools are really match with the micron graduated table sizes of most mammalian cells. The size fiting gives high truth in cell use and high spatial and temporal declarations in quantitative measurings of cellular responses. Many of the cells sense mechanical forces and change over them from mechanical into biochemical signals. This mechanism is known as mechanotransduction. Therefore, the MEMS techniques have an progressively strong impact on cell mechanobiology.

4.1. Microcantilever-Based Force Detectors

Atomic force microscopy ( AFM ) is capable of uncovering surface constructions with high spacial declaration. In AFM, the cantilever scanned across surface utilizing x-y piezoelectric tubing. The optical maser beam detect the flexing gesture of lever ( altering force ) reflected from rear of lever into photodetector. The feedback cringle maintains the changeless force by traveling lever up & A ; down ( z-piezo ) . The tip is attached to the terminal of cantilever with a low spring invariable. We can mensurate the force between cantilever tip and cell by utilizing a optical maser to observe lever gesture. The microcantilever is used to deform a cell and cell stiffness can be measured from the warp of cantilever.

The distortion of little cells are usually induced by the major techniques, such as micropipette aspiration, optical maser caparison, and magnetic distortion cytometry ( MTC ) , mentioned in old subdivisions, every bit good as AFM. These techniques besides measure the response of their corresponding cell force in the scope of 1 pN-10 nN. However, big cell distortion can bring on the big cell force response in many physiological conditions ( e.g. axonal hurt of & gt ; 50 % strain ) . The new types of microcantilevers or microcantilever-based MEMS devices are advanced in microfabrication and nanofabrication techniques. These are used to examine cell mechanical responses, such as cell indenture force response, cell stretch force response, and in situ observation of the cytoskeletal constituents during examining, under big distortions in the scope of 1 nN to 1 & A ; micro ; N, leting broad applications in analyzing cell mechanobiology. The grip forces generated by fibroblasts are measured by Galbraith et Al utilizing a microfabricated device capable of finding subcellular forces generated by single adhesive contacts [ 59 ] . The forces exerted on adhesive contacts can be continuously monitored by this device. To mensurate the responses of adherent fibroblasts to stretching forces, Yang and Saif developed a microfabricated force detector [ 60 ] .

Mentions

  1. Prince alberts B ( 1989 ) Molecular biological science of the cell. Garland, New York
  2. Camelliti P, Borg TK, Kohl P ( 2005 ) Structural and functional word picture of cardiac fibroblasts. Cardiovasc Res 65 ( 1 ) :40-51
  3. Mathews MB ( 1975 ) Connective tissue: macromolecular construction and development, Springer Berlin Heidelberg, New York
  4. Stockwell RA ( 1979 ) Biology of gristle cells. Cambridge ; New York. Cambridge Univ. Press.
  5. Lane Smith R, Trindade MC, Ikenoue T, Mohtai M, Das P, Carter DR, Goodman SB, SchurmanDJ ( 2000 ) Effects of shear emphasis on articular chondrocyte metamorphosis. Biorheology 37 ( 1-2 ) :95-107
  6. Aubin JE, Triffitt JT ( 2002 ) Mesenchymal root cells and osteoblast distinction. Academic Press, San Diego
  7. Michiels C ( 2003 ) Endothelial cell maps. J Cell Physiol 196 ( 3 ) :430-443
  8. Toborek M, Kaiser S ( 1999 ) Endothelial cell maps. Relationship to atherogenesis. Basic Res Cardiol 94 ( 5 ) :295-314
  9. Jackson CL, Schwartz SM ( 1992 ) Pharmacology of smooth musculus cell reproduction. High blood pressure 20 ( 6 ) :713-736
  10. Brown, T. D. ( 2000 ) . Techniques for mechanical stimulation of cells in vitro: A review.J. Biomech. 33, 3-14.
  11. Lee, A. A. , Delhaas, T. , Waldman, L. K. , MacKenna, D. A. , Villarreal, F. J. , and McCulloch, A. D. ( 1996 ) . An equibiaxial strain system for civilized cells. Am. J. Physiol.271, C1400-1408.
  12. Wang, J. H. , Goldschmidt-Clermont, P. , Wille, J. , and Yin, F. C. ( 2001b ) . Specificity of endothelial cell reorientation in response to cyclic mechanical stretching. J. Biomech. 34, 1563-1572.
  13. Wang, J. H. , and Grood, E. S. ( 2000 ) . The strain magnitude and contact counsel determine orientation response of fibroblasts to cyclic substrate strains. Connect. Tissue Res. 41, 29-36.
  14. Wang, J. H. , Jia, F. , Gilbert, T. W. , and Woo, S. L. ( 2003a ) . Cell orientation determines the alliance of cell-produced collagenic matrix. J. Biomech. 36, 97-102.
  15. Hochmuth RM. 2000. Micropipette aspiration of life cells. J. Biomech. 33:15-22
  16. Jones WR, Ting-Beall HP, Lee GM, Kelley SS, Hochmuth RM, Guilak F. 1999. Changes in the immature ‘s modulus and volumetric belongingss of chondrocytes isolated from normal and osteoarthritic human gristle. J. Biomech. 32:119-27
  17. Thoumine O, Ott A. 1997. Time scale dependent viscoelastic and contractile governments in fibroblasts probed by microplate use. J. Cell Sci. 110:2109-16
  18. Herant M, MarganskiWA, Dembo M. 2003. The mechanics of neutrophils: man-made modeling of three experiments. Biophys. J. 84:3389-413
  19. Liu XY, Wang YF, Sun Y. 2009. Cell contour trailing and informations synchronism for real-time, high truth micropipette aspiration. IEEE Trans. Autom. Sci. Eng. In imperativeness
  20. Evans E, Skalak R. 1980. Mechanicss and Thermodynamicss of Biomembranes. Boca Raton, FL: CRC
  21. Needham D, Nunn RS. 1990. Elastic distortion and failure of lipid bilayer membranes incorporating cholesterin. Biophys. J. 58:997-1009
  22. Theret DP, Levesque MJ, Sato M, Nerem RM, Wheeler LT. 1988. The application of a homogenous half-space theoretical account in the analysis of endothelial cell micropipette measurings. J. Biomech. Eng. 110:190-99
  23. Evans E, Yeung A. 1989. Apparent viscousness and cortical tenseness of blood granulocytes determined by micropipette aspiration. Biophys. J. 56:151-60
  24. Sato M, Ohshima N, Nerem RM. 1996. Viscoelastic belongingss of civilized porcine aortal endothelial cells exposed to shear emphasis. J. Biomech. 29:461-67
  25. Effler JC, Kee YS, Berk JM, TranMN, Iglesias PA, RobinsonDN.2006. Mitosis-specific mechanosensing and contractile-protein redistribution control cell form. Curr. Biol. 16:1962-67
  26. Shao JY, Hochmuth RM. 1996. Micropipette suction for mensurating piconewton forces of adhesion and tether formation from neutrophil membranes. Biophys. J. 71:2892-901
  27. Ashkin A, Dziedzic J, Yamane T. 1987. Optical caparison and use of individual cells utilizing infrared optical maser beams. Nature 330:769-71
  28. Ashkin A, Dziedzic J. 1987. Optical caparison and use of viruses and bacteriums. Science 235:1517-20
  29. Dao M, Lim C, Suresh S. 2003. Mechanicss of the human ruddy blood cell deformed by optical tweezers.J. Mech. Phys. Solids 51:2259-80
  30. Henon S, Lenormand G, Richert A, Gallet F. 1999. A new finding of the shear modulus of the human red blood cell membrane utilizing optical pincers. Biophys. J. 76:1145-51
  31. Seeger S, Monajembashi S, Hutter K, Futterman G, Wolfrum J, Greulich K. 1991. Application of optical maser optical pincers in immunology and molecular-genetics. Cytometry 12:497-504
  32. Murdock D, Ermilov S, Spector A, Popel A, Brownell W, Anvari B. 2005. Effectss of Thorazine on mechanical belongingss of the outer hair cell plasma membrane. Biophys. J. 89:4090-95
  33. Edidin M, Kuo S, Sheetz M. 1991. Lateral motions of membrane-glycoproteins restricted by dynamic cytoplasmatic barriers. Science 254:1379-82
  34. 44. Dai J, Sheetz M. 1995. Mechanical-properties of neural growing cone membranes surveies by tether formation with optical maser optical pincers. Biophys. J. 68:988-96
  35. Huang W, Anvari B, Torres JH, LeBaron RG, Athanasiou KA. 2003. Temporal effects of cell adhesion on mechanical features of the individual chondrocyte. J. Orthop. Res. 21:88-95
  36. Yanai M, Butler J, Suzuki T, Kanda A, Kurachi M, et Al. 1999. Intracellular snap and viscousness in the organic structure, prima, and draging parts of traveling neutrophils. Am. J. Physiol. Cell Physiol. 277: C432-40
  37. Ashkin A, Schutze K, Dziedzic J, Euteneur U, Schliwa M. 1990. Force coevals of organelle conveyance measured invivo by an infrared-laser trap. Nature 348:346-48
  38. Bronkhorst P, Streekstra G, Grimbergen J, Nijhof E, Sixma J, Brakenhoff G. 1995. A new method to analyze shape recovery of ruddy blood cells utilizing multiple optical caparison. Biophys. J. 69:1666-73
  39. Kaneta T, Makihara J, Imasaka T. 2001.An ” Optical channel ” : Atechnique for the rating of biological cell snap. Anal. Chem. 73:5791-95
  40. Peterman E, Gittes F, Schmidt C. 2003. Laser-induced warming in optical traps. Biophys. J. 84:1308-16
  41. Xie C, Goodman C, Dinno M, Li Y. 2004. Real-time raman spectrometry of optically trapped life cells and cell organs. Opt. Express. 12:6208-14
  42. Schneckenburger H, Hendinger A, Sailer R, Gschwend M, Strauss W, et Al. 2000. Cell viability in optical pincers: high power red laser rectifying tube versus neodymium: YAG optical maser. J. Biomed. Opt. 5:40-44
  43. Nahmias Y, Schwartz R, Verfaillie C, Odde D. 2005. Laser-guided direct authorship for 3-dimensional tissue technology. Biotech. Bioeng. 92:129-36
  44. Guck J, Ananthakrishnan R, Mahmood H, Moon T, Cunningham C, Kas J. 2001. The optical stretcher: a fresh optical maser tool to micromanipulate cells. Biophys. J. 81:767-84
  45. Guilford W, Tournas J, Dascalu D, Watson D. 2004. Making multiple time-shared optical maser traps with coincident supplanting sensing utilizing digital signal processing hardware. Anal. Biochem. 326:153-66
  46. Flynn R, Birkbeck A, Gross M, Ozkan M, Shao B, et Al. 2002. Parallel conveyance of biological cells utilizing separately addressable VCSEL arrays as optical pincers. Sens. Actuators. B Chem. 87:239-43
  47. Moffitt JR, Chemla YR, Smith SB, Bustamante C. 2008. Recent progresss in optical pincers. Annu. Rev. Biochem. 77:205-28
  48. Chiou P, Ohta A, Wu M. 2005. Massively parallel use of individual cells and microparticles utilizing optical images. Nature 436:370-72
  49. Miao XY, Lin LY. 2007. Traping and use of biological atoms through a plasmonic platform. IEEE J. Sel. Top. Quantum Electron. 13:1655-62
  50. Kuo SC. 2001. Using optics to mensurate biological forces and mechanics. Traffic 2:757-63
  51. Yamada S, Wirtz D, Kuo SC. 2000. Mechanicss of life cells measured by optical maser tracking microrheology. Biophys. J. 78:1736-47
  52. Wang Y, Botvinick EL, Zhao Y, Berns MW, Usami S, et Al. 2005. Visualizing the mechanical activation of Src. Nature 434:1040-45
  53. Gosse C, Croquette V. 2002. Magnetic pincers: micromanipulation and force measuring at the molecular degree. Biophys. J. 82:3314-29
  54. Ziemann F, Radler J, Sackmann E. 1994. Local measurings of viscoelastic moduli of embroiled actin webs utilizing an hovering magnetic bead microrheometer. Biophys. J. 66:2210-16
  55. Bausch A, Ziemann F, Boulbitch A, Jacobson K, Sackmann E. 1998. Local measurings of viscoelastic parametric quantities of disciple cell surfaces by magnetic bead microrheometry. Biophys. J. 75:2038-49
  56. Wang N, Butler J, Ingber D. 1993. Mechanotransduction across the cell-surface and through the cytoskeleton. Science 260:1124-27
  57. Wang N, Ingber DE. 1995. Probing transmembrane mechanical yoke and cytomechanics utilizing magnetic distortion cytometry. Biochem. Cell Biol. 73:327-35
  58. Na S, Collin O, Chowdhury F, Tay B, Ouyang M, et Al. 2008. Rapid signal transduction in life cells is a alone characteristic of mechanotransduction. Proc. Natl. Acad. Sci. USA 105:6626-31
  59. Galbraith CG, Sheetz MP. 1997. A micromachined device provides a new crook on fibroblast grip forces. Proc. Natl. Acad. Sci. USA 94:9114-18
  60. Yang S, Saif T. 2005. Reversible and quotable additive local cell force response under big stretches. Exp. Cell Res. 305:42-50

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