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1 ntained a 13 mum spacer to minimize detector dead volume.
2 es, carryover from run to run, and increased dead volume.
3 stagnant sample associated with the injector dead volume.
4 traditional capillary GC columns without any dead volumes.
5 channel exit ensures subnanoliter postcolumn dead volumes.
6 n or elimination, or both, of detection cell dead volume, (2) the ability to interrogate a nearly pur
7                Additionally, to decrease the dead volume and attain a better resolution, MGC was util
8 ages of convenient customization of the cell dead volume and convenient visual inspection of the surf
9 d to transient analysis by virtue of its low dead volume and high sensitivity.
10 ffect of design variations such as change in dead volume and pillar size within the lateral channels
11 icated devices not only significantly reduce dead volume and sample consumption but also increase the
12 stic microfluidics, significant reduction in dead volume and sample consumption can be achieved using
13              Delivery kinetics depend on the dead volume and the rate of carrier flow.
14          This LC-ESII/MS approach has little dead volume and thus provides excellent chromatographic
15               To minimize the analysis time, dead volumes and capacities of all components were optim
16                 This is mainly attributed to dead volumes and chromatographic processes introduced by
17 the goal of increasing sensitivity, reducing dead-volume and peak band broadening, optimizing combust
18   In addition to its compactness, negligible dead volume, and robustness, the device can be used at a
19  the electrosprayed liquid and minimized the dead volume associated with droplet formation at the ele
20                     In addition, there is no dead volume associated with the porous design, and becau
21 pening and out of the capillary, there is no dead volume associated with this interface.
22 m microchip to capillary indicated a minimum dead volume at the junction.
23 ion of molybdate, which eluted mainly in the dead volume, but had no negative effect on higher thiola
24 hout the immobilized protein to evaluate the dead volume, but this creates several experimental and t
25 m (LMCS), was interfaced to an optimized low dead volume combustion interface to preserve <300 ms ful
26         With the use of a PicoClear tee, the dead volume connection between a 50 microm i.d.
27        This result also reconfirms that zero-dead volume connectors with a sufficiently narrow bore c
28           The use of such arrays as ultralow-dead-volume detectors in microscale gas chromatographic
29 e been optimized for use in flow-through low-dead-volume electrochemical cells.
30 tection features on a fused silica chip in a dead volume-free manner, all extra-column peak dispersio
31 o in the design of microfluidics for stable, dead-volume-free placement of nanoliter-scale volumes of
32 irectly connected to the gel column via zero dead volume fused-silica connectors.
33                          Moreover, the small dead volume in our system allowed for high dynamic contr
34 A side-on interface was designed to minimize dead volume in the nLC x muFFE interface, eliminating th
35 0 microl of sample consumption, inclusive of dead volume in the reservoirs.
36 nnels of a microchip enabled simple and zero dead volume integration of the preconcentration with SDS
37 f high aspect ratio channels allows for zero dead volume interfaces between the microchip platform an
38 e use of postcolumn switching and associated dead volume issues.
39 f fabrication, universality, and lack of any dead volume make this design a superior CE/ESI-MS interf
40 xing chamber, a capillary column, and a zero dead-volume microelectrospray interface.
41 n microfluidics with temperature control and dead-volume minimization to rapidly generate thousands o
42                                      The low dead volume of the emitter arrays preserved peak shape a
43 eparation (little is added to the postcolumn dead volume of the LC system).
44                                              Dead volumes of different CVC lumens vary considerably.
45 ays is often only femto-to microliters, the "dead volume" of solutions supplied in syringes and tubin
46 due to sampling events, the impact of tubing/dead volumes on the estimation of diffusive fluxes and s
47 t outlet pressures up to 0.8 atm using a low-dead-volume polymer-coated surface acoustic wave (SAW) d
48 nt was sampled into microcapillaries using a dead volume-reduced world-to-chip interface.
49 c separation and detection using a true zero dead-volume sheathless CE-MS interface.
50 sheathless FESI device eliminates postcolumn dead volume since small particles (</= 10 micron) are pa
51            The multiemitter device has a low dead volume to facilitate coupling to capillary liquid c
52 wall intact and, therefore, does not add any dead volume to the CE-MS or nLC-MS interface.
53       The integrated nanoESI emitter adds no dead volume to the LC separation, allowing stable electr
54                                        A low-dead-volume valve, connected between the column junction
55 tention coefficient is the evaluation of the dead volume, which is the retention volume that would be