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1 solid stress is on the order of 1.3 to 13.0 kPa (10-100 mmHg)--high enough to cause compression of f
2 +/-5.5 kPa in the nonfailing to 134.4+/-35.0 kPa in the HF to 201.7+/-36.4kPa in the HF+LVAD groups (
4 had the highest probabilities of LSM >/=8.0 kPa (overall probability: 17.2% [12.5-23.4]; this probab
8 adjusted predicted probability of LSM >/=8.0 kPa increased per age decade, with probabilities ranging
10 tion-based study of older adults, LSM >/=8.0 kPa, suggestive of clinically relevant fibrosis, was pre
13 a/year) in 7-14 kPa bLSM, or decrease (</= 0 kPa/year) in >/= 14 kPa bLSM (P = 0.949 between these tw
15 lytical determination (from 0.1627 to 0.0128 kPa at 0.5 kPa O2 and from 0.9393 to 0.1532 kPa at 20 kP
17 sor with a sensitivity ( approximately 0.018 kPa(-1) ), response time ( approximately 60 ms), and goo
18 ressive stiffness of O(1) kPa (0.49 +/- 0.04 kPa stress at 30% compressive strain) and therefore mimi
26 us grade 1, 90.4 kPa +/- 9.3; grade 5, 120.1 kPa +/- 15.4), and there were weak correlations between
27 (20 +/- 7 kPa), PaCO2 40 +/- 5 torr (5 +/- 1 kPa), and core temperature 33 degrees C +/- 1 degrees C.
28 rrected PaCO2 (4.4 kPa [4.1-4.6 kPa] vs. 5.1 kPa [5.0-5.3 kPa], p = 0.0001), and temperature-uncorrec
29 </=0.30, or IQR/M >0.30 with LSE median <7.1 kPa), and "poorly reliable" (IQR/M >0.30 with LSE median
31 rain neurons (ECFNs; optimum approximately 1 kPa) and U251 glioma cells (optimum approximately 100 kP
33 impaired in patients with an increase (>/= 1 kPa/year) in 7-14 kPa bLSM, or decrease (</= 0 kPa/year)
34 Pa(-1) is achieved in the pressure region <1 kPa with power generation of tens of muW cm(-2) from a g
37 rix to collagen-1-coated 2D substrates of ~1 kPa results in self-organization of all three germ layer
39 ith an average compressive stiffness of O(1) kPa (0.49 +/- 0.04 kPa stress at 30% compressive strain)
40 indicators is significantly different (0-10 kPa and 1-100 kPa CO2) that enables a broad variety of a
41 of hMSCs cultured on initially stiff (E ~ 10 kPa) and then soft (E ~ 2 kPa) phototunable PEG hydrogel
43 de substrates of physiological stiffness (10 kPa), and Matrigel micropatterns were used to generate p
44 significantly different (0-10 kPa and 1-100 kPa CO2) that enables a broad variety of applications.
45 th strains of 20-500% and stresses of 10-100 kPa, falling exactly into the dynamic range of a muscle.
46 de gels of three stiffnesses (1, 30, and 100 kPa) and treated with a range of epidermal growth factor
49 c materials with a Young's modulus below 100 kPa conforming to biological applications, yet those gel
50 oft biological tissue (Young's modulus < 100 kPa), and the capability to undergo extreme deformations
53 cisely controllable low moduli from 1 to 100 kPa, below the lower limit of traditional elastomers; mo
56 2 partial pressures in the range of 0.02-105 kPa, where the ultralow partial pressure range is releva
57 airway resistance (abeta coefficient, -0.11 kPa/s; 95% CI, -0.21 to -0.02; P = .02), decreased bronc
67 , lower platelets, and liver stiffness >/=12 kPa at year 5 represent the main risk factors for late H
68 seline and year 5, and liver stiffness >/=12 kPa at year 5 were independently associated with more fr
71 s not statistically significant (506 +/- 126 kPa, P=0.07), the addition of intraluminal thrombus to v
73 anning a vapor pressure range of 0.027 to 13 kPa was generated with modulated peak fwhm (full width a
74 ts with an increase (>/= 1 kPa/year) in 7-14 kPa bLSM, or decrease (</= 0 kPa/year) in >/= 14 kPa bLS
78 n using biogas as the only CO2 source at 140 kPa, the CO2 consumption rate corresponded to 2.59 L CO2
79 rmentation was increased from 101.325 to 140 kPa, higher CO2 solubility was achieved, thereby positiv
80 cifically investigated mild TBI range (0-145 kPa) using physiological (heart rate), pathological (lun
83 -cortex detachment which increased from 0.15 kPa in stem cells to 0.71 kPa following chondrogenic dif
86 is (stage F3-F4, 46 [32.4%] of 142) was 4.15 kPa (AUROC = 0.954, sensitivity = 0.85, specificity = 0.
87 ices with stiffness measurements of 9 and 15 kPa, assessed by immunofluorescent imaging and quantitat
89 kPa at 0.5 kPa O2 and from 0.9393 to 0.1532 kPa at 20 kPa O2) in comparison with a conventional phas
90 media and adventitia layers (from 80 to 160 kPa), dropped abruptly at the interface (from 160 to <5
92 as the difference between 5 and 20 Hz, 0.18 kPa.L(-1).s; Asthma Control Questionnaire score, 0.76; a
93 elastic modulus of the zebra finch ML is 18 kPa at 5% strain, which is comparable to elastic moduli
96 ticity, Et, increases daily for heart to 1-2 kPa by embryonic day 4 (E4), and although this is ~10-fo
97 , P = .0003) but not at 28 Hz (children, 1.2 kPa +/- 0.2; adolescents, 1.3 kPa +/- 0.3; adults, 1.2 k
102 (children, 2.2 kPa +/- 0.3; adolescents, 2.2 kPa +/- 0.2; adults, 2.6 kPa +/- 0.3; analysis of varian
103 cents than in adults at 56 Hz (children, 2.2 kPa +/- 0.3; adolescents, 2.2 kPa +/- 0.2; adults, 2.6 k
104 ctuators that can generate up to 1.7 mN (3.2 kPa) of passive tension force and 300 muN (0.56 kPa) of
106 sensitivity >/=90% were very close: 6.3/6.2 kPa for >/=F2, 8.3/8.2 kPa for >/=F3, and 10.5/9.5 kPa f
107 s were 5.7 kPa (interquartile range, 4.7-7.2 kPa) and independently associated with HBV DNA load, asp
109 radients of 0.5, 1.7, 2.9, 4.5, 6.8, and 8.2 kPa/mm, spanning the in vivo physiological and pathologi
110 ycol) (PEG) hydrogels (Young's modulus E ~ 2 kPa) depended on previous culture time on stiff tissue c
111 ally stiff (E ~ 10 kPa) and then soft (E ~ 2 kPa) phototunable PEG hydrogels resulted in either rever
112 sion with a bulk modulus, kappa = 140 +/- 20 kPa; applying negative pressures leads to volumetric exp
113 5 kPa O2 and from 0.9393 to 0.1532 kPa at 20 kPa O2) in comparison with a conventional phase-modulati
114 st, on stiff substrates (Young's modulus >20 kPa), traction stress plateaus at a limiting value and t
118 er, the operating pressure was less than 200 kPa, which eliminated the need for an expensive high-pre
122 lant of our tissue-engineered construct (239 kPa versus normal=193, P=0.1; versus infarct=304 kPa, P=
123 Calibration experiments performed over 0-25 kPa O2 and 10-30 degrees C temperatures ranges reveal li
124 ints were chosen to predict the absence (<25 kPa) or presence (>/=40 kPa) of LREs, thus enabling corr
126 lnuts subjected to pressure treatment at 256 kPa, 138 degrees C, were able to diminish the IgE cross-
127 nd subsequent stiffening (from ca. 3.5 to 28 kPa) increased the cell area and nuclear localization of
130 logical range of stiffness (E = 1.85 to 5.29 kPa), with and without RGD binding sites or collagen fib
131 Also we determined 146-220 kPa and 221-290 kPa levels as moderate and severe TBI based on 35%, and
133 (children, 1.2 kPa +/- 0.2; adolescents, 1.3 kPa +/- 0.3; adults, 1.2 kPa +/- 0.2; analysis of varian
137 at of the unaffected shoulder (median, 203.3 kPa; IQR, 144.1-242.7 kPa) in the shoulder-neutral posit
141 (4.4 kPa [4.1-4.6 kPa] vs. 5.1 kPa [5.0-5.3 kPa], p = 0.0001), and temperature-uncorrected PaCO2 (p
142 s 46 +/- 12 years, LSM value was 8.4 +/- 6.3 kPa, and 188 patients (12.8%) had metabolic syndrome.
143 ce was similar in 31 hypoxemic (Pao2 </= 7.3 kPa) and 63 less hypoxemic (Pao2 > 8.0 kPa) patients wit
147 have obtained can sustain up to 4.8 x 10(3) kPa pressure, a level comparable to cementitious materia
148 ns by a factor of approximately 360, from 30 kPa to 11 MPa along the first millimeter of the follicle
150 e were exposed to blast wave pressure of 300 kPa (43.5 psi) per day for 3 successive days, and euthan
151 re (100 degrees C) and applied pressure (300 kPa), ground TBEU thermoset powder can be remolded to bu
157 acteristic curve for SWE with a cutoff of 35 kPa for differentiating benign from malignant lesions we
161 very narrow range of ECM stiffness (0.1-0.4 kPa), and such ILP formation is Src family kinase depend
162 gas-phase dehydration of 1-propanol (0.075-4 kPa) was studied on zeolite H-MFI (Si/Al = 26, containin
163 ng alternating traction forces, of up to 1.4 kPa, at each flank of the lamellipodium, ColXVII knockdo
165 sensor unit achieves high sensitivity (14.4 kPa(-1) ), low detection limit (2 Pa), fast response ( a
170 p = 0.006), temperature-corrected PaCO2 (4.4 kPa [4.1-4.6 kPa] vs. 5.1 kPa [5.0-5.3 kPa], p = 0.0001)
171 er median liver stiffness values (7.1 vs 4.4 kPa; P < .001); HIV positive/HCV negative and HIV negati
175 ransistors with a maximum sensitivity of 8.4 kPa(-1), a fast response time of <10 ms, high stability
176 % CI for death by LSM were as follows: 6-9.4 kPa, 1.7 (0.63-4.79), P = 0.288; 9.5-14.5 kPa, 3.38 (1.2
177 5% CI by LSM category were as follows: 6-9.4 kPa, 1.89 (0.18-20.3), P = 0.599; 9.5-14.5 kPa, 6.59 (0.
179 kPa +/- 2.1; annulus fibrosus grade 1, 90.4 kPa +/- 9.3; grade 5, 120.1 kPa +/- 15.4), and there wer
180 ict the absence (<25 kPa) or presence (>/=40 kPa) of LREs, thus enabling correct classification of 82
183 0, 130, 160, 190, 230, 250, 290, 350 and 420 kPa) and determines the mortality rate as a non-linear f
185 monstrates 24 hour survival of rats in 0-450 kPa (0-800 Pas impulse) range at 10 discrete levels (60,
186 d cells and nuclei (day 14) of 1.04 +/- 0.47 kPa, 0.53 +/- 0.12 kPa and 7.06 +/- 4.07 kPa respectivel
187 mal fouling of the MnO2 coated membrane (0.5 kPa for 70 days), while the uncoated membrane experience
188 ermination (from 0.1627 to 0.0128 kPa at 0.5 kPa O2 and from 0.9393 to 0.1532 kPa at 20 kPa O2) in co
190 tile stress (from 1.8 +/- 0.7 to 4.7 +/- 0.5 kPa), and the average strain energy (0.4 +/- 0.2 to 2.1
191 ration grade (nucleus pulposus grade 1, 12.5 kPa +/- 1.3; grade 5, 16.5 kPa +/- 2.1; annulus fibrosus
192 .4 kPa, 1.7 (0.63-4.79), P = 0.288; 9.5-14.5 kPa, 3.38 (1.2-9.5), P = 0.021; >/=14.6 kPa, 12.7 (4.9-3
193 4 kPa, 1.89 (0.18-20.3), P = 0.599; 9.5-14.5 kPa, 6.59 (0.73-59.2), P = 0.092; >/=14.6 kPa, 59.5 (8.3
194 sus grade 1, 12.5 kPa +/- 1.3; grade 5, 16.5 kPa +/- 2.1; annulus fibrosus grade 1, 90.4 kPa +/- 9.3;
197 situ hydrogel softening (from ca. 14 to 3.5 kPa) led to a decrease in the cell area and nuclear loca
198 orta progressively stiffened from 74.3+/-5.5 kPa in the nonfailing to 134.4+/-35.0 kPa in the HF to 2
199 ly higher hepatic stiffness (15.6 versus 5.5 kPa, P < 0.0001), higher celiac RI (0.78 versus 0.73, P
200 (children, 5.6 kPa +/- 0.8; adolescents, 6.5 kPa +/- 1.2; adults, 7.8 kPa +/- 1.2; analysis of varian
202 h cell pre-stress with culture on stiff (7.5 kPa) polyacrylamide gels (with or without transforming g
204 d abruptly at the interface (from 160 to <5 kPa), and increased slightly towards the outer boundary
206 ss values mimicking those found in normal (5 kPa) and glaucomatous meshworks (75 kPa), or tissue cult
208 ge of stiffness from approximately 0.5 to 50 kPa, stemness maintenance did not correlate with initial
209 stiffness at 80 Hz and 48-week feeding, 0.51 kPa +/- 0.12 in the steatohepatitis group vs 0.29 kPa +/
210 air reveal that the presence of H2O at 2.55 kPa enhances CO2 adsorption, while the presence of CO2 a
211 tor that can generate up to 300 microN (0.56 kPa) of active tension force in response to a noninvasiv
212 ) of passive tension force and 300 muN (0.56 kPa) of active tension force in response to external sti
215 fness was around 150 Pa and increased to 1-6 kPa in areas near fibrillar collagen deposition in fibro
220 3; adolescents, 2.2 kPa +/- 0.2; adults, 2.6 kPa +/- 0.3; analysis of variance, P = .009) and 84 Hz (
223 emperature-corrected PaCO2 (4.4 kPa [4.1-4.6 kPa] vs. 5.1 kPa [5.0-5.3 kPa], p = 0.0001), and tempera
226 variance, P = .009) and 84 Hz (children, 5.6 kPa +/- 0.8; adolescents, 6.5 kPa +/- 1.2; adults, 7.8 k
229 dimensional shear wave elastography were 9.6 kPa and 10.2 kPa, and for cirrhosis 19.7 kPa and 16.4 kP
234 mechanical behavior (elastic modulus: ca. 60 kPa; fatigue life: >5000 cycles; mechanically stable at
235 ilopodia formation, whereas adhesion to a 60-kPa Ecad-Fc PA gel induced Arp2/3-dependent lamellipodia
236 gths, generate stresses of approximately 600 kPa, and produce peak power densities over 2 kW/kg-all e
242 es C) and vapor pressure deficit (VPD, +0.66 kPa), annual percent deviation in precipitation (-38%),
243 o, inducing peak dynamic stress change of 67 kPa on the volcano surface and ~120 kPa in the spherical
244 - 0.8% vs 90.1% +/- 0.8%, for a 500 Torr (67 kPa) Xe cell loading-corresponding to nuclear magnetic r
248 han 50 mm Hg, PaO2 150 +/- 50 torr (20 +/- 7 kPa), PaCO2 40 +/- 5 torr (5 +/- 1 kPa), and core temper
249 houlder (median, 203.3 kPa; IQR, 144.1-242.7 kPa) in the shoulder-neutral position (P = .004) but not
250 kPa; interquartile range [IQR], 174.4-256.7 kPa) was significantly greater than that of the unaffect
251 of inspired oxygen (FiO) of 200 mm Hg (26.7 kPa) or less and an expected duration of ventilation of
254 sis was excellent in patients having bLSM <7 kPa, SVR, or no increase (<1 kPa/year) in 7-14 kPa bLSM.
256 or compensated cirrhosis (FibroScan, 9.6-70 kPa; cirrhosis, n = 9); median baseline HCV-RNA level wa
258 rfaces of varying substrate compliance (4-71 kPa) and tissue culture plastic (TCP) (> 1 gigapascal [G
261 .29 measured at GRE MR elastography and 2.76 kPa +/- 1.39 at SE-EPI MR elastography (n = 290; P = .15
262 ate was associated with higher pressure (777 kPa +/- 308 vs 630 kPa +/- 252, respectively; P < .001).
264 fovir HBV DNA levels >2000 IU/mL (mean, -0.8 kPa; P = .048) or TE values >7.6 kPa (mean, -1.2 kPa; P
266 s of the symptomatic shoulder (median, 234.8 kPa; interquartile range [IQR], 174.4-256.7 kPa) was sig
268 8; adolescents, 6.5 kPa +/- 1.2; adults, 7.8 kPa +/- 1.2; analysis of variance, P = .0003) but not at
277 moderate fibrosis (stages F0, F1, F2) (5.93 kPa +/- 2.31 [standard deviation] vs 3.35 kPa +/- 1.44,
280 oxia was defined as PaO2 >/=300 mm Hg (39.99 kPa), hypoxia as any PaO2 <60 mm Hg (7.99 kPa) or PaO2/F
281 PaO2 more than or equal to 300 mm Hg (39.99 kPa), hypoxia as any PaO2 less than 60 mm Hg (7.99 kPa)
282 xia was defined as PaO2 >/= 300 mm Hg (39.99 kPa), hypoxia as any PaO2<60 mm Hg (7.99 kPa) or PaO2/Fi
283 .99 kPa), hypoxia as any PaO2<60 mm Hg (7.99 kPa) or PaO2/FiO2 ratio </= 300, and normoxia, not defin
284 99 kPa), hypoxia as any PaO2 <60 mm Hg (7.99 kPa) or PaO2/FiO2 ratio </=300 and normoxia, not defined
285 hypoxia as any PaO2 less than 60 mm Hg (7.99 kPa) or PaO2/FIO2 ratio less than or equal to 300, and n
287 resolving small pressure changes in the few kPa range, making them unsuitable for applications such
288 ly to 2.3 g mm/m(2)h kPa from 1.7 g mm/m(2)h kPa for SPI alone whereas rutin decreased water vapour p
289 permeability significantly to 2.3 g mm/m(2)h kPa from 1.7 g mm/m(2)h kPa for SPI alone whereas rutin
291 ffness measurement (LSM) >/=8.0 kilopascals (kPa) was used as a cutoff suggesting clinically relevant
293 er stiffness measurements (LSM; kiloPascals [kPa]) at ART initiation were categorized as no or minima
294 er vapor permeability (WVP, from 3 to 9 g.mm.kPa(-1).h(-1).m(-2)), and decreased insoluble matter (IM
295 2) ) and an ultrahigh sensitivity (of 3.1 nF kPa(-1) ), which is a thousand times greater than that o
296 pressure-to-capacitance sensitivity (114 nF kPa(-1) ), which is at least 1000 times higher than any
297 ting in an extraordinary sensitivity (217 nF kPa(-1) or 24 muC N(-1) at a bias of 1.0 V) without usin
298 tiffness, from hundreds of Pa to hundreds of kPa, T cell metabolic properties and cell cycle progress
299 preclinical study, we used MRE to quantify (kPa) the elasticity modulus Gd and viscosity modulus Gl
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