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17 protocols using neofox

1

Measuring Myocardial Oxygen Consumption

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Arterial and venous oxygen was measured using two 420‐μm‐diameter fibre‐optic oxygen sensors (Ocean Optics, NeoFox, UK) calibrated prior to use with 0% O2 (using the reducing agent 4% w/v sodium hydrosulphite) and 100% O2 gassed water. One probe was placed in the aortic inflow arterial line and the second, venous probe was placed in the right ventricular outflow tract inserted via the pulmonary artery. The oxygen content of arterial and venous perfusate was recorded as percentage O2 saturation. Atmospheric pressure (in millimetres of mercury) was measured daily, and MV˙O2 was then calculated according to the following equation:
MV˙O2=PB×Δ%O2100×SO2× CF Dry Wt in micromoles per minute per gram dry weight Where PB is atmospheric pressure (in millimetres of mercury), Δ%O2 is the arteriovenous difference in percentage O2 saturation, SO2 is the solubility of oxygen in Krebs‐Henseleit (KH) buffer = 1.22 ×10−3 μmol ml−1 mmHg−1 at BTSP (Chemnitius et al. 1985; Schenkman et al. 2003), CF is coronary flow (in millilitres per minute) and Dry Wt is the dry weight of the heart (in grams).
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2

Perfusion System for Liver Grafts

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The grafts were perfused using an original MP system (Figure 1) [9 ]. This system consists of the hepatic artery (HA) and portal vein (PV) perfusion circuits. Each circuit consists of a roller-type pump (MasterFlex7520-40; Cole-Parmer, IL, USA), an electrical flow meter (VN05; Aichi Tokei, Japan for PV; FD-SS02; Keyence, Osaka, Japan for HA), a ceramic capacitance pressure sensor (KL76; Nagano Keiki, Nagano, Japan), and a custom-made air trap. An oxygenator (HP0-06 H-C; Senko Medical Instrument, Tokyo, Japan) was installed in the circuit for the PV and HA. Two optical oxygen sensors (NeoFox; Ocean Optics, FL, USA) were installed to measure the oxygen concentration of the perfusate in the PV circuit. The perfusate temperature was controlled by a heat exchanger and ice-cold water. The flow rate of the PV was 0.22 mL/min/g and HA was 0.06 mL/min/g. The oxygen consumption (mg/min/100 g liver) of the organ was calculated as normalized values with the mass of the organ (mg/min/100 g liver) from the difference in the oxygen concentration at the inlet port of the PV circuit and the outlet port positioned near the hepatic vein (HV).
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3

Oxygen Release Kinetics from GelMA-CPN Scaffolds

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To investigate the kinetics of oxygen release from GelMA-impregnated CPN-loaded scaffolds, oxygen-release experiments were conducted in hypoxic conditions with and without cells. To measure the percentage of dissolved oxygen in the media in which either cell-free or cell-seeded scaffolds are placed under hypoxia, 25 mg samples were placed in 24-well plates containing 1 mL of DMEM media. The dissolved oxygen was measured every 24 h for a period of 21 days. The oxygen level was maintained at 4–5% to study the release kinetics independent of atmospheric oxygen levels. To achieve this, a hypoxia chamber from STEMCELL Technologies in Vancouver, Canada was used in accordance with the manufacturer’s instructions for setting up the hypoxia. Catalase (1 mg/mL), an enzyme that increases the conversion efficiency of H2O2 to water and oxygen was used in the media. The oxygen levels were measured using a an optical oxygen sensing probe (NeoFox, Ocean Optics, FL, USA).
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Real-time Arterial Oxygen Monitoring

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To assess the arterial partial pressure of oxygen (PaO2) in real-time, we used a calibrated ruthenium-tipped oxygen-sensing probe (Foxy AL300, OceanOptics, Dunedin, USA) that was advanced to the ascending aorta. The PO2 probe was connected via a fiberglass cable to a server unit (NeoFox, OceanOptics, Dunedin, USA). This PO2 measurement based on the principle of fluorescence quenching of oxygen by the multi-frequency phase fluorimetry (MFPF) method has been previously published [26 (link)]. PO2 values were digitally sampled with a temporal resolution of 10 Hz and stored on a personal computer.
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5

Perfusion System for Organ Grafts

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The grafts were perfused using an original MP system (Fig 1) [15 ]. This system consists of the hepatic artery (HA) and portal vein (PV) perfusion circuits. Each circuit consists of a roller-type pump (MasterFlex7520-40; Cole-Parmer, Bunker Court Vernon Hills, IL, USA), an electrical flow meter (VN05; Aichi Tokei, Japan for PV; FD-SS02, Keyence, Osaka, Japan for HA), a ceramic capacitance pressure sensor (KL76; Nagano Keiki, Nagano, Japan), and a custom-made air trap. An oxygenator (HP0-06 H-C; Senko Medical Instrument, Tokyo, Japan) was installed in the circuit for the PV and HA. Two optical oxygen sensors (NeoFox; Ocean Optics, Seattle, FL, USA) were installed to measure the oxygen concentration of the perfusate in the PV circuit. The temperature of the perfusate was controlled by a heat exchanger and ice-cold water. The flow rate of the PV was 0.22 mL/min/g (liver) and that of the HA was 0.06 mL/min/g (liver).
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6

Electrochemical Characterization Techniques

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Cyclic voltammetry (CV) and controlled potential electrolysis (CPE) measurements were performed under air on a general purpose potentiostat (BioLogic SP-150). A standard three-electrode setup was used including an ITO working electrode layered by method (A), Pt spring auxiliary electrode (∼7 cm2) and Ag/AgCl (3 M KCl, 0.2 V vs. SHE) reference electrode. The cell was equipped with a pH microelectrode (Mettler-Toledo) or a fluorescent O2 sensor (Ocean Optics NeoFox) through slot with o-ring.
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7

Photoelectrochemical Oxygen Measurement

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PEC measurements were performed in a three-electrode glass cell with a quartz window containing an aqueous solution of 1 M Na2SO4. Pt foil was used as the counter electrode and Ag/AgCl as the reference electrode. A 300-W Xenon lamp was used as the light source. A long-pass filter (>420 nm) was used to obtain visible light for PEC measurement. The fluorescence-based O2 sensor (Neofox, Ocean Optics) was used to test the dissolved oxygen in reaction solution. An N2-gas was used to purge the O2 of reaction solution before illumination.
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8

Continuous Arterial PaO2 Monitoring

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A ruthenium-covered probe was inserted via the femoral artery introducer (Foxy-AL300, Ocean Optics, USA) as previously reported [13 (link), 14 (link)]. The tip of the probe is covered with ruthenium-based fluorescent molecules, whose fluorescence is quenched by the presence of molecular oxygen. A fiber optic bundle sends blue LED light to the sensor and the resulting fluorescence is relayed back through the bundle to the detector (NeoFox, Ocean Optics, USA). The decay profile of the fluorescent molecules changes in the presence of molecular oxygen, and arterial PaO2 is calculated automatically by the dedicated software with a time resolution of up to 10 Hz.
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9

Oxygen Consumption Measurement Protocol

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Oxygen consumption was measured as described [37 (link),40 (link)]. Briefly, cells were grown to an A600nm of 0.6 in YPD or YPA medium and 9 x 106 cells were harvested by centrifugation. Cells were resuspended in a buffer containing 10 mM HEPES, 25 mM K2HPO4, pH 7.0 and incubated at 30°C in an oxygen consumption chamber (Instech Laboratories, Inc.) connected to a NeoFOX fluorescence-sensing detector using NeoFOX software (Ocean Optics, Inc.). Results were calculated as pmol O2/106cell/sec and expressed as percentages of the wild-type value. The oxygen consumption rate in wild-type cells (WT) grown in YPD medium was 5.08 pmol/106 cells/second and was set as 100%.
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10

Rapid In Vitro Blood Oxygen Sensing

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We investigated the capacity of an in-house, custom-built fibre optic PO2 sensor to detect rapid PO2 oscillations in blood in vitro. This sensor is made by coating the end section of a silica fibre with a Pt(II) doped polymer sensing material, poly(methyl methacrylate) (PMMA). This PMMA sensor is based on the principle of fluorescence quenching of the platinum complex by oxygen, and is compatible with clinical application. Further technical details about the sensor have been reported previously (Chen et al., 2012a ). The Foxy-AL300 fibre optic PO2 sensor was used as a control for comparison with the PMMA sensor. Each sensor was calibrated in blood at 0 and 50 kPa before each experiment. The two sensors were connected to a phase measurement system (NeoFox, Ocean Optics, Dunedin, FL, USA), and interfaced to a computer through an A/D board sampling at 10 Hz (USB-6251, National Instruments, Austin, TX, USA). In order to compare our data with those reported in the literature (Baumgardner et al., 2002 (link), Shi et al., 2011 (link)), the AL300 sensor was also connected to a light intensity measurement system (USB 2000 spectrometer, Ocean Optics, Dunedin, FL, USA), interfaced to a computer through the A/D board. Data were recorded on a computer by means of a custom program (LabView, National Instruments, Austin, TX, USA).
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