2,5-Dioxopyrrolidin-1-yl 4-(pyren-1-yl)butanoate is an amine-reactive ester that has been widely used for coating carbon nanotube-based biosensors for the capture of antibodies and proteins.

[1]. Benvidi A, et al. Comparison of impedimetric detection of DNA hybridization on the various biosensors based on modified glassy carbon electrodes with PANHS and nanomaterials of RGO and MWCNTs. Talanta. 2016 Jan 15;147:621-7.
[2]. Tian J, et al. Biosensing platform based on graphene oxide via self-assembly induced by synergic interactions. Anal Biochem. 2014 Sep 1;460:16-21.
[3]. Kim, J.P., Lee, B.Y., Hong, S., et al. Ultrasensitive carbon nanotube-based biosensors using antibody-binding fragments. Anal. Biochem. 381(2), 193-198 (2008).
[4]. Karachevtsev, V.A., Stepanian, S.G., Glamazda, A.Y., et al. Noncovalent interaction of single-walled carbon nanotubes with 1-pyrenebutanoic acid succinimide ester and glucoseoxidase. J. Phys. Chem. 115(43), 21072-21082 (2011).

λmax: 234, 243, 265, 276, 326, 342 nm
Emission: 377; 397

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1. Chemically Functionalised Graphene FET Biosensor for the Label-free Sensing of Exosomes
A graphene field-effect transistor (gFET) was non-covalently functionalised with 1-pyrenebutyric acid N-hydroxysuccinimide ester and conjugated with anti-CD63 antibodies for the label-free detection of exosomes. Using a microfluidic channel, part of a graphene film was exposed to solution. The change in electrical properties of the exposed graphene created an additional minimum alongside the original Dirac point in the drain-source current (Ids) - back-gate voltage (Vg) curve. When phosphate buffered saline (PBS) was present in the channel, the additional minimum was present at a Vglower than the original Dirac point and shifted with time when exosomes were introduced into the channel. This shift of the minimum from the PBS reference point reached saturation after 30 minutes and was observed for multiple exosome concentrations. Upon conjugation with an isotype control, sensor response to the highest concentration of exosomes was negligible in comparison to that with anti-CD63 antibody, indicating that the functionalised gFET can specifically detect exosomes at least down to 0.1 μg/mL and is sensitive to concentration. Such a gFET biosensor has not been used before for exosome sensing and could be an effective tool for the liquid-biopsy detection of exosomes as biomarkers for early-stage identification of diseases such as cancer.
Reference: Sci Rep . 2019 Sep 26;9(1):13946. doi: 10.1038/s41598-019-50412-9.

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2. A novel electrochemical DNA biosensor based on a modified magnetic bar carbon paste electrode with Fe3O4NPs-reduced graphene oxide/PANHS nanocomposite
In this study, we have designed a label free DNA biosensor based on a magnetic bar carbon paste electrode (MBCPE) modified with nanomaterial of Fe3O4/reduced graphene oxide (Fe3O4NP-RGO) as a composite and 1- pyrenebutyric acid-N- hydroxysuccinimide ester (PANHS) as a linker for detection of DNA sequences. Probe (BRCA1 5382 insC mutation detection) strands were immobilized on the MBCPE/Fe3O4-RGO/PANHS electrode for the exact incubation time. The characterization of the modified electrode was studied using different techniques such as scanning electron microscopy (SEM), infrared spectroscopy (IR), vibrating sample magnetometer (VSM), electrochemical impedance spectroscopy (EIS) and cyclic voltammetry methods. Some experimental parameters such as immobilization time of probe DNA, time and temperature of hybridization process were investigated. Under the optimum conditions, the immobilization of the probe and its hybridization with the target DNA (Complementary DNA) were tested. This DNA biosensor revealed a good linear relationship between ∆Rct and logarithm of the complementary target DNA concentration ranging from 1.0×10(-18)molL(-1) to 1.0×10(-8)molL(-1) with a correlation coefficient of 0.9935 and a detection limit of 2.8×10(-19)molL(-1). In addition, the mentioned biosensor was satisfactorily applied for discriminating of complementary sequences from non-complementary sequences. The constructed biosensor (MBCPE/Fe3O4-RGO/PANHS/ssDNA) with high sensitivity, selectivity, stability, reproducibility and low cost can be used for detection of BRCA1 5382 insC mutation.
Reference: Mater Biol Appl . 2016 Nov 1;68:1-8. doi: 10.1016/j.msec.2016.05.056.

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3. Detection of Alpha-Fetoprotein in Hepatocellular Carcinoma Patient Plasma with Graphene Field-Effect Transistor
The detection of alpha-fetoprotein (AFP) in plasma is important in the diagnosis of hepatocellular carcinoma (HCC) in humans. We developed a biosensor to detect AFP in HCC patient plasma and in a phosphate buffer saline (PBS) solution using a graphene field-effect transistor (G-FET). The G-FET was functionalized with 1-pyrenebutyric acidN-hydroxysuccinimide ester (PBASE) for immobilization of an anti-AFP antibody. AFP was detected by assessing the shift in the voltage of the Dirac point (ΔVDirac) after binding of AFP to the anti-AFP-immobilized G-FET channel surface. This anti-AFP-immobilized G-FET biosensor was able to detect AFP at a concentration of 0.1 ng mL-1in PBS, and the detection sensitivity was 16.91 mV. In HCC patient plasma, the biosensor was able to detect AFP at a concentration of 12.9 ng mL-1, with a detection sensitivity of 5.68 mV. The sensitivity (ΔVDirac) depended on the concentration of AFP in either PBS or HCC patient plasma. These data suggest that G-FET biosensors could have practical applications in diagnostics.
Sensors (Basel) . 2018 Nov 19;18(11):4032. doi: 10.3390/s18114032.

C24H19NO4

385.4120

385.131

C, 74.79; H, 4.97; N, 3.63; O, 16.60

114932-60-4

130767

Typically exists as light green to green solids at room temperature

1.4±0.1 g/cm3

590.9±43.0 °C at 760 mmHg

132-136ºC(lit.)

311.2±28.2 °C

0.0±1.7 mmHg at 25°C

1.739

3.77

0

4

6

29

660

0

O(C(C([H])([H])C([H])([H])C([H])([H])C1C([H])=C([H])C2C([H])=C([H])C3C([H])=C([H])C([H])=C4C([H])=C([H])C=1C=2C4=3)=O)N1C(C([H])([H])C([H])([H])C1=O)=O

YBNMDCCMCLUHBL-UHFFFAOYSA-N

InChI=1S/C24H19NO4/c26-20-13-14-21(27)25(20)29-22(28)6-2-3-15-7-8-18-10-9-16-4-1-5-17-11-12-19(15)24(18)23(16)17/h1,4-5,7-12H,2-3,6,13-14H2

(2,5-dioxopyrrolidin-1-yl) 4-pyren-1-ylbutanoate

114932-60-4; 1-Pyrenebutyric acid N-hydroxysuccinimide ester; 2,5-DIOXOPYRROLIDIN-1-YL 4-(PYREN-1-YL)BUTANOATE; N-Hydroxysuccinimidyl Pyrenebutanoate; 97427-71-9; Pyrenebutyric acid NHS ester; 1-Succinimidyl-3'-pyrenebutyrate; 1-Pyrenebutanoic acid, 2,5-dioxo-1-pyrrolidinyl ester;

2934.99.9001

Powder      -20°C    3 years

                     4°C     2 years

In solvent   -80°C    6 months

                  -20°C    1 month

Room temperature (This product is stable at ambient temperature for a few days during ordinary shipping and time spent in Customs)

DMSO : ≥ 100 mg/mL (~259.46 mM)
DMF: ~15 mg/ml

Solubility in Formulation 1: ≥ 2.5 mg/mL (6.49 mM) (saturation unknown) in 10% DMSO + 40% PEG300 + 5% Tween80 + 45% Saline (add these co-solvents sequentially from left to right, and one by one), clear solution.
For example, if 1 mL of working solution is to be prepared, you can add 100 μL of 25.0 mg/mL clear DMSO stock solution to 400 μL PEG300 and mix evenly; then add 50 μL Tween-80 to the above solution and mix evenly; then add 450 μL normal saline to adjust the volume to 1 mL.
Preparation of saline: Dissolve 0.9 g of sodium chloride in 100 mL ddH₂ O to obtain a clear solution.

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Solubility in Formulation 2: ≥ 2.5 mg/mL (6.49 mM) (saturation unknown) in 10% DMSO + 90% Corn Oil (add these co-solvents sequentially from left to right, and one by one), clear solution.
For example, if 1 mL of working solution is to be prepared, you can add 100 μL of 25.0 mg/mL clear DMSO stock solution to 900 μL of corn oil and mix evenly.

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 (Please use freshly prepared in vivo formulations for optimal results.)