Hormones within very low levels regulate and control the activity of specific cells and organs of the human body. Hormone imbalance can cause many diseases. Therefore, hormone detection tools have been developed, particularly over the last decade. Peptide hormones have a short half-life, so it is important to detect them within a short time. In this study, we report two types of peptide hormone sensors using human hormone receptor-carrying nanovesicles and graphene field-effect transistors (FETs). Parathyroid hormone (PTH) and glucagon (GCG) are peptide hormones present in human blood that act as ligands to G protein-coupled receptors (GPCRs). In this paper, the parathyroid hormone receptor (PTHR) and the glucagon receptor (GCGR) were expressed in human embryonic kidney-293 (HEK-293) cells, and were constructed as nanovesicles carrying the respective receptors. They were then immobilized onto graphene-based FETs. The two hormone sensors developed were able to detect each target hormone with high sensitivity (ca. 100 fM of PTH and 1 pM of GCG). Also, the sensors accurately recognized target hormones among different types of peptide hormones. In the development of hormone detection tools, this approach, using human hormone receptor-carrying nanovesicles and graphene FETs, offers the possibility of detecting very low concentrations of hormones in real-time.
Hormones in very low concentration control and regulate the activity of certain cells and organs in the human body1. Numerous diseases, such as osteoporosis, cardiovascular, adenoma, hyperplasia, and cancer, are related to hormone imbalance2,3,4,5,6,7. Therefore, significant efforts have been made over the last decade in the development of tools to detect hormones. Well-established detection methods for hormone detection are normally based on immunometric assays8,9,10. However, they have the limitations of selectivity, sensitivity, and time-consuming problems for diagnosis and health screening. Peptide hormones have a short half-life, so in order to detect them, they must be detected within a short time after taking them from the body11. In the case of hormones with short half-life, real-time detectable sensors are needed.
Parathyroid hormone (PTH) is also called parathormone, and secreted in parathyroid glands. This peptide hormone plays an important role in the regulation of bone and mineral metabolism. It is secreted when the concentration of calcium in the blood is low, causing the calcium to dissolve into the blood from the osteoclasts. It is known that adenoma, hyperplasia, and cancer cause high concentration of PTH in blood. PTH in the human body acts as a ligand to the parathyroid hormone receptor (PTHR), a type of GPCR. PTH is an 84-amino acid peptide hormone, and its half-life is (2–4) min12. PTH has been measured by RadioImmunoAssay (RIA) and Enzyme-Linked ImmunoasSAy (ELISA)13,14,15. Recently, the most common method used is ELISA, which has a detection limit of 3 pM. However, this methods require pretreatment and reaction with reagents. Moreover, because PTH exists in various fragments in the blood, it is necessary to measure it using different antibodies for each fragment. As the degree of response in vivo varies depending on the site or length of the fragments, it is necessary to develop a method of measuring that is similar to a real biological system. Glucagon (GCG) is also a peptide hormone produced in the alpha cells of the pancreas, and also acts as a ligand to the glucagon receptor (GCGR). This hormone regulates the concentration of glucose in the bloodstream, as opposed to insulin16. When the glucose level falls too low, glucagon is secreted from the pancreas to convert glycogen into glucose. This hormone is also related to pancreatic tumors. The tumors can cause abnormally high glucagon level. GCG is a 28-amino-acid peptide hormone, and its half-life is (3–6) min. GCG has also been measured by RIA and ELISA (limit of detection: 3 nM) methods. This method also has the same limitations as the above-mentioned PTH measurement method. Therefore, the key factor is detecting peptide hormones from the body with high selectivity, and as soon as possible.
The GPCRs can recognize target substances in the body. Therefore, the GPCR can be applied to a sensor that can detect a target substance with high selectivity17,18,19,20. In our previous research, FET biosensors using human GPCRs have demonstrated the ability to successfully identify target substances21,22,23,24,25,26,27,28,29,30. In particular, sensors using human PTHR has enabled biosystem-like measurements by identifying different signals for different peptide hormone fragments28. GPCR-carrying nanovesicle-based FET sensors showed high performance real-time detection22,31,32. They were able to detect target substances with high sensitivity and selectivity. Also, usage of FET sensors showed highly rapid response (on a time scale of less than 1s). Among transducer materials, graphene has been useful, because it can provide excellent electrical and optical properties33. In addition, graphene provides excellent sensitivity, stability and a rapid response34,35,36,37. Previous study has shown that biosensor using graphene-FET and human GPCR-carrying nanovesicles exhibit excellent sensor characteristics38. Here, two kinds of hormone sensors were successfully demonstrated to detect PTH and GCG using graphene FET sensors fabricated with PTHR- and GCGR-carrying nanovesicles. PTHR and GCGR were expressed in HEK-293 cells, and then nanovesicles were produced. Each of these receptor-carrying nanovesicles was then immobilized on a graphene-based FET sensor, and constructed with one or other of the two hormone sensors. These sensors can be developed as a tool that can enable diagnosis by detecting hormones. They will also be useful as screening tools to discover alternative molecules.
Construction of human hormone receptor-carrying nanovesicles and functional characterization of hormone receptors
HEK-293 cells were transfected with pDsRed-N1 containing human PTHR and GCGR, and then stable cell lines were constructed. After, the hormone receptor-carrying nanovesicles were constructed as shown in Fig. 1. Detailed processes can be found in our previous studies31,38,39.
Since PTHR and GCGR genes are inserted in the pDsRed N-1 vector, expression in HEK-293 cells can be easily confirmed by fluorescence microscopy. Figure 2a shows the expression of the hormone proteins tagged with the DsRed protein as a fluorescence image. Figure 2a(i) shows that PTHR with DsRed exhibits red fluorescence and was well expressed in cells. Figure 2a(ii) also shows the appearance of GCGR with DsRed can be confirmed by red fluorescence. The left images are fluorescence microscope images, and the right images are cell images obtained by applying the bright field. Comparison of fluorescence images with bright field images indicate that the expression rate is 80–90%. Calcium signal analysis was performed to confirm the function of these expressed hormone receptors (Fig. 2b). Figure 2b(i) shows that the relative fluorescence unit (340/380 nm) increases with increasing intracellular calcium concentration when stimulated with 1 μM PTH to cells expressing PTHR. Figure 2b(ii) also shows that the signals are increased when GCGR-expressed cells were stimulated with 1 μM GCG. These results confirmed that the two receptors, GPCRs along the cAMP signaling pathway, are stimulated by target hormones to generate intracellular signals which cause intracellular calcium influx. Also, this indicates that the hormone receptor-expressing cells with the accessory protein DsRed are able to carry out intracellular signaling normally.
Then stable cell lines were produced to increase the number of receptors present on the nanoveislce. The hormone receptor cells were treated with cytochalasin B, which destabilizes the cell membrane and makes the cell membrane unstable, and then gently agitated. Hormone receptor-carrying nanovesicles were produced by budded off from receptor-expressing HEK-293 cells. The constructed nanovesicles have not only receptors but also G proteins and other intracellular signalling machineries. To investigate whether the produced nanovesicles carrying hormone receptors are stimulated by the respective hormones and have intracellular signal transduction into the nanovesicles, calcium signal analysis was performed. Figure 2c(i) shows that the PTHR-carrying nanovesicles exhibit signals when stimulated with 1 μM PTH (blue line), compared to nanovesicles made with HEK-293 that are not expressed at all (black line). Figure 2c(ii) also shows the same content as the calcium signals for the GCGR-carrying nanovesicles (red line). The red line pick to 0.02 at around 25 seconds, seems to be an artifact caused by injection of GCG, an effect often observed in experiments. The actual signal is correct to see 0.01 except for artifacts. These results indicate that the nanovesicles maintain the intrinsic function of hormone receptor cell signaling. This indicates that the change in signal is due to a calcium influx from outside of the cell or nanovesicle. However, the calcium signal does not fully recover to baseline in the case of nanovesicles. This is perhaps due to a lack of ATP, ion pumps and calmodulin that may prevent nanovesicles from discharging calcium ion22,40,41.
Fabrication and characterization of hormone sensors
Figure 3a shows a schematic of the immobilization of the nanovesicles on graphene electrode (GE). Based on our previous research38, the CVD-grown graphene was in the form of a single layer. Therefore, the thickness of the graphene channel was estimated to be about 0.8 nm, which is the thickness of a single layer of graphene. The length and width of the graphene pattern was about 50 µm × 50 µm and this graphene pattern was utilized as the channel region. Then, proteins of the nanovesicles interacted with the succinimidyl groups of the PSE as the linker molecules, forming stable peptide bonding. To remove excess PSE, the GEs were washed three times with pure methanol before immobilization of the nanovesicles. To visualize the immobilization of the nanovesicles on the graphene surface, field-emission scanning electron microscopy (FE-SEM) measurement was carried out. Figure 3b shows the FE-SEM image of the nanovesicles immobilized on graphene. This shows that the diameter of the nanovesicles produced is about (100 to 150) nm. In order to utilize the electrical characteristics of the nanovesicle-immobilized graphene-FET configuration, current–voltage (I–V) measurements were performed (Fig. 3c). Figure 3c shows the changes in the I–V values before and after PSE treatment, and nanovesicles immobilization on the surface of the GE channel. Although the dI/dV value decreased moderately after nanovesicle immobilization, the I–V relationship remained linear. These results indicate that hormone sensors can maintain reliable electrical contacts, and that interaction between target hormones and nanovesicles can be detected by observing changes in current. In addition, the immobilization of the nanovesicle was indirectly proven through changes in the I–V values. Figure 3d shows the output curves of the hormone sensor in various Vg ranges from (0.1 to −0.7) V. The drain-source current (Isd) increases negatively according to the negatively increasing Vg. Also, Fig. 3e displays the Isd–Vg transfer curve at a constant drain voltage (a constant value of Vsd = –100 mV). Vg was applied from –1 to 1.5 V at a sweep rate of –50 mV. Isd increased as Vg was reduced from 0.35 to –1.0 V, which corresponds to the output characteristics seen in Fig. 3d. The result shows that the FET-graphene sensor maintains p-type behavior under our experimental conditions. Moreover, the linear properties (ohmic contact) of the I–V curves were maintained under the various Vg, implying that the electrostatic gating effect can be the major influence leading to the current changes in the hormone sensor.
Real-time responses of hormone sensors
To evaluate the sensing properties of the hormone receptor-carrying nanovesicle-based FET type hormone sensors, phosphate-buffered solution (PBS) containing 2 mM Ca2+ was used, which helped maintain effective gate regulation. The real-time responses of the liquid-ion gated FET sensors were measured at the p-type region. Graphene-based sensors presented ambipolar (p-type or n-type) properties, but exhibited a more sensitive and stable performance in the p-type region, due to the adsorption of oxygen from water or air. The main function of hormone receptor-carrying nanovesicles is to bind to hormone molecules, and signals derived from binding events activated the cAMP pathway of nanovesicles42. Activation of the Ca2+ channel induces influx of Ca2+ into the nanovesicles, which accumulates the potential of the nanovesicles immobilized on the graphene-FET. The size of the nanovesicles on the surface of the graphene is 100 nm. For this size, a screening effect dominates while charge detection is severely hampered43. However, Ca2+ ions flew into the nanovesicles after ligand binding. The accumulated Ca2+ caused a positive gate effect on the surface of the hormone sensor. The current decreased when the gate voltage was positively increased, as shown in Fig. 3d. Therefore, we can say the positive gate effect reduces the current of the p-type graphene -FET. This type of current decrease was demonstrated with a shift of the Dirac point of our group research27. In addition, our previous study showed that FET sensors could not detect signals when using buffer without Ca2+ or when Ca2+ channel blocker (MgCl2) was added to normal sensing buffer31. Moreover, the signal tended to increase when the concentration of Ca2+ in the buffer was increased44. These results support the conclusion that the signal change is caused by Ca2+ influx in the nanovesicles.
Figure 4a,c show the real-time responses of the PTH sensor (Fig. 4a) and GCG sensor (Fig. 4c) observed by monitoring the Isd after loading various concentrations of PTH and GCG. Negatively recorded currents can be explained by the reduction of the major carrier (hole) by the Ca2+ induction accumulated in the graphene. The specific binding of hormone to receptors on the nanovesicle promotes the activity of the calcium ion channel, allowing positive charges to be generated in the liquid ion gate dielectric near the graphene surface. As a result, carriers in the graphene channel, which are charged positively, decreased, resulting in a negative increase in current. From this detection mechanism, the nanovesicle-based hormone sensors have very sensitive response, but there is no significant signal from the pristine GE as control experiment. The minimum detection levels (MDL) of the PTH and GCG sensors were 100 fM and 1 pM, respectively, using the PTHR-carrying nanovesicles and the GCGR-carrying nanovesicles. The sensing signal immediately decreased upon the addition of PTH or GCG, indicating that the hormone sensor featured rapid response time of less than 1 second. The instantaneous current changes were monitored over a wide range of PTH/GCG concentrations (100 fM to 10 nM/1 pm to 10 nM). When the hormone sensor was interacted with higher concentrations of the hormones, the Isd value gradually decreased.
Figure 4b,d show highly selective responses of the hormone sensors to other peptide hormones. With the addition of non-target hormone molecules, including glucagon-like peptide-1 (GLP-1), secretin (SEC) and PTH or GCG, no significant change in Isd was monitored, but the current changes were clearly observed by the injection of PTH 100 fM or GCG 1 pM. These results indicate that the hormone sensors exhibit high selectivity, because hormone receptors on the nanovesicles have high specificity for the target ligand hormone.
In summary, two kinds of liquid-ion gated FET type hormone sensors were successfully demonstrated using graphene-FET and human hormone receptor-carrying nanovesicles. The electric field induction responses from the nanovesicle-based hormone sensors showed high detection performance at unprecedented low concentrations (ca. 100 fM of PTH and 1 pM of GCG). In addition, hormone sensors based on hormone receptor-carrying nanovesicles were able to distinguish hormones from non-target molecules. All reactions were detected within 1 second, and real-time detection was possible. This method seems to be able to measure hormones in a much faster and more accurate way than conventional peptide hormone detection methods. Therefore, these FET-type hormone sensors using human hormone receptor-carrying nanovesicles can be used as transducers for high-performance sensor applications, leading to a rapid and accurate methodology for the diagnosis and management of diseases.
Construction of hormone receptor-carrying nanovesicles
HEK-293 cells were cultured in Dulbecco’s modified Eagle medium (DMEM, Welgene, Republic of Korea), supplemented with 10% fetal bovine serum and 1% penicillin-streptomycin (Gibco, USA) at 37 °C under 5% CO2. HEK-293 cells were transfected with pDsRed-N1 containing human PTHR and GCGR, using Lipofectamine3000 (Invitrogen, USA), according to the manufacturer’s instructions. After the transfection, the expression of PTHR and GCGR was confirmed by fluorescence microscopy, and then cells were cultured for 1 day, and transferred to the media containing G-418 (1 mg/ml) for selection. After 1 week, G-418 resistant cell colonies were separately picked up, and cultured in fresh medium containing G-418. The cells stably expressing hormone receptors were suspended in serum-free DMEM containing cytochalasin B (20 μg/ml, Sigma, USA), and incubated at 37 °C with 300 rpm agitation for 20 min. Nanovesicles were separated from cells and cell debris by centrifugation (1,000 g, 5 min for cells, 2,000 g, 20 min for cell debris) in an Eppendorf tube, and collected by centrifugation at 12,000 g for 30 min. The nanovesicles were finally resuspended in Dulbecco’s phosphate buffered saline (DPBS, Gibco, USA). The produced nanovesicles were used immediately, or stored at –80 °C for subsequent experiments.
Intracellular calcium assay
For calcium signalling analysis, stable cell lines expressing PTHR and GCGR were incubated in Ringer’s solution (140 mM NaCl, 1 mM MgCl2, 1.8 mM CaCl2, 5 mM KCl, 5 mM glucose, and 10 mM HEPES (pH 7.4)) containing 10 mM Fura-2/AM (Invitrogen, USA) for 30 min at 37 °C. After incubation, the cells were washed several times with Ringer’s solution without Fura-2/AM, and the cleavage of the AM ester group was followed by incubation for 1 h at 37 °C. Using a spectrofluorophotometer (Tecan, Switzerland), the fluorescence signal upon the addition of hormone was measured at 510 nm by dual excitation at (340 and 380) nm. For calcium analysis of nanovesicles, nanovesicles carrying PTHR and GCGR were generated from Fura2-AM loaded cells. Next, 96-wells plates were treated with poly-D-lysine, and the nanovesicle solutions were then immobilized on the plates at 37 °C for 2 h. The calcium signals upon the addition of hormones were measured by the same processor of calcium signalling analysis.
Fabrication of graphene electrode
Single-layer graphene was fabricated using a chemical vapor deposition (CVD) method, and prepared on Cu foil (25 μm-thick). The size of the graphene channel was about 50 µm × 50 µm. The fabrication of GEs method is the same as previous study45.
Immobilization of hormone receptor-carrying nanovesicles on GE
The above-prepared GEs were dipped in 1 mM 1-pyrenebutanoic acid N-hydroxysuccinimidyl ester (PSE) solution in methanol for 30 min at ambient temperature. To remove excess PSE, the GEs were washed three times with pure methanol. The PSE was introduced onto the graphene through π–π interaction between the surface of the graphene and the pyrene groups of the PSE. To build the nanovesicle-based hormone sensor, a 5 μl droplet of nanovesicle solution (1 mg/mL of total protein concentration) was used for the immobilization and placed on PSE treated GEs for 3 h. The proteins of the nanovesicle interacted with the succinimidyl groups of the PSE, resulting in chemically stable peptide bonds. Finally, the nanovesicle-immobilized GEs were rinsed with distilled water.
Glass chamber (200 μl Volume) was designed and placed on GE and filled with pH 7.4 DPBS containing 2 mM of CaCl2. The current change was observed and normalized as ΔI/I0 = (I − I0)/I0. Where I0 is the initial current and I is the measured real-time current.
Neave, N. Hormones and behaviour: a psychological approach. (Cambridge University Press, 2007).
Lübke, K., Schillinger, E. & Töpert, M. Hormone receptors. Angew. Chem. Int. Ed. 15, 741–748 (1976).
Schauer, R. The mode of action of hormones. Angew. Chem. Int. Ed. 11, 7–16 (1972).
Hodsman, A. B. et al. Parathyroid hormone and teriparatide for the treatment of osteoporosis: a review of the evidence and suggested guidelines for its use. Endocr. Rev 26, 688–703 (2005).
Hagström, E. et al. Plasma parathyroid hormone and the risk of cardiovascular mortality in the community. Circulation 119, 2765–2771 (2009).
Mannstadt, M., Juppner, H. & Gardella, T. J. Receptors for PTH and PTHrP: their biological importance and functional properties. Am. J. Physiol. Renal Physiol. 277, F665–F675 (1999).
Downs, T. M., Burton, D. W., Araiza, F. L., Hastings, R. H. & Deftos, L. J. PTHrP stimulates prostate cancer cell growth and upregulates aldo–keto reductase 1C3. Cancer Lett. 306, 52–59 (2011).
Zafrani, B. et al. High sensitivity and specificity of immunohistochemistry for the detection of hormone receptors in breast carcinoma: comparison with biochemical determination in a prospective study of 793 cases. Histopathology 37, 536–545 (2000).
Hsu, S.-M., Raine, L. & Fanger, H. A comparative study of the peroxidase-antiperoxidase method and an avidin-biotin complex method for studying polypeptide hormones with radioimmunoassay antibodies. Am. J. Clin. Pathol. 75, 734–738 (2016).
La Rosa, S., Celato, N., Uccella, S. & Capella, C. Detection of gonadotropin-releasing hormone receptor in normal human pituitary cells and pituitary adenomas using immunohistochemistry. Virchows Archiv 437, 264–269 (2000).
Bieglmayer, C., Prager, G. & Niederle, B. Kinetic analyses of parathyroid hormone clearance as measured by three rapid immunoassays during parathyroidectomy. Clin. Chem. 48, 1731–1738 (2002).
Souberbielle, J.-C. P., Roth, H. & Fouque, D. P. Parathyroid hormone measurement in CKD. Kidney Int. 77, 93–100 (2010).
Arnaud, C. D., Tsao, H. S. & Littledike, T. Radioimmunoassay of human parathyroid hormone in serum. J. Clin. Invest. 50, 21–34 (1971).
Hosseinpanah, F., Heibatollahi, M., Moghbel, N., Asefzade, S. & Azizi, F. The effects of air pollution on vitamin D status in healthy women: a cross sectional study. BMC Public Health 10, 519 (2010).
Schepky, A. G., Bensch, K. W., Schulz‐Knappe, P. & Forssmann, W. G. Human hemofiltrate as a source of circulating bioactive peptides: determination of amino acids, peptides and proteins. Biomed. Chromatogr. 8, 90–94 (1994).
Voet, D. & Voet, J. G. Biochemistry, 1995. J. Wiley & Sons, ISBN X 47158651 (1995).
Lee, S. H., Ko, H. J. & Park, T. H. Real-time monitoring of odorant-induced cellular reactions using surface plasmon resonance. Biosens. Bioelectron 25, 55–60 (2009).
Lee, S. H., Jun, S. B., Ko, H. J., Kim, S. J. & Park, T. H. Cell-based olfactory biosensor using microfabricated planar electrode. Biosens. Bioelectron 24, 2659–2664 (2009).
Ko, H. J. & Park, T. H. Dual signal transduction mediated by a single type of olfactory receptor expressed in a heterologous system. Biol. Chem 387, 59–68 (2006).
Lee, S. H. & Park, T. H. Recent advances in the development of bioelectronic nose. Biotechnol. Bioprocess Eng. 15, 22–29 (2010).
Song, H. S. et al. Human Taste Receptor-Functionalized Field Effect Transistor as a Human-Like Nanobioelectronic Tongue. Nano Lett. 13, 172–178 (2012).
Song, H. S. et al. Bioelectronic tongue using heterodimeric human taste receptor for the discrimination of sweeteners with human-like performance. ACS Nano 8, 9781–9789 (2014).
Son, M., Kim, D., Ko, H. J., Hong, S. & Park, T. H. A Portable and Multiplexed Bioelectronic Sensor using Human Olfactory and Taste Receptors. Biosens. Bioelectron 87, 901–907 (2017).
Park, S. J. et al. Ultrasensitive Flexible Graphene based Field-Effect Transistor (FET)-Type Bioelectronic Nose. Nano Lett. 12, 5082–5090 (2012).
Lee, S. H. et al. Mimicking The Human Smell Sensing Mechanism with An Artificial Nose Platform. Biomaterials 33, 1722–1729 (2012).
Lee, S. H., Jin, H. J., Song, H. S., Hong, S. & Park, T. H. Bioelectronic Nose with High Sensitivity and Selectivity Using Shemically Functionalized Carbon Nanotube Combined with Human Olfactory Receptor. J. Biotechnol. 157, 467–472 (2012).
Kwon, O. S. et al. An Ultrasensitive, Selective, Multiplexed Superbioelectronic Nose That Mimics The Human Sense of Smell. Nano Lett. 15, 6559–6567 (2015).
Kwon, O. S. et al. Ultrasensitive and selective recognition of peptide hormone using close-packed arrays of hPTHR-conjugated polymer nanoparticles. ACS Nano 6, 5549–5558 (2012).
Kim, T. H. et al. “Bioelectronic Super-Taster” Device Based on Taste Receptor-Carbon Nanotube Hybrid Structures. Lab on a Chip 11, 2262–2267 (2011).
Kim, B. et al. Highly selective and sensitive detection of neurotransmitters using receptor-modified single-walled carbon nanotube sensors. Nanotechnology 24, 285501 (2013).
Jin, H. J. et al. Nanovesicle-Based Bioelectronic Nose Platform Mimicking Human Olfactory Signal Transduction. Biosens. Bioelectron 35, 335–341 (2012).
Park, J. et al. A bioelectronic sensor based on canine olfactory nanovesicle–carbon nanotube hybrid structures for the fast assessment of food quality. Analyst 137, 3249–3254 (2012).
Kwon, O. S. et al. Flexible FET-Type VEGF Aptasensor based on Nitrogen-Doped Graphene Converted from Conducting Polymer. ACS Nano 6, 1486–1493 (2012).
Mohanty, N. & Berry, V. Graphene-based single-bacterium resolution biodevice and DNA transistor: interfacing graphene derivatives with nanoscale and microscale biocomponents. Nano Lett. 8, 4469–4476 (2008).
Schedin, F. et al. Detection of individual gas molecules adsorbed on graphene. Nature materials 6, 652 (2007).
An, J. H., Park, S. J., Kwon, O. S., Bae, J. & Jang, J. High-Performance Flexible Graphene Aptasensor for Mercury Detection in Mussels. ACS Nano 7, 10563–10571 (2013).
Kwon, O. S. et al. Large‐Scale Graphene Micropattern Nano‐Biohybrids: High‐Performance Transducers for FET‐Type Flexible Fluidic HIV Immunoassays. Adv. Mater. 25, 4177–4185 (2013).
Ahn, S. R. et al. Duplex Bioelectronic Tongue for Sensing Umami and Sweet Tastes Based on Human Taste Receptor Nanovesicles. ACS Nano 10, 7287–7296 (2016).
Lim, J. H. et al. Nanovesicle‐Based Bioelectronic Nose for the Diagnosis of Lung Cancer from Human Blood. Adv. Healthc. Mater 3, 360–366 (2014).
Dong, H., Dunn, J. & Lytton, J. Stoichiometry of the cardiac Na+/Ca 2+ exchanger NCX1. 1 measured in transfected HEK cells. Biophys. J. 82, 1943–1952 (2002).
Liu, M., Chen, T. Y., Ahamed, B., Li, J. & Yau, K. W. Calcium-calmodulin modulation of the olfactory cyclic nucleotide-gated cation channel. Science 266, 1348–1354 (1994).
Park, S. J. et al. Human Dopamine Receptor Nanovesicles for Gate-Potential Modulators in High-Performance Field-Effect Transistor Biosensors. Sci. Rep. 4 (2014).
Matsumoto, A. & Miyahara, Y. Current and emerging challenges of field effect transistor based bio-sensing. Nanoscale 5, 10702–10718 (2013).
Lim, J. H., Oh, E. H., Park, J., Hong, S. & Park, T. H. Ion-channel-coupled receptor-based platform for a real-time measurement of G-protein-coupled receptor activities. ACS Nano. 9, 1699–1706 (2015).
Ahn, S. R. et al. High-performance bioelectronic tongue using ligand binding domain T1R1 VFT for umami taste detection. Biosens. Bioelectron 117, 628–636 (2018).
This study was supported by the National Research Foundation, funded by the Korean government (MSIT) (2018R1A2B3004498), and also by the KIST Institutional Program (No. 2E28390).
The authors declare no competing interests.
Publisher’s note Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
About this article
Cite this article
Ahn, S.R., An, J.H., Lee, S.H. et al. Peptide hormone sensors using human hormone receptor-carrying nanovesicles and graphene FETs. Sci Rep 10, 388 (2020). https://doi.org/10.1038/s41598-019-57339-1