Three of our five senses, namely, seeing, hearing, and touching, have been commercialized in small powerful sensors and are present in almost every electronic device (smartphone etc). Odor and taste, due to their fundamentally different detection mechanism, represent an extreme challenge for the technical implementation. In contrast to readily attainable mechano- or photoreceptors, chemoreceptors which are capable of translating a chemical-biological signal into an electronic one and are a prerequisite for odor and taste sensors. In this presentation we will highlight our research efforts using three different biomimetic approaches (Figure 1): A) an array of ultra-low cost chemiresistors based on conductive polymers[1] is used to mimic the combinatorial code of the olfactory process. The conductive polymers respond to odorants with changes in their electronic performance and by tuning their chemical side groups they can be more specifically tailored to different chemical classes. B) In order to improve the specificity of the sensors we also use odorant-binding proteins – derived from insects - as a biological recognition unit for fragrances.[2] The binding of an odorant to an odorant-binding protein alters its three-dimensional structure. This conformational change is then converted into an electronic signal because the structural variation also causes a change in the electronic properties of the underlying transistor material. Finally, we present our newest efforts in using artificial membrane structures[3] (tethered lipid membranes) to better mimic the cell membranes which, host the olfactory receptors in the real world and which are essential to take advantage of the signal amplification process in olfaction. The aim of our research is to produce, characterize, compare and benchmark these systems with other methods, tools and finally mother nature itself (electroantennography) to create a better understanding of the olfactory process. Figure 1: Schematic illustration of our biomimetic smell sensor efforts. Left: Schematic of a field-effect transistor endowed with odorant binding proteins; Middle: Logo: illustration of the use of insect odorant binding proteins for smell sensing; Right: difference between human- and electronic nose concepts

Three of our five senses, namely, seeing, hearing, and touching, have been commercialized in small powerful sensors and are present in almost every electronic device (smartphone etc). Odor and taste, due to their fundamentally different detection mechanism, represent an extreme challenge for the technical implementation. In contrast to readily attainable mechano- or photoreceptors, chemoreceptors which are capable of translating a chemical-biological signal into an electronic one and are a prerequisite for odor and taste sensors. In this presentation we will highlight our research efforts using three different biomimetic approaches (Figure 1): A) an array of ultra-low cost chemiresistors based on conductive polymers[1] is used to mimic the combinatorial code of the olfactory process. The conductive polymers respond to odorants with changes in their electronic performance and by tuning their chemical side groups they can be more specifically tailored to different chemical classes. B) In order to improve the specificity of the sensors we also use odorant-binding proteins – derived from insects - as a biological recognition unit for fragrances.[2] The binding of an odorant to an odorant-binding protein alters its three-dimensional structure. This conformational change is then converted into an electronic signal because the structural variation also causes a change in the electronic properties of the underlying transistor material. Finally, we present our newest efforts in using artificial membrane structures[3] (tethered lipid membranes) to better mimic the cell membranes which, host the olfactory receptors in the real world and which are essential to take advantage of the signal amplification process in olfaction. The aim of our research is to produce, characterize, compare and benchmark these systems with other methods, tools and finally mother nature itself (electroantennography) to create a better understanding of the olfactory process. Figure 1: Schematic illustration of our biomimetic smell sensor efforts. Left: Schematic of a field-effect transistor endowed with odorant binding proteins; Middle: Logo: illustration of the use of insect odorant binding proteins for smell sensing; Right: difference between human- and electronic nose concepts

Three of our five senses, namely, seeing, hearing, and touching, have been commercialized in small powerful sensors and are present in almost every electronic device (smartphone etc). Odor and taste, due to their fundamentally different detection mechanism, represent an extreme challenge for the technical implementation. In contrast to readily attainable mechano- or photoreceptors, chemoreceptors which are capable of translating a chemical-biological signal into an electronic one and are a prerequisite for odor and taste sensors. In this presentation we will highlight our research efforts using three different biomimetic approaches (Figure 1): A) an array of ultra-low cost chemiresistors based on conductive polymers[1] is used to mimic the combinatorial code of the olfactory process. The conductive polymers respond to odorants with changes in their electronic performance and by tuning their chemical side groups they can be more specifically tailored to different chemical classes. B) In order to improve the specificity of the sensors we also use odorant-binding proteins – derived from insects - as a biological recognition unit for fragrances.[2] The binding of an odorant to an odorant-binding protein alters its three-dimensional structure. This conformational change is then converted into an electronic signal because the structural variation also causes a change in the electronic properties of the underlying transistor material. Finally, we present our newest efforts in using artificial membrane structures[3] (tethered lipid membranes) to better mimic the cell membranes which, host the olfactory receptors in the real world and which are essential to take advantage of the signal amplification process in olfaction. The aim of our research is to produce, characterize, compare and benchmark these systems with other methods, tools and finally mother nature itself (electroantennography) to create a better understanding of the olfactory process. Figure 1: Schematic illustration of our biomimetic smell sensor efforts. Left: Schematic of a field-effect transistor endowed with odorant binding proteins; Middle: Logo: illustration of the use of insect odorant binding proteins for smell sensing; Right: difference between human- and electronic nose concepts

Nucleic acid diagnostics is crucial for the diagnosis of various diseases as well as for their treatment monitoring. In recent years, short non-coding RNAs, such as microRNAs (miRNAs), have increasingly gained in importance as potential biomarkers in clinical diagnostics. The presence or dysregulation of certain miRNA expression levels in human body fluids can be linked to many diseases, including Alzheimer or various types of cancer [1]. Besides its wide application in gene editing, CRISPR/Cas technology offers a powerful tool for the highly sensitive and selective quantification of nucleic acids [2]. In this talk, the first CRISPR/Cas13a powered electrochemical microfluidic biosensor (CRISPR-Biosensor) for the on-site testing of miRNAs will be presented [3]. The applicability of the CRISPR-Biosensor is successfully showed by measuring two different miRNAs, miR-19b and miR-20a, from very low sample volumes (less than 0.6 µl). Without any target amplification, the CRISPR-Biosensor features a low-cost, easily scalable and multiplexed approach for on-site nucleic acid testing.

Nucleic acid diagnostics is crucial for the diagnosis of various diseases as well as for their treatment monitoring. In recent years, short non-coding RNAs, such as microRNAs (miRNAs), have increasingly gained in importance as potential biomarkers in clinical diagnostics. The presence or dysregulation of certain miRNA expression levels in human body fluids can be linked to many diseases, including Alzheimer or various types of cancer [1]. Besides its wide application in gene editing, CRISPR/Cas technology offers a powerful tool for the highly sensitive and selective quantification of nucleic acids [2]. In this talk, the first CRISPR/Cas13a powered electrochemical microfluidic biosensor (CRISPR-Biosensor) for the on-site testing of miRNAs will be presented [3]. The applicability of the CRISPR-Biosensor is successfully showed by measuring two different miRNAs, miR-19b and miR-20a, from very low sample volumes (less than 0.6 µl). Without any target amplification, the CRISPR-Biosensor features a low-cost, easily scalable and multiplexed approach for on-site nucleic acid testing.

Nucleic acid diagnostics is crucial for the diagnosis of various diseases as well as for their treatment monitoring. In recent years, short non-coding RNAs, such as microRNAs (miRNAs), have increasingly gained in importance as potential biomarkers in clinical diagnostics. The presence or dysregulation of certain miRNA expression levels in human body fluids can be linked to many diseases, including Alzheimer or various types of cancer [1]. Besides its wide application in gene editing, CRISPR/Cas technology offers a powerful tool for the highly sensitive and selective quantification of nucleic acids [2]. In this talk, the first CRISPR/Cas13a powered electrochemical microfluidic biosensor (CRISPR-Biosensor) for the on-site testing of miRNAs will be presented [3]. The applicability of the CRISPR-Biosensor is successfully showed by measuring two different miRNAs, miR-19b and miR-20a, from very low sample volumes (less than 0.6 µl). Without any target amplification, the CRISPR-Biosensor features a low-cost, easily scalable and multiplexed approach for on-site nucleic acid testing.

Electrolyte Gated Organic Transistors (EGOTs) are organic electronic devices composed of three electrodes that feature an electrolyte solution serving as the gate dielectric. The working mechanism of EGOTs is based on the migration of the ions present in the electrolyte upon application of a given potential between two of the device electrodes, namely the gate and the source. Depending on the active material used and in particular to its permeability to the electrolyte ions, EGOTs are usually named EGOFETs (Electrolyte Gated Organic Field Effect Transistors) or OECTs (Organic Electrochemical Transistors), respectively [1,2]. Both EGOFETs and OECTs are rapidly emerging as alternative strategies to state-of-the-art chemo- and biosensors: to enable selective biosensing with EGOTs, a biomolecule serving as a specific recognition moiety is typically immobilized at one of the relevant device interfaces. EGOT biosensors provide a real-time, label-free response and they can ensure ultralow limits of detection exploiting the capacitive coupling between the electrolyte solution and the semiconducting channel. We recently demonstrated EGOTs to quantify analytes in solution spanning a wide range of lengthscales, from neurotransmitter dopamine to antibodies and even plant viruses [3,4]. I will present an overview of our latest achievements, to highlight both the high potential held by EGOT-based biosensors and their current limitations. Different examples of integration of biomolecules within EGOFETs and OECTs architecture will be discussed, and evidences of how the choice of materials largely impacts on the operational regime of EGOTs will be provided, to provide some guidelines to tailor the device properties for selected biosensing applications.

Electrolyte Gated Organic Transistors (EGOTs) are organic electronic devices composed of three electrodes that feature an electrolyte solution serving as the gate dielectric. The working mechanism of EGOTs is based on the migration of the ions present in the electrolyte upon application of a given potential between two of the device electrodes, namely the gate and the source. Depending on the active material used and in particular to its permeability to the electrolyte ions, EGOTs are usually named EGOFETs (Electrolyte Gated Organic Field Effect Transistors) or OECTs (Organic Electrochemical Transistors), respectively [1,2]. Both EGOFETs and OECTs are rapidly emerging as alternative strategies to state-of-the-art chemo- and biosensors: to enable selective biosensing with EGOTs, a biomolecule serving as a specific recognition moiety is typically immobilized at one of the relevant device interfaces. EGOT biosensors provide a real-time, label-free response and they can ensure ultralow limits of detection exploiting the capacitive coupling between the electrolyte solution and the semiconducting channel. We recently demonstrated EGOTs to quantify analytes in solution spanning a wide range of lengthscales, from neurotransmitter dopamine to antibodies and even plant viruses [3,4]. I will present an overview of our latest achievements, to highlight both the high potential held by EGOT-based biosensors and their current limitations. Different examples of integration of biomolecules within EGOFETs and OECTs architecture will be discussed, and evidences of how the choice of materials largely impacts on the operational regime of EGOTs will be provided, to provide some guidelines to tailor the device properties for selected biosensing applications.

Electrolyte Gated Organic Transistors (EGOTs) are organic electronic devices composed of three electrodes that feature an electrolyte solution serving as the gate dielectric. The working mechanism of EGOTs is based on the migration of the ions present in the electrolyte upon application of a given potential between two of the device electrodes, namely the gate and the source. Depending on the active material used and in particular to its permeability to the electrolyte ions, EGOTs are usually named EGOFETs (Electrolyte Gated Organic Field Effect Transistors) or OECTs (Organic Electrochemical Transistors), respectively [1,2]. Both EGOFETs and OECTs are rapidly emerging as alternative strategies to state-of-the-art chemo- and biosensors: to enable selective biosensing with EGOTs, a biomolecule serving as a specific recognition moiety is typically immobilized at one of the relevant device interfaces. EGOT biosensors provide a real-time, label-free response and they can ensure ultralow limits of detection exploiting the capacitive coupling between the electrolyte solution and the semiconducting channel. We recently demonstrated EGOTs to quantify analytes in solution spanning a wide range of lengthscales, from neurotransmitter dopamine to antibodies and even plant viruses [3,4]. I will present an overview of our latest achievements, to highlight both the high potential held by EGOT-based biosensors and their current limitations. Different examples of integration of biomolecules within EGOFETs and OECTs architecture will be discussed, and evidences of how the choice of materials largely impacts on the operational regime of EGOTs will be provided, to provide some guidelines to tailor the device properties for selected biosensing applications.

SERS is a powerful analytical technique for the development of fast diagnostic assays, applied on biofluids in point-of-care or screening testing.[1] The integration of SERS with microfluidics allows the miniaturisation and automation, reducing acquisition times, of complex biological samples analysis.[2] Thanks to these advantages, lab-on-a-chip SERS (LoC SERS) is considered to be a powerful technology that may be implemented in food safety for the fast detection of foodborne pathogens.[3] Herein, we demonstrated the potential of surface-enhanced Raman scattering (SERS) spectroscopy combined with microfluidics for the detection and discrimination of foodborne pathogens. SERS-tagged gold nanostars (GNSs) were functionalized with a monoclonal antibody specific for Listeria monocytogenes. In the presence of L. monocytogenes, a SERS signal corresponding to the SERS tag paired to the antibody was detected in real time and in continuous flow, enabling the discrimination of L. monocytogenes and L. innocua in just 100 s. To the best of our knowledge, this is the first time that SERS tags have been used for the in-flow detection of living organisms.[4] The optofluidics SERS-based proof-of-concept herein described demonstrated to be a reliable approach for the specific detection of L. monocytogenes, and compatible for high-throughput screening of this bacterial pathogen. The fact of performing the analysis in a microfluidics platform offers automation, a higher control on sample handling and a better reproducibility. The described methodology was highly specific, as even though it was reported that mAb C11E9 cross-reacted with some strains of L. innocua, we demonstrated that this SERS-based approach was capable of discriminating among both species. The utility of these integrated optofluidic sensors is not limited to foodborne pathogens and can be expanded to the analysis of other types of bacteria or cells in different fields of research.

SERS is a powerful analytical technique for the development of fast diagnostic assays, applied on biofluids in point-of-care or screening testing.[1] The integration of SERS with microfluidics allows the miniaturisation and automation, reducing acquisition times, of complex biological samples analysis.[2] Thanks to these advantages, lab-on-a-chip SERS (LoC SERS) is considered to be a powerful technology that may be implemented in food safety for the fast detection of foodborne pathogens.[3] Herein, we demonstrated the potential of surface-enhanced Raman scattering (SERS) spectroscopy combined with microfluidics for the detection and discrimination of foodborne pathogens. SERS-tagged gold nanostars (GNSs) were functionalized with a monoclonal antibody specific for Listeria monocytogenes. In the presence of L. monocytogenes, a SERS signal corresponding to the SERS tag paired to the antibody was detected in real time and in continuous flow, enabling the discrimination of L. monocytogenes and L. innocua in just 100 s. To the best of our knowledge, this is the first time that SERS tags have been used for the in-flow detection of living organisms.[4] The optofluidics SERS-based proof-of-concept herein described demonstrated to be a reliable approach for the specific detection of L. monocytogenes, and compatible for high-throughput screening of this bacterial pathogen. The fact of performing the analysis in a microfluidics platform offers automation, a higher control on sample handling and a better reproducibility. The described methodology was highly specific, as even though it was reported that mAb C11E9 cross-reacted with some strains of L. innocua, we demonstrated that this SERS-based approach was capable of discriminating among both species. The utility of these integrated optofluidic sensors is not limited to foodborne pathogens and can be expanded to the analysis of other types of bacteria or cells in different fields of research.

SERS is a powerful analytical technique for the development of fast diagnostic assays, applied on biofluids in point-of-care or screening testing.[1] The integration of SERS with microfluidics allows the miniaturisation and automation, reducing acquisition times, of complex biological samples analysis.[2] Thanks to these advantages, lab-on-a-chip SERS (LoC SERS) is considered to be a powerful technology that may be implemented in food safety for the fast detection of foodborne pathogens.[3] Herein, we demonstrated the potential of surface-enhanced Raman scattering (SERS) spectroscopy combined with microfluidics for the detection and discrimination of foodborne pathogens. SERS-tagged gold nanostars (GNSs) were functionalized with a monoclonal antibody specific for Listeria monocytogenes. In the presence of L. monocytogenes, a SERS signal corresponding to the SERS tag paired to the antibody was detected in real time and in continuous flow, enabling the discrimination of L. monocytogenes and L. innocua in just 100 s. To the best of our knowledge, this is the first time that SERS tags have been used for the in-flow detection of living organisms.[4] The optofluidics SERS-based proof-of-concept herein described demonstrated to be a reliable approach for the specific detection of L. monocytogenes, and compatible for high-throughput screening of this bacterial pathogen. The fact of performing the analysis in a microfluidics platform offers automation, a higher control on sample handling and a better reproducibility. The described methodology was highly specific, as even though it was reported that mAb C11E9 cross-reacted with some strains of L. innocua, we demonstrated that this SERS-based approach was capable of discriminating among both species. The utility of these integrated optofluidic sensors is not limited to foodborne pathogens and can be expanded to the analysis of other types of bacteria or cells in different fields of research.