Application of PEDOT:PSS and Its Composites in Electrochemical and Electronic Chemosensors

Abstract

Poly(3,4-ethylenedioxythiophene):polystyrene sulfonate (PEDOT:PSS) is a highly important and attractive conducting polymer as well as commercially available in organic electronics, including electrochemical and electronic chemosensors, due to its unique features such as excellent solution-fabrication capability and miscibility, high and controllable conductivity, excellent chemical and electrochemical stability, good optical transparency and biocompatibility. In this review, we present a comprehensive overview of the recent research progress of PEDOT:PSS and its composites, and the application in electrochemical and electronic sensors for detecting liquid-phase or gaseous chemical analytes, including inorganic or organic ions, pH, humidity, hydrogen peroxide (H₂O₂), ammonia (NH₃), CO, CO₂, NO₂, and organic solvent vapors like methanol, acetone, etc. We will discuss in detail the structural, architectural and morphological optimization of PEDOT:PSS and its composites with other additives, as well as the fabrication technology of diverse sensor systems in response to a wide range of analytes in varying environments. At the end of the review will be given a perspective summary covering both the key challenges and potential solutions in the future research of PEDOT:PSS-based chemosensors, especially those in a flexible or wearable format.

1. Introduction

It remains imperative to develop chemosensor techniques for environmental, health and safety monitoring [1,2]. With the technical advancement in instrumentation, microelectronics and computers, it becomes more feasible nowadays to design and construct chemosensors utilizing most of the known chemical, physical and biological properties or features of sensor materials. Chemosensors may be classified into different types according to the sensor operating principle. Typical types of chemosensors include optical [3] (based on colorimetric or fluorescence change), electrical [4] (based on measurement of resistance, capacitance, impedance or other electrical signal), IR spectrometry, mass spectrometry, chromatography, surface acoustic wave, and others. Among all these types of sensors, chemosensors based on electrical signal modulation are much more straightforward and facile for device design, signal transduction and system integration, which combined can be made to be portable and small in size, thus suited for real-time onsite operation. Electrochemical [5] and electronic signals [6] are mostly used in electrical mode chemosensors. Upon exposure to the chemical analytes, an electrochemical sensor can transform the amperometric, potentiometric, or voltammetric effect of the analyte–electrode interactions (mostly in liquid solutions) into a measurable signal that in turn can identify and quantize the presence of different analytes [4]. In comparison, an electronic chemosensor usually outputs a signal directly arising from the change of electrical properties (resistive, conductivity, etc.) of the sensor material caused by the surface charge-transfer interaction with chemical analytes (mostly in the gas phase).

The overall performance of chemosensors is determined by several factors such as chemical and physical properties of sensing material, device geometry, and signal transduction. Improvement of the sensor performance demands a synergistic optimization of the above-mentioned factors. In terms of sensing materials, diverse conductive materials such as conducting polymers, polymer/carbon composites, graphene, and metal or semiconductor nanocrystals show great promise [7]. Especially, conducting polymers such as poly(3,4-ethylenedioxythiophene) (PEDOT) [8], polypyrrole (PPy) [9] and polyaniline (PANI) [10] are among the highest attractive sensing materials owing to their intriguing features such as their all-organic nature with good designability, intrinsic electrical conductivity, high signal transduction, dimensional durability, mechanical flexibility, and chemical stability. The synthesis of the polymers, usually via convenient chemical or electrochemical polymerization methods, are simple and cost effective. The polymers thus synthesized can retain their electrical conductivity and chemical/physical stability when used in chemosensors. Such durability is crucial for chemosensors, for which the sensing repeatability is one of the most important factors affecting the real application of sensor devices.

Among the conducting polymers used for chemosensors, PEDOT exhibits a relatively high stability and adjustable conductivity (10⁻³–10³ S cm⁻¹) compared to PPy and PANI. The linear, rigid molecular conformation of PEDOT facilitates its charge transport [11]. To be suited for use in chemoresistive sensors, the conductivity of polymers must be at an appropriate level and, more importantly, adjustable. Indeed, if the conductivity is too low or too high, the sensor performance will be limited by the low signal-to-noise ratio [12]. PEDOT by itself is typically insoluble in water or common organic solvents [13]. However, if it is synthesized in the presence of poly(4-styrenesulfonate) (PSS), an stable aqueous dispersion containing both polymers (PEDOT:PSS) (Figure 1b) can be obtained, which is normally of a dark-blue color [14]. As a commercially available and ready-to-use waterborne dispersion, PEDOT:PSS remains attractive for development as organic electronics (including thermoelectric conversion [15], photovoltaic devices [16], supercapacitors [17] and sensors [18], etc.) because of its excellent solution-fabrication capability and miscibility into functionally films (usually by drop-casting [19], spin-coating [20], and spray-coating [21]) exhibiting a high and controllable conductivity, a high work function, excellent chemical and electrochemical stability, good optical transparency, good biocompatibility, and so on [22]. Since year 2000 when the three discoverers of conducting polymers won the Nobel Prize in Chemistry, PEDOT:PSS and its hybrid composites with metal/metal oxide nanoparticles, insulating polymers, carbon materials and others have been extensively studied and applied widely in organic electronics including electrochemical and/or electronic chemosensors as covered in this review. These research activities have produced thousands of peer-reviewed papers and patents.

In the last decade, some excellent reviews have been published on the related topics of electrical sensors based on various conducting polymers. For example, Liao et al. [23] reviewed the development of organic electrochemical transistor (OECT)-based sensors by focusing on the functionalization of PEDOT:PSS films as channel materials. Rahimzadeh et al. [13] reviewed the recent advancement in PEDOT-based electrochemical biosensors. Various PEDOT composites blended with nanomaterials such as carbon nanomaterials and metal/metal oxide nanoparticles, and the applications in electrochemical sensors were described by Kaur et al. [18] However, there still lacks a special and comprehensive review of electrochemical and electronic chemosensors based on PEDOT:PSS and its composites.

In this review, we will focus on the recent research progress of PEDOT:PSS and its composites, and the application in electrochemical and electronic sensors for detecting liquid-phase or gaseous chemical analytes, including inorganic or organic ions, pH, humidity, hydrogen peroxide (H₂O₂), ammonia (NH₃), CO, CO₂, NO₂, and organic solvent vapors like methanol, acetone, etc. We will discuss in detail the structural, architectural and morphological optimization of PEDOT:PSS and its composites with other additives, as well as the fabrication technology of diverse sensor systems in response to a wide range of analytes in varying environments. It is expected that this review will not only provide a deep, comprehensive understanding of the structure, architecture and composite design rules, chemical stimuli response mechanisms, and sensing processes of PEDOT:PSS-based electrochemical/electronic chemosensors, but also help extend the research of PEDOT:PSS-based composites into other emerging areas, especially flexible, stretchable, and wearable electronics, for which chemosensors play crucial roles in the development of multimodal sensors and related system integration.

2. PEDOT:PSS-Based Electrochemical Chemosensors

A typical electrochemical sensor has been considered as electrochemical cells containing three or two electrodes (Figure 1a) immersed in an electrolyte solution. A characteristic three-electrode system contains a reference, counter, and working electrode (sensing electrode). The working electrode has a chemically stable solid conductive substance (conventionally gold, carbon, and platinum), and the reference electrode generally contains the silver wire coated with a layer of silver chloride (Ag/AgCl) to provide a fixed stable potential to other electrodes, and a platinum wire is usually employed as the counter electrode (not necessary in a two-electrode system) to the working electrode. The electrochemical procedures can usually be classified into three key categories concerning different modes of measurement: current (voltammetry, amperometry), potential difference (potentiometry), and impedance (electrochemical impedance spectroscopy) [11]. The common current mode-based sensors are to measure the current under the potential of a working electrode against a reference electrode. This electrical current results from the electrolysis of chemical analytes (e.g., molecules, ions) through either electrochemical oxidation or reduction at the working electrode surface. This procedure depends on the mass transport rate of the analytes to the electrode, as well as the rate of electron transfer at the electrode surface. In addition to the conventional electrochemical systems, OECT (Figure 1b) is another sensor architecture commonly used in chemical and biological detection. In a regular OECT configuration, the gate is immersed in an electrolyte and the active material channel is in direct contact with an electrolyte and with the source and drain [24]. The important sensing interfaces for analyte monitoring are the gate electrode surface and channel surface. Any chemical reaction occurring on these two surfaces may induce a change in interfacial potential, and result in a change in channel current, which in turn can be used as a sensor response signal [23].

It is important to note that for the development of electrochemical chemosensors to determinate different analytes, the working electrodes have often been modified with appropriate substances to achieve the desired performance such as improved selectivity, sensitivity and stability. PEDOT:PSS has not only been employed as a common material for working electrodes, but has also been proven compatible and processible with metal or carbon materials for surface modification. Besides, good biocompatibility of PEDOT:PSS makes it an ideal material for bioelectronic applications. PEDOT:PSS is an excellent matrix for functionalization with various biological components such as antibodies [25], enzymes [26], and peptides [27] to be developed as electrochemical biosensors. There are several reviews [2,5,28] focused on such electrochemical biosensors integrated with conducting polymers including PEDOT:PSS for monitoring the biological targets such as DNA, proteins [27], glucose [29], and other biomarkers. In this section, we just give a brief summary about this aspect of research, while the main attention will be laid on the issues and improvements of electrochemical chemosensors towards biological and environmental analytes such as H₂O₂, pH, NH₄⁺, some inorganic ions and organic compounds, etc. (Table 1).

2.1. H₂O₂ Detection

Hydrogen peroxide (H₂O₂) has been widely used in industry as it plays crucial roles in chemical, pharmaceutical, and food manufacturing [32]. H₂O₂ is also an important component or synthetic precursor for some improvised explosives. Moreover, H₂O₂ is a key marker in biological processes as it is involved in signaling paths such as cellular growth, senescence and apoptosis, wherein it can be generated through different stimuli. Detection of H₂O₂ can help probe the biomolecules in different fluids as H₂O₂ is often a byproduct of many biochemical reactions involving oxidase enzymes such as glucose, cholesterol and lactate oxidase, etc. For these reasons, the development of chemosensors for trace level detection of H₂O₂ has remained the focus of chemosensor research, for which most of the sensors reported are based on electrochemical system owing to the electroactive nature of H₂O₂. In this section, we focus on the direct detection of H₂O₂, and exclude the indirect detection of H₂O₂ as a byproduct of a redox reaction.

As shown in Table 1, most of the electrochemical sensors developed for H₂O₂ are amperometric types and used glassy carbon electrode (GCE) or a screen-printed electrode (SPE) as the working electrode substrate. GCE has the advantages of wide commercial availability, a low background current, and easy surface modification, while SPE is small in volume and easy to be integrated in a sensor system for miniaturization.

The main architecture of components of a typical working electrode for electrochemical detection of H₂O₂ is shown in Figure 2. The electrochemistry technique based on a simple and low-cost enzyme electrode has been extensively employed for accurate determination of H₂O₂ due to the intrinsic selectivity and sensitivity of enzymatic reactions [33,34]. The most frequently used enzyme to decompose H₂O₂ is horseradish peroxidase (HRP), which catalyzes the oxidation of a substrate using H₂O₂ as the oxidizing agent, allowing for direct electron transfer through the electrode. In this situation, PEDOT:PSS was coated on the electrode to immobilize HRP because of its good conductivity and biocompatibility, providing an ideal microenvironment for keeping biological activity while facilitating the direct electron transfer between the enzyme’s active sites and the electrode. After the surface modification of the electrode and immobilization of the enzyme, a Nafion film is usually coated to prevent the modification layer from falling off because PEDOT:PSS is prone to swell and fall off from the substrate in an aqueous solution.

As an example of success, Zhang et al. [33] fabricated a hybrid composite of PEDOT:PSS and chitosan micelles and coated it on the surface of GCE, followed by immobilization with HRP. The presence of PEDOT:PSS was found to be capable of enhancing the interfacial electron transfer between HRP and the electrode. The sensor thus fabricated showed a very low detection limit (LDL) of 0.03 nM and a dynamic linear range between 0.1 nM and 10 nM for detection of H₂O₂. The wide detection range was attributed to the large surface area of the hybrid film of PEDOT:PSS, which in turn facilitates the immobilization of HRP. The large surface area would also facilitate the signal transduction from the enzyme to the electrode. The similar advantage of a large surface area of electrode for improving the sensor performance was also evidenced in a sensor involving PEDOT:PSS hydrogel, which was also conducive to a high loading of enzymes like HRP [34].

In recent years, gold nanoparticles (AuNPs) and silver nanoparticles (AgNPs) have been widely used in the fabrication of electrochemical biosensors because of their unique properties such as high biocompatibility, good conductivity, high catalytic activity, and size-dependent properties. Compared to the pristine PEDOT:PSS, the composites with an encapsulation of the metal nanoparticles could further enhance the electron exchange and realize the direct electrochemical redox reactions of enzymes since metal nanoparticles may act as electron relays in the PEDOT:PSS film. As evidenced in many studies, the GCEs modified with HRP/PEDOT:PSS/AuNPs [35] and HRP/PEDOT:PSS/AgNPs [36] showed excellent electrocatalytic ability and were thus sensitive to detection for H₂O₂ with a wide linear range of 0.2~380 μM and 0.05~20 μM, respectively. More sophisticated, a ternary composite [37] with PEDOT:PSS, AuNPs and reduced-graphene oxide (rGO) was assembled with HRP on a screen-printed gold electrode (SPGE) for amperometric detection of H₂O₂. This composite sensor exhibited a high sensitivity of up to 677 A mM⁻¹ cm⁻², with a wide linear range from 5 to 400 μM and LDL of 0.08 μM. The enhanced sensing performance could be ascribed to the intimate contact of AuNPs onto the rough surface of the PEDOT:PSS-rGO nanocomposite, which has a high electrical conductivity and a large surface area, allowing for the growth and support of nanoparticles while still maintaining the high electrical conductivity.

While PEDOT:PSS and other materials have been commonly used to immobilize enzymes on an electrode for retaining the enzymatic biologic activity and electrically connecting the enzyme with the electrode surface, the research of PEDOT:PSS-based electrochemical sensors for H₂O₂ has also been extended from use of enzymes to enzymeless active composites such as Meldola Blue (MDB) and Prussian Blue (PB). This alternative approach aims to overcome the technical limitations of enzymes like poor stability and the complexity of the immobilization process involving enzymes. Siao et al. [38] reported an enzymeless electrochemical sensor for H₂O₂, which was fabricated with PEDOT:PSS and Meldola Blue (MDB) on a GCE. The sensor thus fabricated could electrocatalytically reduce H₂O₂ with a low overpotential and showed a linear response in the concentration range of 5 to 120 μM with a LDL of 0.1 μM and a sensitivity of 353.9 μAmM⁻¹ cm⁻².

Although electrochemical sensors are usually suitable for detection of analytes in solutions, there exists a potential to adapt the sensor for gas phase chemical detection by combining the sensor system with an air extraction system that can concentrate airborne analytes into solution to be ready for electrochemical detection. Recently, Chen et al. [19] prepared a new composite consisting of PEDOT:PSS, PB, ethylene glycol (EG), and divinyl sulfone (DVS). After drop-casting it onto a SPGE, the sensor showed a good linear response between 0.1 μM to 25.6 μM with a sensitivity of −0.95 A M⁻¹ cm⁻² and LDL of 0.22 μM for solution phase detection. When combing the sensor with an exhaled breath condensate (EBC) device, it became capable of directing detection of H₂O₂ in human breath, which may provide a new way for noninvasive diagnosis or screenings of diseases (e.g., cancers) as H₂O₂ has been identified as one of the common breath biomarkers for humans.

2.2. pH Detection

pH is an extremely important parameter in biological processes and related chemical reactions. Detection of pH changes can provide diagnostic information about health and medical status. In particular, pH variations in human sweat have been correlated to blood glucose levels [39] and the pH of a wound exudate is indicative of the progression of the wound-healing process and the presence of bacterial colonies [40]. Real-time analysis of such biofluids can be achieved by means of portable and wearable sensing devices integrated into clothing, bandages or other everyday accessories, which imposes a great technical challenge to the traditional chemical sensors. While much effort has been put into combining flexible substrates with traditional rigid sensing materials to fabricate pH sensors with a good performance, the flexibility of PEDOT:PSS film and its biocompatibility for wearable bioelectronics are beyond the reach of these technologies. Within the PEDOT:PSS composite, the PEDOT chains are uniformly distributed along the PSS polymer chains under slightly acidic conditions. Such an optimized distribution of PEDOT chains within the colloidal PEDOT:PSS system ensures the formation of a continuous electrical connection between PEDOT segments. When the pH shifts from acidic to basic, the homogeneous distribution of PEDOT along the PSS polymer chains is interrupted by the negatively charged hydroxyl groups. Under more basic conditions, the PEDOT short chains are neutralized by the hydroxyl groups, forming a new hydrophobic phase which is covered by the long chains of PSS [41] (Figure 3a). As a result, conductivity of the polymer film declined significantly. However, swelling of the hydrophilic PSS in PEDOT:PSS could affect the resistance of the electrode, leading to poor pH sensitivity in electrochemical sensors. In general, electrochemical sensing of pH relies on the potentiometric measurement of an active working electrode with respect to the reference electrode.

The conductivity of PEDOT:PSS used in the electrochemical sensors can be improved by various methods [42] in order to overcome the above-mentioned technical limitations. The PEDOT:PSS composite is often fabricated with other pH-sensitive materials acting as a charge transfer layer of work electrode. PANI, for example, has low conductivity, but its various oxidation states are pH-dependent, making it suitable for pH sensing. Smith et al. [40] deposited the dispersions of PEDOT:PSS and multiwalled carbon nanotubes (MWCNTs) on cotton (Figure 3b,c) by a dipping method, followed by electrochemical deposition of PANI to fabricate a fibril material to function as the working electrode. The fiber electrode showed a rapid response (−61 ± 2 mV pH⁻¹) over a wide pH range (2–12) and a high selectivity in the presence of varying interfering ions (NH₄⁺, Mg²⁺, Ca²⁺, K⁺ and Na⁺). The PANI/PEDOT:PSS-MWCNTs-cotton fibril composite showed intermediate values of ultimate tensile strengths (130 ± 25 MPa, 10 ± 2% strain at break) whilst maintaining sufficient flexibility. The fibril materials have an obvious ability to inhibit the growth of bacteria and has biocompatibility with skin cells. This highlights the potential to develop these fibril materials as pH-sensing fabrics for wound monitoring. Smith et al. [43] also directly prepared PEDOT:PSS fibers (Figure 3d) by wet spinning and then electrodeposited PANI onto them for pH detection. The pristine PEDOT:PSS fibers were treated with dimethyl sulfoxide (DMSO) and their diameters were controlled to obtain a high conductivity (802 ± 122 S cm⁻¹). The thicker fibers have a higher PSS-to-PEDOT ratio, which leads to more water being absorbed by the hydrophilic PSS, resulting in more swelling during pH analysis. This would affect the resistance of the electrode and thus the potential and slope of voltage vs. pH (Figure 3e). The best pH response and lowest swelling was achieved by the thin fiber prepared from DMSO treatment, which gave a response of −56 ± 7 mV pH⁻¹.

2.3. Ion Detection

When PEDOT:PSS is introduced into an ion sensor, it acts as an ion-to-electron transducer layer to decrease the impedance and promote the charge transfer within the sensor, which significantly improves the potentiometric stability and detection performance. The selectivity of such an ion sensor comes from the use of an ion-selective membrane (ISM). ISM allows for only specific ions to transport from the solution to the conductive layer, whereas it blocks the transport of other interfering ions, thus enabling selective detection of a variety of cations and anions such as Na⁺, K⁺ [44], Ca²⁺, NH₄⁺ [45], Cu²⁺ [46], Mg²⁺, Cl⁻ [47], etc.

For many years, direct potentiometry and ion-selective electrodes have been useful tools for determining ion concentrations in human body fluids and other areas in medical analyses. Urbanowicz et al. [47] fabricated a two-layer surface coating on the gold electrode: electrically synthesized PEDOT:PSS forming an intermediate layer and ISM, to monitor Na⁺, K⁺, Ca²⁺, Mg²⁺ and Cl⁻ in human saliva (Figure 4a). The sensor consisted of a reference electrode and an ion selective electrode, showing a wide linear range and sensitivity (Table 1) assuring its applicability in biomedical fields.

PEDOT:PSS is characterized by high stability, high ionic mobility and a high charge transfer rate, as well as good adhesion to the membrane material and electrode substrate. The most common ways to deposit PEDOT:PSS onto the electron conductive substrate are via drop-casting, spin-coating, or inkjet printing, etc. However, as reported in many publications, the films of the same conducting polymer fabricated with different deposition methods may show different characteristics [48]. These factors affect the reproducibility of electrical potentials, which are critical characteristics for the mass production of ion-selective electrodes. In this regard, Wang et al. [49] studied a Ca²⁺ sensor based on a screen-printing technique, that is, PEDOT:PSS was screen-printed on carbon paste electrodes as internal solid contacts for both ion-selective and reference electrodes. The screen-printing method provides a cost-effective and reproducible way of mass-manufacturing portable ion sensors.

Recently, Coppedè et al. [44] fabricated a textile OECT device (Figure 4b) by soaking an acrylic textile thread with PEDOT:PSS. The selectivity was improved by directly functionalizing the textile device with ISM. Membrane selectivity was tested by comparing the transistor response with interfering ions, proving successfully the selective response to Na⁺, K⁺, Ca²⁺. This direct functionalization of textile fibers as an active channel may find wide application in the wearable devices for analyzing liquid samples, such as sweat, enabling real-time monitoring and screening of health.

2.4. Other Analyte Detection

As described above, in electrochemical sensors, the sensing signal comes from the redox reaction of the analyte on the electrode surface. PEDOT:PSS is used to modify the bare electrode to improve the detection sensitivity due to its excellent electrochemical and environmental stability, good biocompatibility, superior film-forming properties, and fine tuning of their physicochemical properties [50,51]. In addition, researchers have often combined PEDOT:PSS with different nanoscale catalytic materials (mainly carbon materials [52,53,54,55] and metal/metal oxide nanoparticles [56,57,58,59]) to form composites in order to promote rapid electron transfer. Such an approach has great potential for application in the construction of electrochemical sensors for various biological and environmental detections [18].

The incorporation of different nanostructures into PEDOT:PSS generally improves the interaction and the electrocatalytic activity with the analyte in a synergistic way, which leads to an amplified signal output. As shown in Figure 5a, carbon black (CB), graphene oxide (GO), copper nanoparticles (CuNPs) and PEDOT:PSS can be mixed and used for surface modification of the GCE electrode [57]. The cyclic voltammograms of the GCE electrode before and after modification with a PEDOT-PSS film containing GO, CB-GO or CuNPs/CB-GO was shown in Figure 5b. It is clear that the peak current was relatively increased after each step of modification, indicating that the electroactive surface area of GCE increased after every modification. And the quinary mixtures of isoproterenol, acetaminophen, folic acid, propranolol and caffeine was determined by square-wave voltammetry (Figure 5c), resulting the linear ranges and LDL of micromolar concentration levels, as shown in Table 1.

In addition, various other methods have been proven to be quite useful for fabrication of low-resistance PEDOT:PSS films for electrochemical analyte detection [49,59,60]. For example, our group [60] prepared PEDOT:PSS films with enhanced conductivity by DMSO second-doping, which can be directly used as flexible electrodes for detection of p-butylhydroquinone (TBHQ), which gave a LDL of 0.15 μM. However, the poor water resistance and weather stability of the PEDOT:PSS film would limit the widespread application in electrochemical analysis. To solve this problem, Zhang et al. [61] introduced carboxymethyl cellulose (CMC) into PEDOT:PSS, which demonstrated a significant improvement of the flexibility, adhesion and long-term electrode stability in water, as well as the electrocatalytic ability for maleic hydrazide (MH), salicylic acid (SA), and sunset yellow. In their subsequent work [62], a carbon nanotube with a large rough surface area was added to the composite of PEDOT:PSS and CMC to improve the electrochemical sensing performance of PEDOT:PSS composites. The fabricated PEDOT:PSS-CMC-SWCNT/GCE exhibited enhanced electron transfer and a synergistic electrocatalytic ability towards maleic hydrazide, and displayed excellent sensing performance with a wide linear range (0.8 to 51 μM), a low LDL (0.1 μM) and good sensing stability.

Table 1. Comparison of PEDOT:PSS-based electrochemical chemosensors for different analytes.

Working Electrode	Analyte	Model	LDL	Sensitivity	Linear Range	Ref.
PEDOT:PSS-PB-EG-DVS/SPGE	H2O2	Amperometry	219 nM	−0.95 A M−1 cm−2	0.1–25.6 μM	[19]
Nafion/HRP/PEDOT:PSS-CS micelle/GCE	H2O2	Amperometry	0.03 nM	-	0.1 nM–10 nM	[33]
Nafion/HRP/PEDOT:PSS hydrogel/GCE	H2O2	Amperometry	0.94 μM	155 μA mM−1	0.0088–0.15 mM	[34]
			0.045 mM	3.5 μA mM−1	0.4–10 mM
HRP-PEDOT:PSS-AuNPs/GCE	H2O2	Amperometry	0.1 μM	-	0.2–380 μM	[35]
Nafion/HRP/AgNPs/PEDOT:PSS-Nafion/GCE	H2O2	Amperometry	0.02 μM	-	0.05–20 μM	[36]
HRP/PEDOT:PSS-rGO-AuNPs/SPGE	H2O2	Amperometry	0.08 μM	677 μA mM−1 cm−2	0.5–400 μM	[37]
PEDOT:PSS-MDB/GCE	H2O2	Amperometry	0.1 μM	353.9 mA mM−1 cm−2	5–120 μM	[38]
PANI/PEDOT:PSS/G	pH	Potentiometry	-	75.06 mV pH−1	4–7	[39]
PANI/PEDOT:PSS-MWCNTs-cotton	pH	Potentiometry	-	−61 ± 2 mV pH−1	2–12	[40]
PANI/PEDOT:PSS fiber	pH	Potentiometry	-	−56 ± 7 mV pH−1	3–7	[43]
K+ ISM/PEDOT:PSS-acrylic textile	K+	OECT	-	3.49 M−1	0.01–1000 mM	[44]
NH4+ and Ca2+ ISM/PEDOT:PSS	NH4+ Ca2+	OECT	-	-	10–1000 μM	[45]
Cu2+-ISM/PEDOT:PSS/GCE	Cu2+	Potentiometry	0.5 nM	28.1 ± 0.4 mV dec−1	1 nM–1 mM	[46]
ISMs/PEDOT:PSS/GCE	Na+	Potentiometry	-	56 ± 1 mV dec−1	0.1–100 μM	[47]
	K+		-	58 ± 1 mV dec−1	0.01 mM–100 μM
	Ca2+		-	29 ± 1 mV dec−1	0.01–100 μM
	Mg2+		-	30 ± 1 mV dec−1	1–100 μM
	Cl−		-	−54 ± 1 mV dec−1	0.1–100 μM
Pb2+-ISM/PEDOT:PSS/GCE	Pb2+	Potentiometry	0.1 μM	27 mV dec−1	10−5–10−7 M	[49]
PEDOT:PSS/glassy-carbon disk	thiols	Amperometry	0.005 mM	0.43 A M−1 cm−2	0.005–0.1 mM	[50]
PEDOT:PSS/GCE	Tricresyl phosphate	Voltammetry	70 ppb	-	50–300 ppb	[51]
PEDOT:PSS-GO/PET	carbofuran	Voltammetry	0.1 µM	-	1 mM–90 mM	[52]
PEDOT:PSS-β-CD-SWCNT-COOH/GCE	shikonin	Voltammetry	1.80 nM	-	6.0–30,000 nM	[53]
PEDOT:PSS-rGO/GCE	nimesulide	Voltammetry	2.4 nM	-	80–1900 nM	[54]
	piroxicam		0.1 µM		0.87–260 µM
PEDOT:PSS-G/SPCE	2,2-diphenyl1-picrylhydrazyl (DPPH)	Amperometry	0.59 μM	-	5–30 μM	[55]
PEDOT:PSS-MgO/GCE	bisphenol A	Voltammetry	0.5 nM	-	1.0 nM–0.4 μM and 0.4–10 μM	[56]
CuNPs/GO-CB-PEDOT:PSS/GCE	isoproterenol	Voltammetry	1.9 μM	0.062 μA μM−1	8–50 μM	[57]
	acetaminophen		0.23 μM	0.29 μA μM−1	0.9–7 μM
	folic acid		1.0 μM	0.098 μA μM−1	5–31 μM
	propranolol		0.18 μM	0.92 μA μM−1	0.5–2.9 μM
	caffeine		3.4 μM	0.028 μA μM−1	11–64 μM
PEDOT:PSS-ZnO/GCE	chlorogenic acid	Voltammetry	0.02 μM	26.38 μA mΜ−1 cm−2	0.03–476.2 μM	[58]
AgNPs/PEDOT:PSS-H2SO4/glass	nitrite	Amperometry	0.34 μM	0.03639 μA μM−1 cm−2	0.5–3400 μM	[59]
PEDOT:PSS-DMSO film	tert-butylhydroquinone	Voltammetry	0.15 μM	-	0.5–200 μM	[60]
PEDOT:PSS-CMC/GCE	tryptophan	Voltammetry	0.02 μM	-	0.05–100 mM	[61]
PEDOT:PSS-CMC-SWCNT/GCE	maleic hydrazide	Voltammetry	0.1 µM	-	0.8–51 µM	[62]

Table 1. Comparison of PEDOT:PSS-based electrochemical chemosensors for different analytes.

Working Electrode	Analyte	Model	LDL	Sensitivity	Linear Range	Ref.
PEDOT:PSS-PB-EG-DVS/SPGE	H2O2	Amperometry	219 nM	−0.95 A M−1 cm−2	0.1–25.6 μM	[19]
Nafion/HRP/PEDOT:PSS-CS micelle/GCE	H2O2	Amperometry	0.03 nM	-	0.1 nM–10 nM	[33]
Nafion/HRP/PEDOT:PSS hydrogel/GCE	H2O2	Amperometry	0.94 μM	155 μA mM−1	0.0088–0.15 mM	[34]
			0.045 mM	3.5 μA mM−1	0.4–10 mM
HRP-PEDOT:PSS-AuNPs/GCE	H2O2	Amperometry	0.1 μM	-	0.2–380 μM	[35]
Nafion/HRP/AgNPs/PEDOT:PSS-Nafion/GCE	H2O2	Amperometry	0.02 μM	-	0.05–20 μM	[36]
HRP/PEDOT:PSS-rGO-AuNPs/SPGE	H2O2	Amperometry	0.08 μM	677 μA mM−1 cm−2	0.5–400 μM	[37]
PEDOT:PSS-MDB/GCE	H2O2	Amperometry	0.1 μM	353.9 mA mM−1 cm−2	5–120 μM	[38]
PANI/PEDOT:PSS/G	pH	Potentiometry	-	75.06 mV pH−1	4–7	[39]
PANI/PEDOT:PSS-MWCNTs-cotton	pH	Potentiometry	-	−61 ± 2 mV pH−1	2–12	[40]
PANI/PEDOT:PSS fiber	pH	Potentiometry	-	−56 ± 7 mV pH−1	3–7	[43]
K+ ISM/PEDOT:PSS-acrylic textile	K+	OECT	-	3.49 M−1	0.01–1000 mM	[44]
NH4+ and Ca2+ ISM/PEDOT:PSS	NH4+ Ca2+	OECT	-	-	10–1000 μM	[45]
Cu2+-ISM/PEDOT:PSS/GCE	Cu2+	Potentiometry	0.5 nM	28.1 ± 0.4 mV dec−1	1 nM–1 mM	[46]
ISMs/PEDOT:PSS/GCE	Na+	Potentiometry	-	56 ± 1 mV dec−1	0.1–100 μM	[47]
	K+		-	58 ± 1 mV dec−1	0.01 mM–100 μM
	Ca2+		-	29 ± 1 mV dec−1	0.01–100 μM
	Mg2+		-	30 ± 1 mV dec−1	1–100 μM
	Cl−		-	−54 ± 1 mV dec−1	0.1–100 μM
Pb2+-ISM/PEDOT:PSS/GCE	Pb2+	Potentiometry	0.1 μM	27 mV dec−1	10−5–10−7 M	[49]
PEDOT:PSS/glassy-carbon disk	thiols	Amperometry	0.005 mM	0.43 A M−1 cm−2	0.005–0.1 mM	[50]
PEDOT:PSS/GCE	Tricresyl phosphate	Voltammetry	70 ppb	-	50–300 ppb	[51]
PEDOT:PSS-GO/PET	carbofuran	Voltammetry	0.1 µM	-	1 mM–90 mM	[52]
PEDOT:PSS-β-CD-SWCNT-COOH/GCE	shikonin	Voltammetry	1.80 nM	-	6.0–30,000 nM	[53]
PEDOT:PSS-rGO/GCE	nimesulide	Voltammetry	2.4 nM	-	80–1900 nM	[54]
	piroxicam		0.1 µM		0.87–260 µM
PEDOT:PSS-G/SPCE	2,2-diphenyl1-picrylhydrazyl (DPPH)	Amperometry	0.59 μM	-	5–30 μM	[55]
PEDOT:PSS-MgO/GCE	bisphenol A	Voltammetry	0.5 nM	-	1.0 nM–0.4 μM and 0.4–10 μM	[56]
CuNPs/GO-CB-PEDOT:PSS/GCE	isoproterenol	Voltammetry	1.9 μM	0.062 μA μM−1	8–50 μM	[57]
	acetaminophen		0.23 μM	0.29 μA μM−1	0.9–7 μM
	folic acid		1.0 μM	0.098 μA μM−1	5–31 μM
	propranolol		0.18 μM	0.92 μA μM−1	0.5–2.9 μM
	caffeine		3.4 μM	0.028 μA μM−1	11–64 μM
PEDOT:PSS-ZnO/GCE	chlorogenic acid	Voltammetry	0.02 μM	26.38 μA mΜ−1 cm−2	0.03–476.2 μM	[58]
AgNPs/PEDOT:PSS-H2SO4/glass	nitrite	Amperometry	0.34 μM	0.03639 μA μM−1 cm−2	0.5–3400 μM	[59]
PEDOT:PSS-DMSO film	tert-butylhydroquinone	Voltammetry	0.15 μM	-	0.5–200 μM	[60]
PEDOT:PSS-CMC/GCE	tryptophan	Voltammetry	0.02 μM	-	0.05–100 mM	[61]
PEDOT:PSS-CMC-SWCNT/GCE	maleic hydrazide	Voltammetry	0.1 µM	-	0.8–51 µM	[62]

3. PEDOT:PSS-Based Electronic Chemosensors

Compared with electrochemical chemosensors, electronic chemosensors are relatively simple in construction. Most of them are based on a simple interdigital (IDT) electrode or conductive sensing materials deposited directly on substrates that are connected to a measurement system (Figure 6a,b). The changes in the current, resistance or capacitance [63] caused by the surface interaction with the analytes can be measured and transduced to an output signal. Due to their low cost, small size, and ease of use, electronic chemosensors are commonly used for monitoring humidity and various gases and chemicals.

In most cases, PEDOT:PSS is deposited on IDT electrodes or other substrates by drop-casting or spin-coating. The resulted pristine PEDOT:PSS film presents a low sensitivity and a slow response because the film’s morphology, microstructure and porosity do not satisfy the need of gas sensing performance. Hence, nanostructure engineering of PEDOT:PSS would be crucial for enhancing the gas sensing performance. Typical ways to fabricate nanostructured PEDOT:PSS include nano-confined strategies such as electrospinning [66] and other template methods [67,68]. Furthermore, PEDOT:PSS is printable [10], thus allowing to produce highly uniform films on various flexible substrates such as polyethylene terephthalate (PET) and paper, for which the thickness of the film can be precisely controlled by techniques like inkjet printing.

PEDOT:PSS can also be blended with other functional materials such as carbon materials and metal oxide semiconductors through solution processing, and the composites thus obtained can then be deposited on a substrate through the methods mentioned above to improve the performance of electronic chemosensors. The material composition, structure, sensing mechanism and performance of various PEDOT:PSS composites as used in electronic chemosensors towards humidity, ammonia, CO_X, NO₂, and volatile organic compounds (VOCs), are listed in Table 2 and discussed accordingly in the following sections.

3.1. Humidity Detection

Humidity sensors are widely used in environmental monitoring, healthcare and the construction of electronic and optical devices [10]. It is essential to monitor, detect and control the ambient humidity in many manufacturing situations. Although numerous studies have been made towards developing humidity sensors, the current research and development in this field still faces many technical challenges regarding both material design and structure engineering.

As a ready-to-use waterborne dispersion, PEDOT:PSS is by nature a water-absorbing material, which remains as a typical problem for its practical application in organic electronic devices (wherein humidity effect or moisture-induced degradation of electronic performance must be avoided). However, such a “negative” effect for electronics can be turned into something positive to enable the development of humidity sensors. PEDOT:PSS films are characterized by a granular structure in which PEDOT-rich grains (conductive) are surrounded by PSS (insulating, hydrophilic). When the relative humidity (RH) increases, a decrease in conductivity of PEDOT:PSS can usually be observed, which is ascribed to the decreasing electrical interconnections among PEDOT chains caused by the water absorption (swelling) of PSS. Humidity sensors based on a PEDOT:PSS film generally demonstrate a linear response towards relative humidity changing from 20% to 80%. However, such PEDOT:PSS materials would lose their sensing function when the humidity exceeds 80% since the conductivity turns to an increase at a RH >80%, which is due to the saturation of the PEDOT:PSS film with water or a water layer formed on the surface of the film (enabling or enhancing ionic conductivity) [69].

In recent years, the humidity sensors based on PEDOT:PSS are mainly fabricated by spin-coating, spray-coating, or drop-casting. These methods have a few disadvantages, such as film inhomogeneity, an uncontrollable shape and a low production efficiency. The non-porous structure produced therefrom also results in a long sensing response and recovery time [70], which limits the application of these sensors in the areas such as respiratory monitoring, wherein the response/recovery cycling must be faster (shorter) than a single respiratory period (normally in 3–4 s) [67]. In addition, the three fabrication methods mentioned above are generally suitable for large-area manufacturing of macroscopic devices, but not microscale miniaturized devices, which are otherwise crucial for integration with other functional devices [71]. In this regard, new efforts have been made in order to develop alternative methods for film fabrication, with the aim of improving sensor performance.

Thanks to the excellent solution processability of PEDOT:PSS, many other methods have been exploited and developed to fabricate films from the polymer composite. Among them, the dipping method [72] was used to blend PEDOT:PSS with nanofiber fabrics, which was suited for development as a humidity sensor. The surface area and open porosity of nanofiber fabrics help improve the sensing performance through enhanced surface absorption of gas analytes. Inkjet printing technology can also be perfectly compatible with PEDOT:PSS, and the material thus printed is usually suited for exploitation as a gas sensor device. The recent advancement in inkjet printing equipment further renders the film fabrication of PEDOT:PSS regarding morphology uniformness and repeatability, low cost, and adaptability to a wide range of substrates and materials [10,73]. This helps facilitate the research and development of PEDOT:PSS composites as electronic chemosensors.

In Wang’s recent work [71], a micron line humidity sensor (Figure 7a) was fabricated by printing PEDOT:PSS with a femtosecond laser, for which the laser beam was applied directly to PEDOT:PSS in the channel between two electrodes, thus processing the sample into a designed pattern. This micro-fabrication technology combines the advantages of high precision, arbitrary patterning and a wide selection of processing materials. The dimensional size of the sensor device fabricated was about 6 mm² and the effective working area was less than 100 μm². The small size is convenient for integration with other functionalized sensing chips. The sensor exhibited quite a short response/recovery time (0.86 s/0.59 s) (Figure 7e), enabling real-time respiration monitoring of human and rats under different physiological conditions (Figure 7f). Accompanied by human exhalation, the sensor channel is highly moisturized, causing an increased humidity exposure towards the sensor surface. During inhalation, the inhaling air from the atmosphere will reduce the level of humidity around the sensor. The humidity sensor was placed on the skin under the nose of the tester as shown in Figure 7b. The current versus time curve during respiration is shown in Figure 7c,d, indicating that the PEDOT:PSS micron line humidity sensor can effectively monitor the real-time respiratory rate of human motion.

Similarly, Duan et al. [67] improved the sensing performance by limiting the dimension of the sensing layer. As shown in Figure 8a, they designed a PDMS (polydimethylsiloxane) mold with nanogrooves (70 nm in width and 80 nm in depth) and placed it in contact with the PET substrate to form nanochannels. Then PEDOT:PSS aqueous solution was cast into the channels. After the solvent completely evaporated, the PDMS mold was removed from the PET substrate, leaving the solidified PEDOT:PSS in the format of nanowires on the PET substrate (Figure 8b). This nano-confined strategy facilitates the absorption/desorption of water molecules and maximizes the sensor response to moisture (Figure 8c), in contrast to the slow adsorption, diffusion, and desorption as observed in the typical network of polymer films (Figure 8d). The nanoscale humidity sensor showed a high sensitivity (5.46%) and ultrafast response (0.63 s) when changing humidity between 0% and 13%. It also demonstrated real-time monitoring of human respiration (Figure 8e) and excellent mechanical durability and robustness (Figure 8f).

PET, PI (Polyimide) and other substrates perform well in flexibility and possess good adhesion to human skin, which greatly facilitates their application in sensors that can potentially be used in electronic skin, and other biomedical and wearable devices. Similarly, paper also possesses good flexibility, while the material cost is extremely low. In this regard, research effort has been made to develop paper-based humidity sensors by blending with PEDOT:PSS [70,74]. Paper has a strong water-absorption rate, making it easy to blend with PEDOT:PSS simply by dipping the paper in an aqueous dispersion of the polymer. The composite thus fabricated takes the intrinsic porous morphology of paper, highly conducive to diffusion and surface absorption of gas analytes, which is in turn desirable for use as a humidity sensor. These flexible substrates are also perfectly integrated with printing technology, showing good flexibility in several types of flexibility tests, including outer/inner bending, twisting, and stretching. These tests show great promise for applications in various emerging flexible electronics and optoelectronic devices.

Some technical challenges, such as slow response and recovery, still remain for PEDOT:PSS-based humidity sensors. In order to solve these challenges, piezoelectric LiNbO₃ substrate was used to produce surface acoustic waves (SAW), which helped release the water molecules from the sensing layer when the IDT was supplied with a high frequency. As evidenced in Aziz’s work [75,76], as shown in Table 2, SAW could indeed significantly improve the recovery time of the PEDOT:PSS humidity sensor.

In addition, PEDOT:PSS has often been combined with other materials, e.g., polyvinyl alcohol (PVA) [76], ZnSnO₃ [75], or Fe₃O₄/γ-Fe₂O₃ [69] nanoparticles, to produce a polymer composite in porous structure (Figure 9), which is conducive to the adsorption and desorption of water vapor, and is thus suited for development as a humidity sensor. These PEDOT:PSS composites are expected to further improve the sensing performance, as well as enable some special features or functions intrinsic to the nanoparticles encapsulated. For example, by incorporating the Fe₃O₄/γ-Fe₂O₃ nanoparticles into PEDOT:PSS, the nanostructured films became magnetic, meaning that the film could be easily transferred, simply by using a magnet, onto rigid substrates such as silicon, steel and glass, as well as flexible substrates such as elastomers, paper, plastic frames, or metal weaves in arbitrary shapes and topographies without being damaged or broken [69]. The advantage of using ZnSnO₃ nanoparticles as an additive is the wide sensing range (0–90% RH) and the high repeatability (response remains as high as 77% of the initial value after 2 months of continuous operation). Due to the high hydrophilicity of GO, the PEDOT:PSS composite with GO demonstrated a sensitive chemoresistive and dielectric response towards water vapor, making it an ideal candidate as a humidity sensor. Romero et al. [77] reported on a humidity sensor using PEDOT:PSS-GO composite as the capacitive sensing layer, which showed a sensitivity of 1.22 nF/%RH at 1 kHz.

Considering the fact that a humidity sensor with a single active material has a limit in the detection range, some researchers [64,78] chose multiple IDTs fabricated with different active sensor materials connected in a series on a single chip (Figure 6c). For example, GO, PEDOT:PSS, and Methyl Red materials have sensing responses of 0 to 78% RH, 30 to 75% RH, and 25 to 100% RH, respectively. A humidity sensor [78] incorporating all the three sensors on IDT electrodes in a series can detect a full range of humidity from 0% RH to 100% RH with the response and recovery times to be as fast as 1 s and 3.5 s, respectively. Similarly, by connecting the PEDOT:PSS-based portion with the MoS₂-based portion in a series, the humidity sensing device [64] showed high sensitivity (50 kΩ/%RH or 800 Hz/%RH) in a wide range of 0% RH–80% RH. In contrast, if the composite film of PEDOT:PSS and MoS₂ was fabricated as a humidity sensor, interesting phenomena would occur, i.e., an increase in MoS₂ addition would turn the positive resistance response to negative response upon exposure to humidity [79]. This is likely due to the fact that hole carriers generated in MoS₂ nanosheets may be injected into the PEDOT:PSS chains absorbed with water molecules, which in turn results in enhanced electrical transport along the PEDOT:PSS chains.

In addition to the chemoresistive sensor (with the sensing materials bridged between two electrodes), PEDOT:PSS has also been fabricated as an organic field effect transistor (OFET) sensor (Figure 6d), which provides additional signal amplification through the gate modulation. Zafar et al. [80] reported on an OFET sensor for detecting humidity, for which PEDOT:PSS film was used as the active channel layer and n-type silicon as the gate electrode. The source–drain current flow is not only controlled by the gate voltage, but is also modulated by humidity level in the ambient environment. Within the humidity range (40–80% RH) examined, the channel current has been observed to amplify by nearly 29.4 times of its magnitude at a drain source voltage of −40 V and the gate source voltage of −10 V.

Recently, a hydromorphic dielectric elastomer actuator [65] was proposed for high humidity sensing. The device consists of a relatively water-inert acrylic dielectric elastomer layer sandwiched by a pair of hygroscopic PEDOT:PSS electrodes (Figure 6e). The electrodes became softer upon absorption of moisture, allowing for moisture permeation into the dielectric elastomer substrate during electrical activation and readout. The dielectric elastomeric actuation (under constant voltage) was found to increase with increasing humidity, the current leaking through it rising more significantly. This dielectric elastomer actuator-based humidity sensor remained in working order when a mist of water droplets was sprayed on its electrodes.

3.2. Ammonia Detection

Ammonia (NH₃) is a colorless and highly toxic gas that is mostly produced from industry, but also exists naturally in the atmosphere at low-ppb to sub-ppb levels. It has been widely used in various applications such as fertilizers, refrigeration, water purification, and manufacturing for nitrogenous products. At high concentrations, NH₃ can cause irritation to the skin, eyes, nose, throat, and respiratory tract due to its corrosive properties. Exposure to a massive concentration of NH₃ (>5000 ppm) may be fatal within minutes. Therefore, detection of NH₃ has attracted a great deal of attention of environment protection and human health [20,81].

When the PEDOT:PSS film is exposed to NH₃, the lone pair of electrons of the NH₃ molecule interact with the holes of the p-type PEDOT:PSS grains, and such a neutralization interaction leads to a decrease in charge carrier density of the PEDOT domains, which in turn results in a decrease in the conductivity. However, the pristine PEDOT:PSS film exhibits a poor senor response to NH₃ because the PEDOT domains are surrounded by PSS, for which the electrical conductivity of the film is largely determined by the resistive PSS regions, outweighing the conductivity change of the PEDOT domains [82]. Furthermore, the presence of water (moisture) in ambient air also increases the electrical resistance of the sensor based on PEDOT:PSS, causing additional interreference to the sensor signal [12]. Particularly at a high level of humidity, more moisture would react with NH₃ to produce NH₄OH, which leads to a great fluctuation of resistance change between the introduction of NH₃ and discharge of the NH₃ process [82]. Therefore, the influence of moisture must be taken into account in the design of NH₃ sensors. Some critical parameters for evaluation of NH₃ sensors were listed in Table 2. The stability of sensors also remains crucial for precise, repeated measurements of NH₃ and other gases, especially under trace concentration levels. For example, the baseline resistance of pristine PEDOT:PSS film in one study was found to increase from 3.6 kΩ to 4.1 kΩ after five cycles of testing [82]. Such a baseline shift represents one of the common technical challenges for chemosensors that limits their practical applications.

Electronic chemosensors based on a PEDOT:PSS film generally exhibit low sensitivity in response to NH₃, mainly due to the limited surface area and nonporous structure. Aiming to enhance the sensing sensitivity, PEDOT:PSS in various nanostructures, including nanowires [68] and nanofibers [66], have been fabricated by either a complex nano-confined strategy, or high voltage electro-spinning. These nanostructured materials demonstrate significant enhancement in sensitivity compared to the pristine films. For example, Duan et al. [68] prepared PEDOT:PSS nanowires using a PDMS mold patterned with nanogrooves, and in comparison with the PEDOT:PSS thin film sensors, these nanowires showed a significantly higher sensitivity and a faster response to NH₃, as shown in Figure 10. The increased sensor response was largely attributed to their high surface-volume ratio. These observations indicate that appropriate structural engineering of sensor materials at the nanoscale could enhance the sensor performance, especially the response sensitivity for detection of a low gas concentration.

As mentioned above, the inkjet printing technique has been proven to be effective for fabricating thin films and nanostructures of polyremes like PEDOT:PSS, particularly on flexible substrates like plastic. Inkjet printing is simple, low-cost and capable of large area fabrication with high uniformity, which, combined, make it an ideal technique to prepare flexible gas sensors from PEDOT:PSS films [83]. Moreover, PEDOT:PSS can also be printed together with other functional materials (e.g., graphene [84], FeCl₃ [82]) through appropriate solution processing. Inkjet printing has now become one of the most popular fabrication methods for making flexible gas sensors, taking the advantages of precise control of film thickness and uniformness as deposited. The technical maturation of such a fabrication method will likely promote the research and development of flexible electronics in general, way beyond the chemosensor fields.

Currently, the main drawback of pristine PEDOT:PSS film used in NH₃ sensors lies in its low conductivity and gas sensitivity. This technical problem can be overcome by blending PEDOT:PSS with other electroactive nanomaterials, such as MWCNTs [83], graphene [12,84,85], reduced graphene oxide (rGO) [86] and silver nanowires (AgNWs) [20,87]. These nanomaterials can be mixed homogeneously with the polymer matrix, producing maximal interfacial contact and helping improve the sensing performance. The doped nanomaterials were found to be capable of enhancing significantly the conductivity of PEDOT:PSS, as well as the sensing performance in comparison to the pristine polymer. Guo et al. [20,87] fabricated PEDOT:PSS composite films doped with AgNWs by spin-coating successively a AgNWs dispersion and PEDOT:PSS aqueous solution on PET substrate and tested the chemoresistive sensing for NH₃. The surface bumps at the interface regions induced by the embedded AgNWs under the PEDOT:PSS film can enhance the absorption of NH₃ molecules and thus increase the interface resistance between AgNWs and PEDOT:PSS, which leads to a significant enhancement of detection sensitivity towards NH₃. Inclusion of graphene or rGO in PEDOT:PSS was also found to be able to increase the conductivity depending on the doping concentration and mesoscopic interfacial structure of the blending. The incorporation of graphene in PEDOT:PSS led to a considerable enhancement of the NH₃ response, which was ascribed to a combination of several factors such as an increase in the specific surface area, intrinsic sensing properties of graphene, and π-π interaction between graphene and PEDOT:PSS (helping facilitating the charge transfer) [12]. By doping rGO into PEDOT:PSS [86], a large number of charge carriers (both polarons and bi-polarons) can be generated in the polymer matrix. These charge carriers can be easily transported through the polymer chain, helping improve the chemoresistive sensor response of the PEDOT:PSS film. Moreover, the doping with rGO would also improve the surface roughness and the high surface/volume ratio of PEDOT:PSS film, which are both crucial for enhancing the gas absorption and electrical interaction with the polymer matrix [85].

3.3. CO and CO₂ Detection

For CO or CO₂ sensors, PEDOT:PSS is often used as a host and guest material in hybrid systems due to its good electrical conductivity, film-forming properties and solution processability. The gas sensitivity and selectivity of PEDOT:PSS to CO [88,89] can be improved by blending PEDOT:PSS with metal complexes that have a strong binding towards CO. For example, PEDOT:PSS films doped with 0.1wt. % Co(salen) or Fe(salen) complexes demonstrated a high chemoresistive sensor response towards CO (a flow rate of 19.0 mL min⁻¹ and 8 mL s⁻¹, respectively.), −25.0 ± 0.05% and −31.32 ± 0.88%, respectively. A new pyrimidine-fused heterocyclic compound, bis(2hydroxyphenyl)dihydropyrido [2,3-d:6,5-d]dipyrimidine-tetraone (B2HDDT), was also employed as a molecular dopant for PEDOT:PSS by Memarzadeh et al. [90] B2HDDT contains numerous functional groups that can form hydrogen bonds with CO and PEDOT:PSS, thus helping capture CO within the polymer matrix and improve the detection sensitivity. In Kim’s recent work [91], a porous PEDOT:PSS-MWCNTs composite was exploited for CO sensing. Although the surface coating of PEDOT:PSS reduced the number of adsorption sites on CNT, the conductive polymer layer thus coated helps bridge the CNTs electrically and form a network with high conductivity, which facilitates the long range charge transport and ultimately leads to enhancement in gas sensing.

The graphene layer and the PEDOT:PSS layer were printed on PET layer by layer to manufacture the CO₂ sensor [92]. The variation of the electrical conductivity of graphene due to gas molecule adsorption and the conductivity of the graphene layer increases when the concentration of the CO₂ gas increases. The main reason to use a layer of PEDOT:PSS under the sensing layer of graphene is to realize a uniform layer over IDT electrodes, guaranteeing continuity of the resistive contact between IDT fingers and a layer with a resistance value higher than the pure IDT electrode. This allows for making dominant the effect of the resistance variation of the graphene layer, super-imposed to the PEDOT:PSS layer. Considering the effect of exogenous factors such as humidity on the PEDOT:PSS layer, graphene as the outer layer can also performed as a shield.

The existence of moisture is critical for CO₂ detection. Chuang et al. [93] developed a CO₂ sensing material based on PEDOT:PSS blended with PANI. The effects of humidity on PEDOT:PSS and PANI counteract each other in the conductivity change characteristic. As CO₂ and H₂O molecular adsorption increased, the conductivity of PEDOT:PSS-PANI increased because of the carbonate formation between CO₂ and the secondary amine backbone of PANI. This resulted in a high selectivity between CO₂ and H₂O molecules of the developed PEDOT:PSS-PANI sensing composite.

3.4. NO₂ Detection

NO₂ is a toxic air pollutant mainly released in the automotive industry and vehicles. It greatly threatens environmental security due to its role as a source of photochemical smog and acid rain. Therefore, it is demanding to develop inexpensive, sensitive, selective and simple devices to detect low concentrations of NO₂ gas at room temperature ambient conditions for environmental monitoring [94]. NO₂ is a strong electron withdrawing molecule that can easily deplete electrons from the sensing material, causing changes in the conductivity. PEDOT:PSS composites mixed with semiconducting metal oxides (e.g., WO₃ [94,95], TiO₂ [96]) have been proven to be effective for detection of NO₂, even at room temperature. Metal oxide semiconductors have been commonly used as chemoresistive materials for sensing redox active gases or chemical analytes through interfacial charge transfer interaction. However, the metal oxides normally suffer from the high operation temperature (typically 200 to 500 °C). The new approach with PEDOT:PSS composites may provide an alternative way to solve this technical challenge for metal oxide sensors.

Blending PEDOT:PSS with metal oxide semiconductors (especially in the format of nanoparticles) provides dual functions. On the one hand, PEDOT:PSS provides conducting channels for the charge carriers, thereby producing a much lower initial resistance, helping enhance the signal-to-noise ratio for the sensing response. On the other hand, the heterojunctions formed at the interface between metal oxide and PEDOT:PSS would provide abundant adsorption sites for gas analytes, thus maximizing the chemoresistive sensing response. Indeed, a chemoresistive sensor based on PEDOT:PSS-WO₃ composite exhibited a low initial resistance (~870 Ω) and a good sensing response (~1.2) towards 50 ppb NO₂ gas at room temperature, with a response and recovery time of 45.1 and 88.7 s, respectively [95].

3.5. Volatile Organic Compounds (VOCs) Detection

The increased emission of harmful VOCs, such as methanol [97,98,99,100], acetone [101], formaldehyde [102], and nitrobenzene [103], has been widely considered as a serious threat to the environment and to human health, as these toxic VOCs are proven to be correlated with the increasing cases of many diseases [99], such as allergies, asthma, cancer, and emphysema. Therefore, it is essential to monitor the concentration of VOCs in the environment in real time.

Many VOCs are chemically or electrically active, meaning that they are capable of inducing a change in the conductivity of the PEDOT:PSS, thus generating a chemoresistive signal response. Various substrates such as PDMS, PET, paper, even cotton [101] have been used for the construction of PEDOT:PSS sensors for gas phase detection of VOCs. Fabrication of PEDOT:PSS films on a substrate can be realized with various processing methods, including drop-casting [100], dipping method [101], inkjet printing [102], etc. More interesting, Sarkar et al. [99] adopted a novel fabrication approach by firstly creating quasi-periodic cracks in PEDOT:PSS film using strain, followed by engineering the crack morphology with controlled plasma etching (Figure 11). These engineered cracks provide electrical conduction pathways that can be turned on and off in response to absorption of methanol vapor, which enables ultra-high sensitivity for chemoresistive sensing with an on/off ratio as high as 10⁶. A variety of nanomaterials have been blended with PEDOT:PSS to fabricate composites suited for chemoresistive sensing of VOCs, as listed in Table 2. Most of these composites possess a large surface area that is conducive to absorption of gas analytes, resulting in a high sensor performance.

Table 2. Comparison of PEDOT:PSS-based electrical chemosensors for different analytes.

Sensing Material	Mechanism	Sensor Structure	Analyte	Sensitivity	Response/Recovery Time	Sensing Range	Reference
PEDOT:PSS	Capacitance	IDT	Humidity	-	<30 s/<1 min	52.0–93.4% RH	[63]
PEDOT:PSS/MoS2	Impedance	Dual IDT’s in series Sensor array	Humidity	50 kΩ/%RH, 850 Hz/%RH	0.5 s/0.8 s	0–80% RH	[64]
PEDOT:PSS	Resistance	Dielectric elastomer actuator	Humidity	-	-	30–90%RH	[65]
PEDOT:PSS	Resistance	Nanowires	Humidity	5.46%	0.63 s/2.05 s	0–60% RH	[67]
PEDOT:PSS-Fe3O4/γ-Fe2O3	Resistance	electrodes on substrate	Humidity	0.65%/ΔRH	>1 s/>1 s	30–70%RH	[69]
PEDOT:PSS-Graphene	Resistance	paper substrate	Humidity	-	-	20–90% RH	[70]
PEDOT:PSS	Resistance	micron line	Humidity	0.19% (ΔR/R0)/%RH	0.86 s/0.59 s	11–69% RH	[71]
PEDOT:PSS)/polyacrylonitrile fabrics	Resistance	IDT	Humidity	110%	2 s/7 s	0–100% RH	[72]
PEDOT:PSS-ZnSnO3	Impedance	IDT with SAW effect	Humidity	-	0.2 s/0.2 s	0–90%RH	[75]
PEDOT:PSS–PVA	Impedance Capacitance	IDT with SAW effect	Humidity	350 Ω/%RH 28 pF/%RH	0.63 s/0.56 s	0–80% RH	[76]
PEDOT:PSS/GO	Capacitance	Two interdigitally arranged IDT	Humidity	1.22 nF/%RH	-	25–85% RH	[77]
PEDOT:PSS-MoS2	Impedance based	Glass substrates	Humidity	-	-	50–75% RH	[79]
PEDOT:PSS-Graphene	Resistance	IDT	NH3	116.38% (1000 ppm)	7.7 min/10 min	−1500 ppm	[12]
AgNWs/PEDOT:PSS	Resistance	PET substrate	NH3	5% (1 ppm)	-	0.5–25 ppm	[20]
PEDOT:PSS nanowire	Resistance	Silicon substrate	NH3	0.8% (3.2 ppm)	57 s/163 s	3–60 ppm	[66]
Si/PEDOT:PSS	Current	OFET	NH3	-	13 s/8 s	-	[81]
ITO/PEDOT:PSS			NH3	-	29 s/22 s
PEDOT:PSS-FeCl3	Resistance	IDT	NH3	7.6% (0.5 ppm)	20 s	0.1–200 ppm	[82]
PEDOT:PSS-MWCNTs	Resistance	IDT	NH3	73.7% (1000 ppm)	-	0–1000 ppm	[83]
PEDOT:PSS-graphene	Resistance	IDT	NH3	6.9% (1000 ppm)	3 min/5 min	25–1000 ppm	[84]
(CuTSPc@3D-(N)GF)/(PEDOT-PSS)	Resistance	IDT	NH3	-	-	1–1000 ppm	[85]
PEDOT-PSS rGO	Resistance	IDT	NH3	-	1.05 min/2.84 min	-	[86]
PEDOT:PSS-Co(salen)	Resistance	IDT	CO	25.0 ± 0.05%	-	0.5–10.0% CO (v/v) N2	[88]
PEDOT:PSS-Fe(III)(salen)	Resistance	IDT	CO	31.32 ± 0.88%	38 s/5 s	-	[89]
PEDOT:PSS-B2HDDT	Resistance	PET substrate	CO	55% (common gas)	-	0–66 vol%	[90]
PEDOT:PSS-MWCNTs	Resistance	PDMS substrate	CO	0.05 ± 0.004% (1000 ppm)	10.6 ± 0.4 s/24.6 ± 1.2 s	250–1000 ppm	[91]
Graphene/PEDOT:PSS	Resistance	PET substrate	CO2	4.7 µΩ/Ω/ppm (420 ppm)	-	400–4200 ppm	[92]
PEDOT:PSS-PANI	Resistance	IDT	CO	3.24% (1000 ppm)	-	500–2000 ppm	[93]
PEDOT:PSS-WO3	Resistance	IDT	NO2	2.31 (80 ppm)	-	10–80 ppm	[94]
PEDOT:PSS-WO3	Resistance	IDT	NO2	-	45.1 s/88.7 s	50–220 ppb	[95]
PEDOT:PSS-TiO2	Current	IDT	NO2	-	-	10–130 ppb	[96]
PEDOT:PSS-graphene	Resistance	IDT	Methanol	13.5% (50 ppm)	12 s/32 s	1–1000 ppm	[97]
PEDOT:PSS-GO	Resistance	IDT	Methanol	11% (35 ppm)	3.2 s/16 s	3–700 ppm	[98]
PEDOT:PSS thin film	Resistance	PDMS substrate	Methanol	∼106 (300 ppm)	<5 s/<5 s	6–300 ppm	[99]
PEDOT:PSS-Ti3C2Tx	Resistance	IDT	Methanol	5.54	-	-	[100]
PEDOT:PSS-cotton	Current	Cotton	Acetone	53%	1 min/2 min	1–30% (acetone solvent)	[101]
PEDOT:PSS-MWCNTs	Resistance	IDT	Formaldehyde	30.5% (10 ppm)	45 s/<7 s	10–200 ppm	[102]
PEDOT:PSS-graphite nanosheets	Resistance	Glass substrate	Nitroaromatics	-	1.15 min/1.88 min	-	[103]

Table 2. Comparison of PEDOT:PSS-based electrical chemosensors for different analytes.

Sensing Material	Mechanism	Sensor Structure	Analyte	Sensitivity	Response/Recovery Time	Sensing Range	Reference
PEDOT:PSS	Capacitance	IDT	Humidity	-	<30 s/<1 min	52.0–93.4% RH	[63]
PEDOT:PSS/MoS2	Impedance	Dual IDT’s in series Sensor array	Humidity	50 kΩ/%RH, 850 Hz/%RH	0.5 s/0.8 s	0–80% RH	[64]
PEDOT:PSS	Resistance	Dielectric elastomer actuator	Humidity	-	-	30–90%RH	[65]
PEDOT:PSS	Resistance	Nanowires	Humidity	5.46%	0.63 s/2.05 s	0–60% RH	[67]
PEDOT:PSS-Fe3O4/γ-Fe2O3	Resistance	electrodes on substrate	Humidity	0.65%/ΔRH	>1 s/>1 s	30–70%RH	[69]
PEDOT:PSS-Graphene	Resistance	paper substrate	Humidity	-	-	20–90% RH	[70]
PEDOT:PSS	Resistance	micron line	Humidity	0.19% (ΔR/R0)/%RH	0.86 s/0.59 s	11–69% RH	[71]
PEDOT:PSS)/polyacrylonitrile fabrics	Resistance	IDT	Humidity	110%	2 s/7 s	0–100% RH	[72]
PEDOT:PSS-ZnSnO3	Impedance	IDT with SAW effect	Humidity	-	0.2 s/0.2 s	0–90%RH	[75]
PEDOT:PSS–PVA	Impedance Capacitance	IDT with SAW effect	Humidity	350 Ω/%RH 28 pF/%RH	0.63 s/0.56 s	0–80% RH	[76]
PEDOT:PSS/GO	Capacitance	Two interdigitally arranged IDT	Humidity	1.22 nF/%RH	-	25–85% RH	[77]
PEDOT:PSS-MoS2	Impedance based	Glass substrates	Humidity	-	-	50–75% RH	[79]
PEDOT:PSS-Graphene	Resistance	IDT	NH3	116.38% (1000 ppm)	7.7 min/10 min	−1500 ppm	[12]
AgNWs/PEDOT:PSS	Resistance	PET substrate	NH3	5% (1 ppm)	-	0.5–25 ppm	[20]
PEDOT:PSS nanowire	Resistance	Silicon substrate	NH3	0.8% (3.2 ppm)	57 s/163 s	3–60 ppm	[66]
Si/PEDOT:PSS	Current	OFET	NH3	-	13 s/8 s	-	[81]
ITO/PEDOT:PSS			NH3	-	29 s/22 s
PEDOT:PSS-FeCl3	Resistance	IDT	NH3	7.6% (0.5 ppm)	20 s	0.1–200 ppm	[82]
PEDOT:PSS-MWCNTs	Resistance	IDT	NH3	73.7% (1000 ppm)	-	0–1000 ppm	[83]
PEDOT:PSS-graphene	Resistance	IDT	NH3	6.9% (1000 ppm)	3 min/5 min	25–1000 ppm	[84]
(CuTSPc@3D-(N)GF)/(PEDOT-PSS)	Resistance	IDT	NH3	-	-	1–1000 ppm	[85]
PEDOT-PSS rGO	Resistance	IDT	NH3	-	1.05 min/2.84 min	-	[86]
PEDOT:PSS-Co(salen)	Resistance	IDT	CO	25.0 ± 0.05%	-	0.5–10.0% CO (v/v) N2	[88]
PEDOT:PSS-Fe(III)(salen)	Resistance	IDT	CO	31.32 ± 0.88%	38 s/5 s	-	[89]
PEDOT:PSS-B2HDDT	Resistance	PET substrate	CO	55% (common gas)	-	0–66 vol%	[90]
PEDOT:PSS-MWCNTs	Resistance	PDMS substrate	CO	0.05 ± 0.004% (1000 ppm)	10.6 ± 0.4 s/24.6 ± 1.2 s	250–1000 ppm	[91]
Graphene/PEDOT:PSS	Resistance	PET substrate	CO2	4.7 µΩ/Ω/ppm (420 ppm)	-	400–4200 ppm	[92]
PEDOT:PSS-PANI	Resistance	IDT	CO	3.24% (1000 ppm)	-	500–2000 ppm	[93]
PEDOT:PSS-WO3	Resistance	IDT	NO2	2.31 (80 ppm)	-	10–80 ppm	[94]
PEDOT:PSS-WO3	Resistance	IDT	NO2	-	45.1 s/88.7 s	50–220 ppb	[95]
PEDOT:PSS-TiO2	Current	IDT	NO2	-	-	10–130 ppb	[96]
PEDOT:PSS-graphene	Resistance	IDT	Methanol	13.5% (50 ppm)	12 s/32 s	1–1000 ppm	[97]
PEDOT:PSS-GO	Resistance	IDT	Methanol	11% (35 ppm)	3.2 s/16 s	3–700 ppm	[98]
PEDOT:PSS thin film	Resistance	PDMS substrate	Methanol	∼106 (300 ppm)	<5 s/<5 s	6–300 ppm	[99]
PEDOT:PSS-Ti3C2Tx	Resistance	IDT	Methanol	5.54	-	-	[100]
PEDOT:PSS-cotton	Current	Cotton	Acetone	53%	1 min/2 min	1–30% (acetone solvent)	[101]
PEDOT:PSS-MWCNTs	Resistance	IDT	Formaldehyde	30.5% (10 ppm)	45 s/<7 s	10–200 ppm	[102]
PEDOT:PSS-graphite nanosheets	Resistance	Glass substrate	Nitroaromatics	-	1.15 min/1.88 min	-	[103]

Wang et al. [100] fabricated a methanol gas sensor by blending PEDOT:PSS with Ti₃C₂T_x at a mass ratio of 4:1. As one of the most widely studied two-dimensional transition metal carbides (MXene), Ti₃C₂T_x has been proven to be a promising gas-sensing material that can be used to detect ultralow concentration of gases at room temperature. The high sensing sensitivity of Ti₃C₂T_x is due to the large specific surface area and the plenty of surface functional groups that endow Ti₃C₂T_x with abundant active sites for interacting with gas molecules. When tested at room temperature, the PEDOT:PSS-Ti₃C₂T_x composite possessed a high response ratio of the largest response and the second largest response (5.54) and an enhanced response compared to pure PEDOT:PSS and pure Ti₃C₂T_x for methanol gas. The high sensing response was due to the increased interlayer spacing between PEDOT:PSS and Ti₃C₂T_x (allowing for increased absorption of gas analytes) while still maintaining a high conductivity.

The combination of PEDOT:PSS with other carbon nanomaterials (graphene [97], GO [98], MWCNTs [102], etc.) represents another potential solution to enhance the sensitivity and selectivity of the chemoresistive sensing for VOCs. The incorporation of these carbon materials into PEDOT:PSS resulted in a significant increase in charge carrier concentration. For example, the conductivity of a pristine PEDOT:PSS film and the composite blended with N-doped graphene quantum dots, were measured to be 650 and 1365 S cm⁻¹, respectively, using a 4-point probe technique under an applied current of 10 nA [97]. Moreover, the high density of chemical groups (especially hydroxyl and carboxylic groups) on GO can also enhance the surface adsorption of VOCs through hydrogen bonding along with other chemical interactions, which in turn may lead to much improved detection sensitivity towards VOCs [98].

4. Conclusions and Perspective

In conclusion, significant achievements have been achieved in PEDOT:PSS and its composites as applied in electrochemical and electronic chemosensors over the past decade, for which a wealth of novel materials, design principles, and sensing mechanisms have been developed. Most of the research advancements relied on the design and optimization of PEDOT:PSS composites, in correlation with the specific film and nanostructure fabrication techniques that are suited for production of a sensor device in large scale and with sufficient reproducibility. In this regard, the emerging nanomaterials (e.g., those based on carbons, metal oxides, etc.) and nanoscale engineering methods and instrumentation have now commonly been employed to help the fabrication of PEDOT:PSS composites and film printing on various substrates, including the flexible ones that are ideal for manufacturing wearable devices.

Although PEDOT:PSS has many advantages such as an adjustable electrical conductivity, mechanical flexibility, strong solution processability and good biocompatibility, there are still some technical concerns that need to be solved or improved before the PEDOT:PSS-based sensors can be practically used, especially in the fields of flexible or wearable electronics. For electrochemical sensors, PEDOT:PSS or its composites with other nanomaterials are often coated onto a substrate to function as a working electrode. One of the existing problems with such electrodes is that the PEDOT:PSS coating may swell or even fall off the electrode when immersed in aqueous solution. Although some research efforts (e.g., covered with a Nafion film) have been made to improve the robustness of PEDOT:PSS coating, the extra coverage layer like Nafion would likely inhibit the contact between PEDOT:PSS and analytes. The same water-swelling problem may also be encountered in electronic sensors employing PEDOT:PSS film as the active material. When operated in an ambient atmosphere with a high humidity, the absorption and condensation of moisture on the film could cause degradation of the electrical conductivity or sensing performance. Solutions to this water-related stability problem are expected to rely on the design of a new material structure, for which appropriate additives may be blended homogeneously with the polymer to enhance the hydrophobicity (thus minimizing the water absorption) while still maintaining the high electrical conductivity and solution processability intrinsic to PEDOT:PSS.

As a typical polymer that is suited for development as flexible or wearable electronics, even with self-healing characteristics, PEDOT:PSS-based chemosensors have been extensively exploited with the aim to be adapted with flexible substrate or integrated with wearable systems. Specific research efforts have also been made to shrink the size of the sensors so as to be suited for integration with other electronic devices like data transmission and communication. However, traditional film fabrication methods and the associated structure engineering techniques are not suited for the construction of small devices or system miniaturization. In this regard, the emerging nanofiber and cleanroom technologies (e.g., nanopatterning, nano-lithography, nano-templating, etc.) will provide great potential for the fabrication of nanostructured films or devices, which in turn would facilitate the system integration and miniaturization. With the versatile coating and structural engineering techniques, PEDOT:PSS or its composites can be modified onto other flexible substrates with a diverse shape and mechanical properties, such as cotton fiber, paper, PET, etc., which are not only flexible, stretchable or bendable, but moreover have a low cost and are environmentally benign, thus serving as ideal candidates for use in future wearable electronics. Moreover, the tensile, mechanical strength and electrical conductivity of PEDOT:PSS films can be adjusted by adding solvents such as DMSO, EG, etc. [104]. This provides more options to modulate and optimize the electrical and mechanical properties of PEDOT:PSS in order to match the technical needs of different types of sensors.