Immunosensors for Detecting Cortisol in Biological Samples: History
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Contributor:
Chrysoula-Evangelia Karachaliou
,
Georgios Koukouvinos
,
Dimitrios Goustouridis
,
Ioannis Raptis
,
Sotirios Kakabakos
,
Panagiota Petrou
,
Evangelia Livaniou

Cortisol is a steroid hormone that is involved in a broad range of physiological processes in human/animal organisms. Cortisol levels in biological samples is a valuable biomarker -e.g., of stress and stress-related diseases; thus, cortisol determination in biological fluids, such as serum, saliva, and urine, is of great clinical value. Although cortisol analysis can be performed with chromatography-based analytical techniques, such as liquid chromatography – tandem mass spectrometry (LC-MS/MS), conventional immunoassays (radioimmunoassays (RIAs), enzyme-linked immunosorbent assays (ELISAs), etc.) are considered the “gold standard” analytical methodology for cortisol, due to their high sensitivity along with a series of practical advantages, such as low-cost instrumentation, fast and easy to perform assay-protocol, and high sample throughput. Research efforts have pointed at the replacement of conventional immunoassays by cortisol immunosensors, which may offer further improvements in the field, such as real-time analysis at the point-of-care (e.g., continuous cortisol monitoring in sweat through wearable electrochemical sensors).

  • biological samples
  • blood plasma/serum
  • cortisol
  • electrochemical immunosensors
  • biomarkers
  • optical immunosensors
  • saliva
  • sweat

1. Electrochemical Cortisol Immunosensors

The first cortisol immunosensors, reported in the mid-1990s [1][2] as already mentioned, were electrochemical. In the meantime, many more electrochemical immunosensors for cortisol have been described in the literature, while some recent review articles have provided accumulative information on cortisol electrochemical sensors [3][4].

During the last decade, various wearable electrochemical sensing platforms, which in general are considered ideal for analyzing sweat samples [5], have been developed and applied to the immunodetection of cortisol in sweat, as critically presented in previous review papers [6][7]. Moreover, several electrochemical cortisol immunosensors for sweat analysis have been described in the literature during the last couple of years (2020-2022) [8][9][10][11][12][13]. Tear analysis by means of electrochemical cortisol immunosensing has also been reported [14].

In Table 1, the researchers present most of the articles published in the last decades regarding the development of electrochemical immunosensors for the detection of cortisol in a variety of samples, ranging from plain buffer solutions [1][15][16], to complex biological specimens. As shown (Table 1), electrochemical cortisol immunosensors have been mainly applied to the analysis of saliva samples [17][18][19][20][21][22][23][24][25][26][27][28][29][30][31], and, to a less extent, blood plasma or serum [32][33][34][35][36][37][38], as well as interstitial fluid [31][39], buffer solutions of rat adrenal gland acute slices [26] and zebra-fish whole body [19]. Early developed electrochemical immunosensors applied to detect cortisol in vivo, in dialysates of the extracellular fluid of animal brain (amygdala region) or in dialysates of circulating blood in conscious animals, are also listed in Table 1 [2][40]. Moreover, as above mentioned, cortisol electrochemical immunosensors have been employed to analyze human/artificial sweat samples [8][9][10][11][24][41][42][43][44]. The underlying immunoassay principle and the electrochemical detection/signal principle of each sensor have been included in Table 1, while cortisol concentrations corresponding to the working range and/or limit of detection (LOD) have been listed as well.

Table 1. Electrochemical cortisol immunosensors.
Immunoassay Principle Signal Transduction
Principle		 Biological Sample Range/LoD Reference
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab 1, immobilized onto gold microelectrodes)		 Cyclic voltammetry Buffer 10 pM–500 nM/
1 pM		 [15]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab, immobilized onto silver/silver oxide (Ag/AgO)—polyaniline nanocomposites)		 Cyclic voltammetry Buffer 1 pM–1 μM
0.64 pM		 [16]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab co-immobilized with HRP on the sensor electrode)		 Amperometry Buffer 10−7–10−5 M [1]
Competitive
(Competition between free cortisol and a BSA-cortisol conjugate immobilized onto magnetic beads for binding to an anti-cortisol Ab labeled with silver nanoclusters (AgNCs)		 Photoelectrochemistry Saliva 0.0001–100 ng/mL/
0.06 pg/mL		 [18]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on polyaniline-modified graphene electrodes)		 Electrochemical impedance spectroscopy Saliva (canine) 0.0005–50 μg/mL/
3.57 fg/mL		 [17]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab labeled with ferrocene-tags and immobilized on a modified tin-doped indium oxide electrode)		 Cyclic voltammetry; square wave voltammetry artificial saliva and zebrafish whole-body 0.001–50 ng/mL/
1.03 pg/mL		 [19]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on a AuNP/MoS2/AuNP–modified screen-printed electrode)		 Differential pulse voltammetry Saliva 0.5–200 nM/
0.11 nM		 [20]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab covalently immobilized on NiO thin film/ITO 2 electrodes)		 Cyclic voltammetry,
Differential pulse voltammetry		 Saliva 1 pg/mL–10 μg/mL/
0.32 pg/mL		 [21]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab covalently immobilized onto micro-Au electrodes)		 Electrochemical impedance spectroscopy Saliva 1 pg/mL–10 ng/mL/
0.87 ± 0.12 pg/mL		 [22]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab co-immobilized with BSA on glassy carbon electrodes that had been coated with tin disulfide nanoflakes)		 Cyclic voltammetry, differential pulse voltammetry Saliva 100 pM–100 μM/
100 pM		 [23]
Competitive
(Competition between an ALP-labeled cortisol conjugate and free cortisol for binding to an anti-cortisol Ab indirectly immobilized on disposable graphite screen-printed electrodes)		 Square wave voltammetry Saliva 0.5–55.1 ng/mL/
1.7 ng/mL		 [25]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on electroreduced graphene oxide deposited on screen-printed electrodes)		 Electrochemical chronoamperometry Saliva, sweat 0.1 ng/mL [24]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab covalently immobilized on reduced graphene oxide channels between two planar electrodes)		 Resistance Human saliva and buffer solution of rat adrenal gland acute slices 10 pg/mL [26]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on Au-substrates modified with ZnO nanostructures (1D nanorods, 2D nanoflakes))		 Cyclic voltammetry Saliva 1 pM [27]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab covalently immobilized on microfabricated interdigitated microelectrodes)		 Cyclic voltammetry Saliva 10 pg/mL–100 ng/mL/
10 pg/mL		 [28]
Competitive
(Competition between a GOD 3–cortisol conjugate and free cortisol for binding to an anti-cortisol Ab immobilized on platinum electrodes;
lateral and vertical fluid control mechanisms were integrated in the sensor)		 Amperometry Saliva 0.1–10 ng/mL [29]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on gold microelectrode arrays)		 Electrochemical impedance spectroscopy Saliva and interstitial fluid 1 pM–100 nM [29]
Competitive
(Competition between free cortisol and a cortisol analog covalently immobilized on single-walled carbon nanotubes and free cortisol for binding to an anti-cortisol Ab)		 Resistance/conductance Saliva 1 pg/mL–10 ng/mL/
1 pg/mL		 [30]
Competitive
(Competition between cortisol immobilized on naflon pretreated glassy carbon electrodes and free cortisol for binding to a biotinylated anti-cortisol Ab; detection was performed via reaction with HRP–streptavidin)		 Electrochemical impedance spectroscopy, cyclic voltammetry Plasma 0.1–1000 ng/mL/
0.05 ng/mL		 [33]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab co-immobilized with GOD on gold electrodes)		 Amperometry Plasma
(fish)		 1.25–200 ng/mL [34]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab, immobilized on interdigitated gold microelectrodes)		 Cyclic voltammetry Plasma 10 pg/mL–500 ng/mL/
10 pg/mL		 [35]
Competitive
(Competition between an ALP-labeled cortisol conjugate and free cortisol for binding to an anti-cortisol Ab covalently immobilized on gold electrodes.		 Amperometry Serum 0–250 ng/mL/
13.4 ng/mL		 [32]
Competitive
(Competition between an ALP-labeled cortisol conjugate and free cortisol for binding to an anti-cortisol Ab immobilized through protein A on magnetic particles; the immunocomplexes formed were trapped on the surface of screen-printed electrodes with a small magnet and ALP activity was monitored)		 Differential pulse voltammetry Serum 5 × 10−3–150 ng/mL/
3.5 pg/mL		 [37]
Competitive
(Competition between an HRP-labeled cortisol conjugate and free cortisol for binding to an anti-cortisol Ab immobilized on gold electrodes functionalized with a AuNP–protein G–DTBP 4 scaffold)		 Square wave voltammetry Buffer, Serum 50–2,500 pg/mL/
16 pg/mL		 [36]
Noncompetitive
(Direct binding of cortisol and cortisone (transformed into cortisol via the enzyme 3α-hydroxysteroid dehydrogenase) to an anti-cortisol Ab immobilized on gold nanowires/working electrodes)		 Square wave voltammetry Buffer, Serum 10–80 μM [38]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on L-cys 5–AuNPs–MXene-modified electrodes)		 Amperometry Artificial Sweat 5–180 ng/mL/
0.54 ng/mL		 [8]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on the surface of flexible screen-printed electrodes coated with AuNPs)		 Differential pulse voltammetry Sweat 7.47 nM [9]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab, immobilized on a flexible electrode prepared on polydimethylsiloxane modified with multiwalled carbon nanotubes and AuNPs)		 Cyclic voltammetry, differential pulse voltammetry Sweat 1 fg/mL–1 μg/mL/
0.3 fg/mL		 [10]
Competitive
(Competition between an HRP–cortisol conjugate and free cortisol for binding to an anti-cortisol antibody immobilized on graphene-based electrode)		 Amperometry Sweat 0.43–50.2 ng/mL [11]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol antibody immobilized on a conductive carbon yarn functionalized with ellipsoidal Fe2O3 particles)		 Cyclic voltammetry Sweat 1 fg/mL–1 μg/mL/
0.005 fg/mL		 [41]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on MoS2 sheets integrated into a nanoporous flexible electrode system)		 Electrochemical impedance spectroscopy Sweat 1–500 ng/mL/
1 ng/mL		 [42]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on ZnO thin film deposited on a flexible nanoporous polyamide membrane; room temperature ionic liquids were employed to enhance sensor stability)		 Electrochemical impedance spectroscopy Sweat 10–200 ng/mL/
10 ng/mL		 [43]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on a ZnO thin film deposited on a flexible nanoporous polyamide membrane)		 Electrochemical impedance spectroscopy Sweat 10–200 ng/mL/
1 ng/mL		 [44]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab, covalently immobilized on a gold microelectrode array)		 Electrochemical impedance spectroscopy Interstitial fluid 1 pM–100 nM [39]
Competitive
(Competition between free cortisol and an HRP–cortisol conjugate for binding to an anti-cortisol antibody immobilized on a platinum electrode)		 Amperometry Dialysates of extracellular fluid of
animal brain, amygdala region (sheep)		 0–100 ng/mL
(in vitro measurement)		 [40]
Competitive
(Competition between HRP–cortisol conjugate and free cortisol for binding to an anti-cortisol antibody immobilized on platinum electrodes)		 Potentiometry Dialysates of animal circulating blood (sheep, cattle, rat) 0.3 μg/100 mL [2]
1 Ab: antibody. 2 ITO: indium tin oxide. 3 GOD: glucose oxidase. 4 DTBP: dimethyl 3,3′-dithiobispropionimidate.2HCl. 5 L-cys: L-cysteine.

2. Optical Cortisol Immunosensors

The first optical cortisol immunosensors were developed in the late 2000s. These sensors, which have been based on the surface plasmon resonance (SPR) detection principle [45][46][47] and applied to the detection of salivary cortisol, are mentioned in a recent review article concerning analysis of saliva as an ideal “health mirror” sample [48]. Since the late 2000s, several other optical cortisol immunosensors have been described in the literature.

In Table 2, the researchers present most of the articles published in the last fifteen years regarding the development of optical immunosensors for detecting cortisol in a variety of matrices, from plain buffer solutions [49][50][51] to complex biological specimens. As shown (Table 2), complex biological samples analyzed for cortisol with optical immunosensors include mainly saliva [46][47][52][53][54][55][56][57][58] as well as blood plasma/serum [59][60] and urine [46].

Table 2. Optical cortisol immunosensors.
Immunoassay Principle Signal Transduction
Principle		 Biological Sample Range/LoD Reference
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on a D-shaped, gold-coated silica optical fiber)		 Surface plasmon resonance (SPR) Buffer 0.01–100 ng/mL/
1.46 ng/mL		 [49]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab immobilized on a plastic optical fiber coated with gold–palladium allοy)		 SPR Buffer 1 pg/mL [50]
Competitive
(Competition between a fluorescently labeled BSA–cortisol conjugate and free cortisol for binding to an anti-cortisol Ab immobilized on glass substrate coated with gold)		 Metal-enhanced fluorescence (MEF) Buffer 0.02 μg/mL [51]
Noncompetitive
(Direct binding between of cortisol to an anti-cortisol Ab or aptamer, immobilized on quantum dots)		 Fluorescence quenching Saliva 1 nM (aptamer-based)
100 pM (Ab-based)		 [52]
Lateral flow–type
Competitive
(Competition between a BSA–cortisol conjugate immobilized on the strip and free cortisol for binding to a Cy3-labeled anti-cortisol Ab)		 Fluorescence
(detected with a smartphone-linked reader)		 Saliva 0.1 ng/mL [53]
Competitive
(Competition between an HRP-labeled cortisol conjugate and free cortisol for binding to an anti-cortisol Ab indirectly immobilized on PDMS microfluidic channel)		 Colorimetry Saliva 0.01–20 ng/mL/
18 pg/mL		 [54]
Lateral flow–type
Competitive
(Competition between an HRP-labeled cortisol conjugate and free cortisol for binding to an anti-cortisol Ab immobilized on the strip)		 Chemiluminescence
(detected through a smartphone camera)		 Saliva 0.3–60 ng/mL/
0.3 ng/mL		 [55]
Lateral flow–type
Competitive
(Based on europium fluorescent particle conjugates)		 Fluorescence
(Detected with a cassette reader transferring results through a Bluetooth device, manufactured by Oasis Diagnostics)		 Saliva 0.91 ng/mL [56]
Competitive
(Competition between a cortisol analogue, hydrocortisone 3-(O-carboxymethyl)oxime, covalently immobilized on gold surface and free cortisol for binding to an anti-cortisol Ab)		 SPR Saliva 10 ppt–100 ppb/
38 ppt		 [57]
Competitive
(Competition between a BSA–cortisol conjugate immobilized on a disposable disk chip and free cortisol for binding to an ALP-labeled anti-cortisol Ab)		 Chemiluminescence Saliva 0.4–11.3 ng/mL [58]
Competitive
(Competition between an in-house prepared cortisol conjugate immobilized on a gold sensor surface and free cortisol for binding to the anti-cortisol Ab; a secondary Ab was used for signal increase)		 SPR Saliva 91–934 pg/mL/
49 pg/mL		 [47]
Noncompetitive
(Direct binding of cortisol to an anti-cortisol Ab covalently immobilized on the polycarboxylate hydrogel–coated sensing surface)		 SPR Saliva, urine 3 μg/L [46]
Competitive
(Competition between a BSA–cortisol conjugate immobilized on the SPR-sensor surface and free cortisol for binding to a monoclonal anti-cortisol Ab)		 SPR Saliva, buffer 1.0 ng/mL [45]
Competitive
(Competition between cortisol analogues, i.e., suitably prepared cortisol–ssDNA conjugates, and free cortisol for binding to a biotinylated anti-cortisol Ab immobilized on streptavidin-coated particles)		 Particle mobility (detected through dark field microscopy) Blood plasma (filtered or microdialysis-sampled) High nM–low μM [59]
Competitive
(Competition between a BSA–cortisol conjugate immobilized on paper and free cortisol for binding to gold nanoparticles loaded with the anti-cortisol Ab)		 Color Blood serum 21.5 μg/dL [60]

3. Conclusions – Future Perspectives 

Cortisol homeostasis is essential for human health, while abnormal cortisol levels have been correlated to and may serve as a valuable biomarker for several disease-states. Thus, it is important to monitor cortisol concentrations in various biological samples by means of proper analytical methods. Cortisol immunoassays are currently considered the analytical method of choice for determining cortisol in biological specimens, such as blood serum/plasma, urine, saliva, or, more recently, hair. Transformation of the conventional immunoassays to technologically advanced antibody-based assays, which can easily be accomplished in a short time by non-skilled persons and are capable of being “integrated” into portable devices for point-of-care measurements, has led to the development of several cortisol immunosensors during the last three decades. Cortisol immunosensors can be divided according to the signal transduction principle they rely upon. Most of cortisol immunosensors are electrochemical and rely on signal measurement through cyclic voltammetry, impedance spectrometry, and amperometry. On the other hand, several optical immunosensors, including flow lateral-type strip sensors, have been developed, especially during the last decade; besides the usually measured optical signals, e.g., SPR signals, some of the most recently reported cortisol immunosensors [59] rely on the measurement of other parameters, e.g., on particle mobility monitoring with the aid of a microscope [61].

Some immunosensors could simultaneously detect cortisol along another biomarker, e.g., insulin [32], lactate [24] or IL-6 [43]; this “multi-analyte” approach, although technologically difficult to achieve and therefore rarely reported, is highly desirable from a clinical point of view. Thus, a dual electrochemical immunosensor proposed for the simultaneous detection of cortisol and insulin at the point-of-care [32] may eventually offer improved management of diabetes.

A great number of cortisol immunosensors have been applied to the analysis of saliva samples and less to urine or blood plasma/serum, while too little information concerning immunosensors for hair cortisol is currently available, at least to the knowledge. This tendency might be attributed, at least partly, to special requirements for the collection and/or treatment of the relevant samples: e.g., the requirement of 24 h-urine collection renders urine samples weak candidates for real-time detection of cortisol through a point-of-care immunosensor device [7]. Other factors supporting this trend may include matrix complexity, need for careful pH adjustment before sample analysis, etc. On the other hand, a special group of electrochemical immunosensors (e.g., miniaturized, and flexible/wearable sensors that are based on new materials, such as two-dimensional nanosheets of MoS2 [42]) have allowed real time and even continuous monitoring of cortisol in sweat. As reported, free (protein-unbound) cortisol seems to be present in sweat glands, through a mechanism resembling transportation of free cortisol by the bloodstream to the salivary glands. From sweat glands, cortisol is thought to reach sweat by passive transportation through the cell lipid-bilayer membrane [62]. Sweat cortisol concentrations have been reported to range from 8 to 142 ng/mL [3][6], the highest levels being found in the morning and correlating with salivary levels [62]. So far, sweat cortisol has not been detected with conventional methods -at least, not routinely, possibly due to difficulties in collecting and properly storing the corresponding samples for subsequent laboratory analysis.

At present, routine analysis of biological samples for cortisol monitoring is only performed in lab-settings [63]. Further research efforts are needed before cortisol immunosensors have become fully commercialized and available to clinical and self-monitoring applications. A first challenge of such efforts would be to perform large validation studies, in order to ensure that the analytical characteristics of the immunosensors developed are of high quality. Although there is always space for improvement, sensitivity/LOD is usually not a problem, while specificity and/or simplicity of production and cost-related issues associated with the anti-cortisol antibodies, which are inherent in all immunochemical analytical techniques, might be addressed by antibodies’ replacement with aptamers [52][64] or molecularly imprinted polymers (MIPs) [65]. However, special attention should be paid on the validation of repeatability/reproducibility [66]as well as operational stability, especially when complex biological samples, such as blood plasma/serum are to be analyzed (which may, e.g., affect integrity and deteriorate functioning of electrodes in electrochemical immunosensors); conditions of reusability as well as storage stability/durability/life span are also issues to be studied. Wearable immunosensors for detection of cortisol mainly in sweat samples seem to provide exciting prospects for further progress in the field, but particular aspects have to be addressed in the years to come [67]. These aspects include accurate sample collection, potential toxicity and biocompatibility of sensor materials, and appropriate power supply of the flexible electronics these sensors require, while data processing and communication constitute a separate research field, which may be further elaborated and improved. Moreover, thorough knowledge of the biological and chemical characteristics of the samples to be analyzed along with a deep insight in cortisol physiology and partitioning/kinetics/dynamics of the hormone in different compartments / fluids of the organism in normal and disease states would nicely supplement research efforts in the field (Figure 1) and relevant studies may be parallel performed. To achieve this, close collaboration among clinicians, physicists, chemists, bio scientists and engineers is a prerequisite.

Figure 1. Cortisol has been detected in various biological fluids and cortisol levels may serve as a valuable biomarker (e.g., of stress). Cortisol determination has been achieved mainly with analytical methods based on specific cortisol-binders, and especially anti-cortisol antibodies. Cortisol immunosensors based on different signal transduction principles are expected to be eventually commercialized and serve as an easy-to-handle, reliable tool for the point-of-care clinical analysis of cortisol.

This entry is adapted from the peer-reviewed paper 10.3390/bios13020285

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