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The electrochemical detection of bioterrorism agents: a review of the detection, diagnostics, and implementation of sensors in biosafety programs for Class A bioweapons


During the past year, disease has shown us the iron grip it can hold over a population of people. Health systems can be overwhelmed, economies can be brought into recession, and many people can be harmed or killed. When weaponized, diseases can be manipulated to create a detriment to health while becoming an economic burden on any society. It is consequently prudent that easy detection of bioweapons is available to governments for protecting their people. Electrochemical sensing displays many distinct advantages, such as its low limit of detection, low cost to run, rapid generation of results, and in many instances portability. We therefore present a wide array of electrochemical sensing platforms currently being fabricated, a brief summary of Class A bioweapons, and the potential future of bioweapon detection and biosafety.


In the era of COVID-19, it has never been more obvious that disease holds immense power to cause fear and disruption. The intentional spread of an infectious agent is therefore of prominent concern for any nation’s security, health, and economy. In the United States of America, the cost of running biosecurity programs was 1.61 B in the 2019 fiscal year, a year in which no attacks were reported, thus indicating the importance of safety to government and security agencies1.

Bioterrorism is defined as the intentional release of biological agents to cause illness or death in people, animals, and plants2. Biowarfare has been utilized long before the known existence of microorganisms. The first recorded use of biological warfare occurred in the fourteenth century BC when the Hittites sent diseased rams to weaken their enemies before battle3. The advancement of microbiology, the dissemination of information, and the ability to select for specific biological agents marked the beginning of the modern use of biowarfare. Bioweapons were used effectively and efficiently in the colonization of the Americas and in the US civil war. Furthermore, bioweapon programs were effectively established during the Second World War. Between 1990 and 1999, the instances of bioterrorism displayed a fivefold increase when compared with the previous 10 years4. In 2001, 2 years after the aforementioned report, the word “bioterrorism” made international headlines due to anthrax attacks at US postal service locations, which resulted in five deaths (Table 1).

Table 1 Examples of the use of microorganisms in biowarfare during the past millennia5

Although attacks are infrequent, the WHO has conducted models to display the profound effect a mass-bioterrorism attack could have on a localized population. The simulation predicted that upon the dissemination of anthrax spores in a densely populated area of 1 million individuals, 95,000 deaths and an additional 30,000 hospitalizations would occur. In addition to the death and injuries that would be present, resources to cope with such an attack would be sparse, especially in rural communities6. This type of event would require mass changes to medical, societal, and residential infrastructure, thus furthering the case that detection and prevention is preferable to a postattack response.

The ability to detect the agent of infection is a key factor in the success of isolating and managing a biohazard incident7. Electrochemical sensing is an ideal platform as testing is generally rapid, easy to use, sensitive, portable, and cost-effective8. By measuring the change in current, potential, conductance, resistance, or impedance due to redox reactions occurring at the electrode or membrane surfaces, the electrochemical output can be immediately interpreted for diagnostic results9,10. All of these characteristics are important for the rapid mobilization of detection programs in response to an attack.

Although there have been many substantial reviews on the topic of bioweapons and bioweapon detection, such as the works published by Walper et al.11, Shah et al.12, and Rowland et al.13, there have been no substantial reviews on the use of electrochemical sensors. Without the presence of any review on the electrochemical detection of bioweapons, it was evident that we could fill a hole in the biosensing literature. We therefore present a review on the advances in electrochemical sensing of biothreats listed in category A by the Centers for Disease Control and Prevention (CDC). These agents are deemed to be the greatest risk for use as biological weapons due to their high rates of transmission and mortality (Table 2).

Table 2 Classification of potential bioterrorism agents (bacteria, virus, protozoan, and toxins) capable of inducing diseases in humans, according to the United States Centers for Disease Control and Prevention (CDC) Strategic Planning Group5

Results and discussion

Electrochemical detection of bioweapons


Bacillus anthracis, a rod-shaped, gram-positive, spore-producing bacterium, is the causative agent of anthrax. Through the creation of potent exotoxins, B. anthracis targets vital systems and organs such as the cardiovascular system and liver, leading to rapid host death14. If a case is suspected in the United States, the Laboratory Response Network, an organization through the CDC, will be sent samples for rigorous testing, such as bacterial culturing, its susceptibility to specific bactericidal agents, and animal pathogenicity testing, all of which may take up to 72 h to complete15. Although 95% of anthrax cases are cutaneous, the inhalation of anthrax is largely concerning as a bioterrorism agent due to the difficulty in regulating airborne particulates; furthermore, death can occur in as little as 4 days after infection without treatment16. With test times taking 3 days and with the possibility of death occurring after 4 days, it is apparent that anthrax is an ideal candidate for the development of a rapid and precise method of testing.

Detection of B. anthracis via gold nanoparticles and electrodes

The use of gold nanoparticles (AuNPs) and gold electrodes in the sensing of biological materials is not a new concept and has been shown to display many advantages when used in tandem with electrochemical sensing. Together, there are three distinct advantages. First, an electrode employing AuNPs provides a much larger surface area, resulting in high current signals. Second, the biological chain can more intimately interact with AuNPs, thus facilitating the electron transport process. Finally, the sensitivity, selectivity, and robustness can be further enhanced17.

One recently developed method of anthrax detection uses the basis of DNA hybridization to detect a global gene regulator: the atxA gene, also known as the anthrax toxin activator gene. The complementary ssDNA to this gene is attached to gold nanoparticles, deposited on (3-mercaptopropyl)trimethoxysilane (MPTS), and then subsequently bound to a glassy carbon (GC) electrode for the creation of a DNA probe18. The ssDNA probe-modified electrode is incubated with the target gene for 40 min before being placed in methylene blue for 5 min, and DNA hybridization is subsequently monitored by differential pulse voltammetry (DPV). Although not rapid, the test is significantly quicker than those currently in use and has the distinct potential to be extremely user friendly.

B. anthracis secretes two types of S-layer proteins, extractable antigen (EA1) and surface array protein (Sap). These novel biomarkers are released in growth medium during replication; no other known bacteria secrete this protein19,20. Boron nitride nanosheets (BNNSs), a structural analog of graphene, are considered a trailblazing material with many breakthroughs in the area of catalysis and biosensing21,22. The use of nanoparticles has also displayed an effectiveness in biosensing; it therefore makes sense that nanosheets and nanoparticles can be used in tandem for the creation of a novel electrochemical sensor for B. anthracis. Using α-B. anthracis Sap antibody-conjugated poly(diallyldimethylammonium chloride)-functionalized BNNSs (Au–Pd NPs@BNNSs/Ab2), 1 pg/ml Sap antigen is consistently and specifically targeted by antibodies and sensed using DPV20. On plate agar, B. anthracis can be identified within 1 h by the detection of Sap, thus providing a markedly quick way to detect B. anthracis during in-lab testing. This sensing platform is therefore highlighted as a cost-effective, sensitive, timely, and specific means to identify B. anthracis in environmental samples (Fig. 1).

Fig. 1: The creation of a nanoparticle based immunosensor for the detection of B. anthracis.
figure 1

Schematic representation of the synthesis of a Au–Pd NPs@BNNSs/Ab2 and b the proposed electrochemical immunosensor20

Another advancement used for threat detection and prevention rather than diagnosis was proposed by Mazzaracchio et al.23. Their work described the creation of a miniaturized gold screen-printed, label-free aptasensor for B. anthracis spores using functionalized simulant B. cereus spores. The aptamer was immobilized on a gold screen-printed electrode; a response was then measured by the use of a portable instrument via electrochemical impedance spectroscopy (EIS). The test had a limit of detection (LOD) of 3 × 103 CFU/ml and must incubate in the suspected sample solution for 3 h. The benefits of using aptamers rather than animal-based detection (such as antibodies) are that they are generally more stable, more cost-effective, and allow for early detection, as antibody species do not need to be developed. Although the proposed device does not provide immediate testing, the benefits of aptamer use, and the portability of the device make further exploration and development worthwhile.

In the work published by O’Sullivan et al.24, a single-pot reaction in combination with PCR amplification allowed researchers to simultaneously duplicate ferrocene-labeled dATP in the virulent DNA markers CAP and PAG. Once amplified, the product was deposited on an array of six modified circular gold electrodes and square wave voltammetry, with alternating potentials of 0–0.6 V, was applied. Limits of detection of 0.8 and 3.4 fM for CAP and PAG targets were found, respectively. The above work provides an extremely low LOD and can target multiple markers but does require amplification of the bacterial sample before detection can occur. This use of PCR restricts its use in testing; thus, this method is no more practical than the current standard in testing. However, the researchers are exploring the use of multiplex isothermal amplification and the use of a portable probe and potentiostat as a way to reduce costs and build upon the project.

Carbon-based electrodes and devices

Carbon nanostructures such as carbon nanotubes (CNTs), fullerenes, graphene nanosheets, and the additional use of carbon nanoparticles have been successfully used in a wide range of sensing platforms and continue to be used in new and novel electrochemical sensors25,26,27. Many organic sensors can be implemented on a platform for flexible and biodegradable devices and resorbable substrates. Carbon-based nanostructured materials, such as CNTs and graphene sheets, offer higher performance than other substances, such as silica, in terms of portability and sensitivity28.

Using a polypyrrole-functionalized carbon paste electrode, B. cereus spores (a simulant of B. anthracis) could be effectively imprinted and measured using cyclic voltammetry (CV)29. Through the use of a cetyl trimethylammonium bromide wash, the spores could be effectively removed from the sensor; thus, the sensor could be reused without compromising the integrity of the polymeric network, allowing for the repeated use of the sensor. Linear data collection was viable between 102 and 105 CFU/ml, showing its potential for use in real-world applications. The sensor was produced using simple polymerization techniques, further displaying a cost-effective means of production while remaining sensitive and rapid (requiring only 5 min of incubation time). Molecularly imprinted sensors are also extremely stable and can withstand environmental stressors, such as temperature, pressure, and pH changes. When stored at room temperature, they remain stable for several years postproduction. These sensors, when refined to be user friendly, should be at the front-line of monitoring B. anthracis attacks, particularly at postal service locations and other front-line agencies.

Glucose oxidase (GOx)-doped gold nanoparticles were used to create a magnetic separation-based detector for anthrax in blood using a newly modified sandwiched electroanalysis method30. Using a tyramine linker, DNA fragments could bind and oxidize the present glucose to H2O2, thus facilitating reductive gold growth into anthrax enzymes. These signals could then be captured and graphed on a semi-log scale, exhibiting a detection limit of ~0.1 fM. This testing can be used to identify anthrax in human blood samples with ultrasensitive precision, but more must be done to understand the mechanism of this process. This process should also be tested against other common proteins and DNA fragments to determine its degree of selectivity (Fig. 2).

Fig. 2: Schematic illustration of the principle and procedure for the electrocatalysis and mutation discrimination of DNA.
figure 2

a The loading of a DNA capture probe onto magnetic beads, the binding of a DNA capture or detection probe with tyramine, and the labeling of a DNA detection probe with GOx-Gold; b electrocatalysis steps, namely, DNA hybridization followed by the catalytic linking of DNA probes, gold growth, and electrochemical measurements on SPE; and c GOx-Gold catalyzed reactions for glucose oxidization and tyramine coupling30

The creation of an electrochemical immunosensor for the sensitive, specific, and easy detection of anthrax protective antigen (PA) toxin in picogram concentrations was developed by Sharma et al.31 in 2015. Bismuth/heavy metal alloys were previously used for the creation of distinct stripping peaks, a broad cathodic potential range, and high sensitivity. The group then created a bismuth/Nafion-multiwall CNT composite. This composite worked in conjunction with titanium phosphate nanoparticle–cadmium ion-mouse anti-PA antibodies for heightened signal output from square wave voltammetry. The technique displayed a linear range from 0.1 to 100 ng/ml; furthermore, it boasted a detection limit of 50 pg/ml. If refined, the above work could be applied to allow for on-site testing, although challenges exist, such as the 35-min testing time needed for a conclusive result.

In the case of an attack, the rapid identification of the bioweapon is of the utmost importance. Ziółkowski et al.32 therefore proposed and developed a cost-effective and fully portable detection test for the B. anthracis pagA gene fragment, a fragment of the anthrax toxin translocating protein. The device uses graphene oxide (GO) nanoflakes to interact with pagA fragments to reveal a fluorescent marker once bound. Using a fluorometric-paired-emitter-detector-diode, this process takes only 2 min; furthermore, this process requires only mass-produced elements such as LEDs, PCR tubes, multimeters, and 2.5 V batteries. Although the detection limit of 0.625 μM is higher than that of spectrofluorophotometers, it is still sufficiently low when compared to PCR product detection methods. Due to the efficiency, cost, and portability of this test, the device could be made standard for environmental testing, along with its use in biosafety facilities and emergency testing (Fig. 3).

Fig. 3
figure 3

FDEDD device; two green LEDs placed coaxially in a 6 cm blacklight—impermeable tube and a red LED placed perpendicular to the axis. The sample is placed in the 0.2 ml PCR tube. The upper part of the PCR tube excellently suits the LED dimension, thereby ensuring no contact between the sample solution and LED. The internal photoelectric effect that generates diode electromotive force (EMF) is measured by a low-budget voltmeter (without any signal amplification)32

The future of detecting B. anthracis

We have found that the FDEDD device allows for the easy, timely, and portable detection of anthrax toxins, thereby promoting its use in security facilities. It is furthermore cost-effective and uses only commercially available materials. The development of other electrochemical fluorescent detection methods can continue to push the movement of such devices into the biosafety sector. The use of GOx-doped gold nanoparticles shows promise in allowing for point-of-care detection in human blood sera, an extremely important advancement for hospitals and individual diagnosis.


Today, botulinum neurotoxin, the product of Clostridium botulinum and the causative agent of botulism, is commonly used in cosmetic enhancement and medicine33. However, its destructive potency and heightened potential as a weapon still looms large. Although there have been no successful attempts to intentionally spread botulinum neurotoxin, it is still sanctioned as a Class A biothreat due to its potency and ease of procurement. With an estimated LD50 in humans of 1 ng/kg, botulinum neurotoxin is one of the most lethal substances known34.

The first case of research surrounding the use of botulinum neurotoxin occurred within Unit 731 of the Japanese biological warfare research unit during the Second World War35. Shortly thereafter, the USA was able to mass produce the toxin for use as a biological weapon. Since then, there have been three attempts to weaponize botulinum toxins by the Japanese cult Aum Shinrikyō36. In the early 1990s, the cult unsuccessfully disseminated large volumes of liquid botulinum toxin from trucks fitted with crude spray devices, deploying these in the vicinity of two U.S. Naval bases, the Narita airport, the Imperial Palace, and the headquarters of a rival religious group37. Fortunately, all these attacks failed; however, they illustrate how easily the toxin can be obtained and disseminated, hence the need for rapid and sensitive testing.

Currently, the standard for detecting the toxin is a mouse bioassay38. These assays involve the intraperitoneal injection of mice with a sample of the suspected toxin and subsequently observing each mouse for symptoms of the disease, such as a wasp-like waist and paralysis, over a 4-day period39. As one can imagine, this inelegant way of testing is both time consuming, uses live animal models, and would be inefficient in the case of a biological attack. We therefore outline some new adaptations and technologies that significantly reduce the time of testing from days to hours.

Identification of Botulinum neurotoxin via synaptosomal-associated protein, 25 kDa (SNAP-25) cleavage

Botulinum neurotoxins are zinc-dependent endopeptidases known to selectively cleave the soluble N-ethylmaleimide sensitive attachment protein receptor (SNARE) group of proteins40. In experiments conducted by Halliwell et al.38, two electrochemical methods were used: electrochemical impedance and a specialized combination of spectroscopy and CV. A gold electrode was then coated with a monolayer of the SNARE protein SNAP-25. This protein was cleaved by interacting with botulinum neurotoxins, and the resulting change in electrochemical properties was monitored using CV and EIS. The impedance biosensor was found to outperform the mouse bioassay in sensitivity, producing a response down to 25 pg/ml toxin and with a run time of <1 h. It is important to note that the samples must undergo processing before the test to filter out contaminating proteases; therefore, this method is not currently viable for point-of-care detection and would find much of its application in a security setting where detection is the primary concern. It should also be noted that pharmaceutical samples were the only tested group, so future tests should be performed on complex matrices, such as human serum.

Stemming off of the same group of researchers, Savage et al.41 took the detection of botulinum toxin a step further by the development of a SNAP-25 and vesicle-associated membrane protein (VAMP) sensor for the detection of botulinum neurotoxin serotypes A through E. Gold electrodes were used and SNAP-25/VAMP monolayers were yet again produced on the electrode surface before EIS was used to detect changes in the proteins. This time, concentrations in the fM range could be consistently detected. These samples were only laboratory species and were not conducted in complex matrices, nor were the samples separated from complex matrices. It would be recommended that the use of such matrices be tested in future studies.

The use of SNAP-25 was again used by Chan et al.42 this time using a GO/gold electrode. SNAP-25 was grafted to the working electrode and detection was conducted via DPV. This sensor was demonstrated to have a linear working range from 1 pg/ml to 1 ng/ml and an LOD of 8.6 pg/ml. Perhaps the more interesting part of the experiment was the feasibility of detection in complex matrices, such as skim milk, thus potentially allowing for detection in liquids and foods (Fig. 4).

Fig. 4
figure 4

Schematic illustration showing the detection mechanism of rGO-based biosensors42

Botulinum neurotoxin detection via electrochemical immunosensing

The creation of an electrochemical immunosensor by Narayanan et al.43 involved the use of graphene nanosheet-aryldiazonium salt-modified glassy carbon electrodes (GCEs) as a sensing platform and the subsequent signal amplification using enzyme-induced silver nanoparticles (AgNPs) deposited on top of gold nanoparticles (AuNPs). The developed electrochemical immunosensor could detect botulinum toxin type E in a linear range from 10 pg/ml to 10 ng/ml with a minimum detection limit of 5.0 pg/ml and a total analysis time of 65 min. Although immunoassays are a less than ideal way of identifying toxins due to the cost of obtaining antibodies and their more complex user interfaces, the presented sensitivity is 5 pg/ml, which is the lowest to date for type E botulinum toxin. This sensor provides a method to detect botulinum toxin type E for prevention and security settings and could further provide useful information due to its low LOD (Fig. 5).

Fig. 5: The efficiency of botulinum toxin detection using GNS/Ph–PhNH2/GCE detection.
figure 5

a Linear sweep stripping voltammetric peak currents against varying concentrations of BoNT/E in buffer solution; b concentration versus stripping current profile of GNS/Ph-PhNH2/GCE against botulinum toxins; c LSV responses on GNS/Ph–PhNH2/GCE against botulinum toxins E, A, B, F, and with no antigen from high to low, respectively43

Botulinum toxin type A antibodies were immobilized on a GC electrode modified with Au nanoparticles/graphene-chitosan (AuNPs-Gr-Cs) for signal amplification purposes. Through the use of EIS, impedance was calculated, and changes were observed due to the resistance created at the redox probe. The impedimetric immunosensor developed by Afkhami et al.44 displayed a detection limit of 0.11 pg/ml and was furthermore able to detect toxins in human serum and milk, thus providing successful testing in complex matrices. Unfortunately, the electrodes could only be used over a 4-day period, as the signal rapidly decreased in efficiency after four consecutive days of use. If the lifetime of this electrode can be increased, it will be a welcome addition to the sensors used for botulinum toxin detection.

Proposed advancements for the detection of botulinum neurotoxin

Due to the integral involvement of SNARE proteins, it is unsurprising that SNAP-25 seems to be a promising protein to target for the detection of botulinum toxins. There is, however, a distinct lack of valuable testing using the SNARE proteins synaptobrevin-2 and syntaxin-1A. If we can implement all three proteins on an electrode, the impedimetric sensor should boast high levels of specificity and a low LOD, showing promise for use in environmental samples. The use of gold nanoparticles/graphene-chitosan also shows high potential for use in testing with complex matrices. Notably, creating covalent bonds between the electrode and detection molecules, such as using reactive carbon paper as the electrode, can increase the electrode life by significant proportions.


Smallpox is caused by the major and minor Variola viruses and was the biological weapon of choice used by European colonists, the British during the American revolution, and the American confederates during the American revolution5. In Europe, during the eighteenth century, smallpox regularly killed between 200,000–600,000 people every year and reported fatality rates were between 20–40%45. As a bioweapon, the smallpox-causing Variola was used to target Indigenous Americans, causing a more than 50% decline in Indigenous American populations46. In more recent memory, as recent as the 1980s, the Soviet Union was able to mass produce liquid-form smallpox biological weapons47. Surprisingly, right around this time, smallpox vaccinations were terminated in most countries48. In fact, if used on contemporary populations, it was determined by Gani et al.49 that between three and five individuals of the present population would be infected by each active case post infection. With a history deep rooted in bioweaponry and a complete recession in vaccinations, smallpox remains one of the most feared and effective potential bioweapon agents in the modern age.

Work conducted in 2005 by Komarova et al.50 used ultrathin DNA-doped polypyrrole films with oligonucleotides to achieve an LOD of 1.6 fmol per 0.1 ml, which is the lowest of any published research. Their work used chronoamperometry to achieve a one-step, reagent-free detection method that yielded results in seconds while being reusable and highly stable for storage. The use of an ultrathin film could be adapted to create a sensor that could be placed discreetly in areas where potential for biothreats is high, such as in ventilation systems. This work has not been built upon since (Fig. 6).

Fig. 6: The proposed horseradish peroxidase-labeled probe and minicell for the detection of variola virus.
figure 6

a The electrochemical minicell and processes used for the preparation of DNA-doped conductive films (internal volume of 100μl, bottom opening of 3mm i.d.) and for target DNA chronoamperometric detection50; b direct detection of DNA hybridization and c, the indirect detection of DNA hybridization

Research by Donaldson et al.51 explored the possibility of detection from throat-swabbed samples. Potential benefits of their work show that the virus could be detected in the oropharyngeal or respiratory mucosa before the infectious stage or the onset of illness, resulting in better prognosis and containment. Due to the low LOD of the polypyrrole probes proposed by Komarova et al.50, an adaptation for its use on throat swabs would streamline detection in cases of bioterrorism for individual cases.


The most storied pandemic known to Europe is the plague, killing an estimated 30–50% of the European population52 and 33% of the estimated global population53. Yersinia pestis, the causative agent of plague, is widely considered one of the most likely pathogens to be used as a bioweapon54. In humans, the plague is a severe clinical infection that can progress rapidly despite antibiotic therapy and is associated with a high-mortality rate55. In fact, in its septicemic and pneumonic presentations, untreated cases are almost unanimously fatal56. Less severe but still presenting a significant mortality rate, untreated bubonic plague has a case fatality of 50–80%52. However, recovery rates are high if detected and treated within 24 h of symptom onset. We will therefore explore new simple techniques for the identification of Yersinia pestis through an electrochemical sensing platform.

By harnessing the power of electrokinetic forces via the addition of electroosmotic flow, Zhao et al.57 were able to combine capillary-based immunochromatography assays with upconversion nanoparticles to increase the signal detection of Y. pestis by 64%. Although this work was not fully automated and required a scientific background to perform, it showed great future potential with a rapid assay time of 5 min and a detection limit of 1.2 × 104 CFU/ml in soil samples. Thus, they demonstrated the potential for electrochemical techniques to enhance previously developed sensors (Fig. 7).

Fig. 7
figure 7

Schematic of the biosensor for the detection of plague. The electric field along the direction of fluid travel was defined as positive, as indicated by the arrow57

The use of EIS and label-free genosensing for detecting was performed by Komarova et al.58. The group created an assay using eight gold electrodes, some conjugated with specific binding sites for Y. pestis DNA detection, while others acted as nonspecific sites to act as a negative control. The assay could perform eight EIS measurements simultaneously in 15 min. The use of multiple electrodes was beneficial in confirming the reliability of detection. However, this study was not comprehensive and only illustrated the potential of the sensor. Thus, the LOD and specificity of Y. pestis should be further investigated.

Proposed advancements for the detection of Yersinia pestis

We feel that the work of Zhao et al. has the potential to be translated into diagnostic and point-of-care applications. Experimentation using similar methods in blood serum would be beneficial to this effect.

Viral hemorrhagic fevers

Viral hemorrhagic fevers (VHFs) are a group of illnesses caused by four different families of viruses: arenaviruses, filoviruses, bunyaviruses, and flaviviruses59. Due to the epidemic causing the potential of VHFs, there has been an increased interest in VHF pathogens60. As global temperatures continue to increase, the potential for VHFs to thrive on a global scale also increases61. The heightened capability for human-to-human transmission and high levels of mortality call for quick, fast, and reliable identification. We will therefore explore the means of the simple electrochemical identification of these easily transmittable and high-mortality diseases (Table 3).

Table 3 Types of VHF, modes of transmission, virulence, therapy, and mortality62


Ebolaviruses are negative strand RNA viruses that belong to the Filoviridae family. These public health pathogens are primarily transmitted by human-to-human contact with infected body fluids and corpses and cause severe and acute systemic disease with extremely high-mortality63. Ebolaviruses have substantial epidemic potential, as shown by the 2013–2016 West African outbreak64. This outbreak was unprecedented in scale, with more than 28,000 confirmed cases and 11,000 deaths65. Although there is no previous use of Ebolavirus as a biological weapon, its ease of transmission, high rate of mortality, and difficulty of containment make it a potent biological agent if weaponized. The rapid and simple electrochemical detection of Ebolavirus is therefore essential in the case of a weaponized attack.

There is a promising sensor for use in underdeveloped and rural areas that meets the criteria for affordable, sensitive, specific, user friendly, rapid and robust, equipment free, and deliverable to end users (ASSURED) testing recommended by the WHO66. This test detects the L gene sequence that is present in the five most common Ebola strains. Padlock probing is used to bind target DNA with magnetic particles that then undergo isothermal amplification and are monitored using square wave voltammetry on commercially available screen-printed electrodes. The sensor has an LOD of 33 cDNA molecules, making it extremely sensitive67. The assay takes a total time of <2.5 h, making it relatively rapid. Isothermal amplification can also be modified to occur at room temperature, making this an ideal test in areas with minimal lab access. To prepare this test for use in industry, the work should be repeated using complex human matrices rather than a cDNA mimic of the virus (Fig. 8).

Fig. 8: Schematic representation of the electrochemical genosensing of Ebolavirus cDNA by rolling circle amplification.
figure 8

A1 Coupling of the circularized biotinylated cDNA (from 200 zmol up to 20 amol) on streptavidin magnetic particles for 5 min at RT. A2 RCA on the streptavidin-MPs using φ29 DNA polymerase for 60 min at 37 °C. A3 Hybridization with readout probe 2 labeled with HRP for 15 min at 37 °C. A4 Enzymatic reaction (with H2O2 as a substrate and hydroquinone (HQ) as a mediator) and electrochemical determination on screen-printed electrodes by square wave voltammetry at a potential ranging from 0 to −0.7 V. Schematic representation of the Aquila-amplified single-molecule counting procedure. B1 RCA using φ29 DNA polymerase for 60 min at 37 °C. B2 Hybridization with readout probe 1 labeled with Cy3. B3 Counting of Cy3-labeled RCA products with an Aquila-amplified single-molecule counter (Q-linea)67

Ilkhani et al.68 again used cDNA to detect Ebolavirus. The surface of a gold screen-printed electrode was modified with complementary ssDNA. When in contact with Ebola, hybridization occurred, and the hybrid was conjugated with a streptavidin-alkaline phosphatase for use in redox processes to facilitate electrochemical measurements. The process was monitored through both EIS and DPV testing. The total detection time was optimized at 60 min. This sensor is not only more rapid than the previous sensor but also requires no amplification of DNA.

Another method of detection for the five most common species of Ebola involves using a field-effect transistor with reduced GO, as the conducting channel, and anti-Ebola probes immobilized on the surface69. This sensor detects the surface glycoprotein that is found in all five common Ebolaviruses. The results are both instantaneous, sensitive, and specific with an LOD of 1 ng/ml. The sensor was tested in a complex matrix containing PBS buffer, human serum, plasma, and Ebola glycoprotein to mimic patient samples. Thus, this sensor is a candidate for rapid and early testing; however, more work needs to be done to improve the sensor function, particularly in patient samples.

In a paper by Yuhai et al.70, a rapid and sensitive detection method for Ebolavirus is made using electroluminescent nanospheres (ENs) to provide an ~85-fold improvement in electroluminescent signaling. The group also added magnetic nanobeads (MBs) to selectively separate Ebola targets in complex media, thus providing another threefold increase in signaling. ENs were constructed by embedding CdSe/ZnS quantum dots into poly(styrene/acrylamide) copolymer nanospheres. These ENs were then attached to polyclonal antibodies and put into solution with Ebolavirus samples. CV was run from −1.65 to 0 V, and a 900 V photomultiplier tube was used for ECL recording. A LOD as low as 5.2 pg/ml Ebolavirus could be detected in 2 h.

The final sensor is the only one to have used samples from patients71. It is rapid, affordable, and specific. This method also uses an Ebola padlock probe for the L gene. cDNA derived from the clinical RNA samples was synthesized using rolling circle amplification onto magnetic beads. These cDNA samples were then labeled with GOx. The sample was then placed on a screen-printed carbon electrode with Prussian blue, followed by the addition of glucose. A chemical reaction occurred, and H2O2 was produced and subsequently reduced. The reduction was measured using chronoamperometry. Although preparation of this sensor and sample is time consuming, the analytical time is <10 min, making it a great point-of-care alternative.


Among VHFs, Ebolavirus, and Marburg virus, which are hemorrhagic fevers of the family filoviridae, are considered the most lethal; these can have a fatality rate of up to 90%72. The CDC recommends the following minimum biosafety and biocontainment requirements that should also be applicable in low-resource settings: the patient should be isolated, preferably in a single room with an adjoining toilet and separate anteroom as a changing area for hospital personnel; personnel must wear a scrub suit, gown, and apron, two pairs of gloves, a mask, headcover, eyewear, and rubber boots; all non-disposable material that has come into contact with the patient should be cleaned with soap and disinfected with bleach; waste should be disposed of in a place set aside for this purpose and burnt at least daily; laboratory workers working with patient material should wear protective clothing; and bodies of deceased patients should be sprayed with bleach, sealed in a body bag that is also sprayed with bleach and buried with the same precautions as are taken in the hospital73. Unfortunately, although Marburg viruses are highly fatal and severely contagious74, there exists a distinct lack of electrochemical detection of Marburg virus (Table 4).

Table 4 Clinical and laboratory features of Marburg hemorrhagic fever72

Yellow fever

A flavivirus transmitted by mosquitos, yellow fever (YF), is noncontagious, but has no specific treatment75 and a fatality rate ranging from 25 to 50%62; thus, its potential as a bioweapon is still high. Vaccination to the disease is only recommended when staying in areas where it is endemic76, meaning that the majority of Western society has no immunity to the disease. Almost all cases of YF in North America are imports; however, with increasing temperatures due to climate change, the habitat of the vector is increasing77. The intentional release of YF vectors could therefore make a permanent home in parts of North America and Europe and become endemic, as seen in Brazil78.

At the time of writing, no electrochemical sensors have been developed for the detection of YF, but there is potential, as work in other flaviviruses is ongoing79,80,81. Whereas current methods of detection struggle with cross-reactivity in confirmative diagnosis75, an electrochemical sensor would be of great benefit.

Other VHFs

The electrochemical sensing of other VHFs is critically under-researched despite the increasing threat of disease vectors becoming permanent fixtures in a warming climate. If weaponized, the distinct lack of sensing poses increased challenges in the rapid mobilization of large-scale testing.

A call for research focus in the detection of VHFs

Due to the ever-increasing global temperatures and following the increased potential for VHF transmission, it is prudent that ready detection and diagnosis of these deadly viruses become standard. Viruses have already shown potential for mass destruction and death. We therefore call for an increase in VHF detection platforms for quick, selective, and effective identification.


Discovered in 1911 by George McCoy while investigating a supposed bubonic plague in squirrels, Francisella tularensis and the disease tularemia was shown to be a highly contagious and infectious illness82. The disease also displays various mechanisms and targets multiple tissues. The most likely to be weaponized is oropharyngeal and gastrointestinal tularemia, which can develop after oral exposure and displays a fatality rate of up to 60%83. These characteristics led to studies of its potential as a biological weapon, including involuntary human experimentation by Japan among civilian, political, and military prisoners. The end goal was for use in warfare during the Second World War84. Later, in the United States, voluntary human experimentation occurred in the 1950s–1960s with penitentiary inmates and noncombatant soldiers82. Soviet Union scientists allegedly developed a vaccine-resistant strain, which they tested as a biological weapon in 1982–198385. Because it has a high aerosol-related infection rate, low infectious dose, and the ability to induce fatal disease, F. tularensis is considered a potential agent of biological warfare.

The most recent electrochemical advancement in detecting F. tularensis was the fabrication of an electrochemiluminescence (ECL) immunosensor by grafting monoclonal antibodies onto screen-printed gold electrodes with automated monitoring86. The sensor used the active luminophore Ru(bpy)3 2+ to detect fragments of the envelope at an LOD of 0.4 ng/ml, while an LOD of 70 bacteria/ml was observed when using whole antibody capture, and 45 bacteria/ml when the whole bacterial cell was targeted. The group also tested for specificity against Yersinia enterocolitica, although it would be further advised to test against other common bacteria.

Del Río et al.87 also featured gold electrodes in their work on the detection of F. tularensis. By using the forward primer Ft FwP for F. tularensis, the primer was immobilized on a gold sensor via the use of a thiol or amino moiety, elongated using recombinase polymerase amplification and then bound with a horseradish peroxidase label. Chronoamperometry was used to detect oxidized tetramethylbenzidine, an indication that the horseradish peroxidase label had bound to the target molecule. The assay could be performed in approximately an hour and had an LOD of 104 DNA copies/µl. However, the overnight incubation period, lack of mobility, and mandatory use of laboratory space currently hinder this work for quick and easy testing (Fig. 9).

Fig. 9: Design of the sensing platfom for the detection of tularemia.
figure 9

a The electrode with its respective counter and reference electrodes and b ensemble with its electrodes, PMMA block, aluminum block, and temperature controller87

Automated sensing is optimal for use in a biothreat situation, as its simplicity results in ease of training in regard to large-scale testing. Work done by Dulay et al.88 resulted in the creation of a fully automated sensing platform using gold electrodes and microfluidics to assist in automation. The only hands-on time is the addition of sample, with a complete run time of <20 min. The sensor detects the lipopolysaccharide found on the bacterial membrane of F. tularensis. This was first done by grafting anti-Francisella antibody FB11 fragments onto the gold-plated electrode and subsequently measuring loose lipopolysaccharide and whole cell F. tularensis using amperometric techniques. Whole antibodies were then grafted onto the electrodes and tested using the same methods. The antibody fragments retained 85% antigen recognition under proper storage over 45 days. A LOD of 38 bacteria/ml was found. The writers report no cross-reactivity and hope to further this platform to perform multiplex detection in real-world applications, such as its implementation in ventilation systems (Fig. 10).

Fig. 10: Amperometric immunosensor detection setup.
figure 10

The setup contains a peristaltic pump positioned behind the reservoirs to provide solution flow into the electrode array mounted within the microfluidics. a Electrode array with microfluidics placed in the platform and connected to the potentiostat for amperometric measurement; b a sample script-based assay program; c electrode array integrated with microfluidics; d a full front view of the prepared testing device; and e lithographically produced gold electrode array with internal reference electrodes and counter electrodes88

Proposed advancements for the detection of Tularemia

The use of automated sensing platforms is a welcome addition to any facility where testing is required. Not only does automation free the hands of researchers, but a testing time of ~15 min is very convenient. We encourage researchers to miniaturize the testing apparatus and use anti-Francisella antibodies and antibody fragments on a chip-like electrochemical sensor. These electrochemical sensors will allow for more affordable and accessible testing platforms.

Combined sensing

The optimal form of sensing for the detection of biothreat agents is a combined sensing platform for the environmental testing of multiple biological weapons at once. These combined platforms would allow for the specific identification and differentiation of a bioweapon via the use of a single test in a timely manner. Thus, these combined platforms would allow for a quick and safe response for security, community, and government locations, along with healthcare systems. Combined systems would also further reduce the cost of buying multiple sensing platforms, reduce the requirement for multiple heavy, unportable machinery, and allow for simplified training.

Most recently, portable BioDetector integrated (pBDi), a portable biothreat detection unit approximately the size of a small suitcase, has been developed to detect four Class A biothreats: Y. pestis, B. anthracis, F. tularensis, and orthopox viruses (making it one of the few electrochemical sensors for smallpox)89. Using gold electrodes conjugated with targeted antibodies, the system enables the specific binding of an antibody to its subsequent antigen. These agents are then quantified by measuring the electrical current of the respective enzymatic redox reactions on the electrode surfaces. The reaction is further amplified via redox cycling, thus increasing the sensitivity of the electrodes. The detection platform is compact and has been developed for ease of use with nonscientific personnel and minimal sample preparation. In addition to a processing time of ~20 min and an LOD of 104 plaque forming units per milliliter, this method shows potential for point-of-care and environmental detection; however, further testing should be performed on complex matrices containing human serum so that point-of-care testing can take place (Fig. 11).

Fig. 11: The pBDi system.
figure 11

a pBDi system including reagents and sample holder with ruggedized tablet PC. b Principle of biothreat agent detection using electrochemical ELISA technology89

Another combined electrochemical sensor detects B. anthracis, F. tularensis, and smallpox based on PCR and amperometric detection90. With an assay time of 8 min, this work shows considerable promise; however, in its current state without full automation and a narrower group of detectable diseases, we believe it to be inferior to the previously mentioned pBDi system.

Another combined sensor using ECL and DNA sensing has been developed but is limited to only B. anthracis and F. tularensis91. In addition, the system is not automated, making it difficult for use in large-scale testing.

Future of the electrochemical sensing of bioweapons

We propose that the ideal platform should be relatively inexpensive, portable, selective to many bioterrorism agents without the creation of false positives or negatives and should boast a low LOD for each bioagent. The WHO’s recommendation for ASSURED testing is critical to the efficient advancement of bioweapon detection. With these changes, we hope that there will be further improvement in the detection, ease of use, reusability, and portability of electrochemical sensors.

The sensitivity and LOD of the most promising electrochemical detection methods targeting bioweapons are listed in Table 5. In summary, the best performing electrochemical sensor targeting Bacillus anthracis has been developed using a GOx-modified gold nanoparticle electrode30 that demonstrates an LOD comparable to or even lower than that of the conventional HCR technique and fluorescence spectroscopy, respectively. The proposed sensing platform has distinctive advantages over other electrochemical sensor prototypes in terms of its amplification of electrical signals and selectivity. The proposed sandwich detection approach enables the ultrasensitive electroanalysis of anthrax DNA present in blood as well as discrimination against targeted DNA with a single-base mutation. The recommended approach for electrochemical detection of Botulinum neurotoxins would be the development of an impedimetric sensor opposed to voltammetry or amperometry signaling. Not only is impedance more sensitive, but it allows for the identification and separation of Faradaic and non-Faradaic processes occurring at the electrode. The proposed bioelectrode41 can detect active toxins at concentrations as low as 25 fg/ml, which is lower than the standard mouse bioassay. However, this biosensor was only tested in buffer solution; therefore, more work is needed to further verify its selectivity in real-world samples, such as within bodily samples or food. The electrochemical detection of viral smallpox DNA showed very good sensitivity at the level of 1.6 fmol/0.1 ml. What should be highlighted as a benefit of this electrochemical sensor is its short analysis time, as it demonstrates a direct response to target DNA. Compared to indirect assays that necessitate electrochemical labels and reagent-intensive amplification, the proposed electrochemical method is reagent-free and detects DNA in one-step. The response time of this bioelectrode is counted in seconds, which is much faster than the conventional method of detection of the same target DNA with similar sensitivity. The electrochemical sensing of Yersinia pestis—the causative agent of plague—has a significant advantage over conventional ELISA, as it is much faster and displays comparable or even better sensitivity. The proposed electrochemical platform57 uses an electroosmotic flow in conjunction with an immunochromatographic assay, resulting in a rapid response. The recent development of an electrochemical detector of Ebolavirus is of great importance because it demonstrates good sensitivity and a short response time without time-consuming sample pretreatment or use of sophisticated instrumentation70. The proposed sensing platform is unique and combines CdSe/ZnS quantum dots acting as an electroluminescent signal amplifier with MBs that selectively separate targets from complex samples. This method simplifies the operation process and saves time. The proposed electroluminescent platform showed good reproducibility and specificity and is highly promising for further development toward clinical diagnostics.

Table 5 Selected sensor parameters for electrochemical detection methods (sensitivity, limit of detection) of bioterrorism agents categorized as class A according to the CDC

The works by Pöhlmann et al.89 established a great foundation for the future of biosensing platforms. These platforms are extremely portable and detect four different Class A bioweapons. If researchers are further able to miniaturize these sensing platforms, allowing them to be transported as kits, the rapid establishment of medical testing sites and medical personnel will be increasingly feasible. It would be of great benefit to tailor these sensing kits for the ability to test complex matrices, such as blood, saliva, and mucous, and environmental samples, such as soil and water.

We further stress that the development of simple electrochemical VHF sensors is paramount to a safe and prepared tomorrow. Especially as global temperatures increase, the ability of VHF vectors, such as ticks, mosquitoes, and others to deliver disease only increases61,99,100. If not used for detecting bioweapon agents, these sensors could be used in the detection of disease. Screen-printed and paper electrodes also display distinct advantages in terms of portability, cost, and ease of use when conducting electrochemical sensing. If possible, these screen-printed or paper electrodes could be beneficial for use in underfunded communities with limited resources.

As time progresses and as history indicates, it becomes increasingly likely that bioweapons will be used not only again but also to a larger degree of success than before. It is apparent that the use of bioweapons in war or in bioterrorism could cause much stress to an established community. We were able to discuss some of the most prolific Class A bioweapon agents and their detection in the environment and clinical studies. If the environment is tested after an attack, the treatment for patients can be accelerated, and proper infrastructure can be erected. For more isolated incidents, such as the mailing of bioweapons, testing units should be available and utilized in biosafety and shipping facilities worldwide. In either case, a rapid and standardized testing regimen for bioterror agents could save not only individuals but also entire cities.


  1. Watson, C., Watson, M., Gastfriend, D. & Sell, T. K. Federal funding for health security in FY2019. Heal. Secur. (2018).

  2. Jansen, H. J., Breeveld, F. J., Stijnis, C. & Grobusch, M. P. Biological warfare, bioterrorism, and biocrime. Clin. Microbiol. Infect. (2014).

  3. Barras, V. & Greub, G. History of biological warfare and bioterrorism. Clin. Microbiol. Infect. (2014).

  4. Grundmann, O. The current state of bioterrorist attack surveillance and preparedness in the US. Risk Manag. Healthc. Policy (2014).

  5. Oliveira, M., Mason-Buck, G., Ballard, D., Branicki, W. & Amorim, A. Biowarfare, bioterrorism and biocrime: a historical overview on microbial harmful applications. Forensic Sci. Int. 314, 110366 (2020).

    Article  Google Scholar 

  6. Holmberg, B. Biological aspects of chemical and biological weapons. Ambio 4, 211–215 (1975).

    Google Scholar 

  7. Sharififar, S., Jahangiri, K., Zareiyan, A. & Khoshvaghti, A. Factors affecting hospital response in biological disasters: a qualitative study. Med. J. Islam Repub. Iran 34, 1–12 (2020).

    Google Scholar 

  8. Zhu, C., Yang, G., Li, H., Du, D. & Lin, Y. Electrochemical sensors and biosensors based on nanomaterials and nanostructures. Anal. Chem. (2015).

  9. Sharma, R. & Raghavarao, K. S. M. S. Nanoparticle-based aptasensors for food contaminant detection. In Nanomaterials for Food Applications (eds Amparo, L. R., Maria, J. F. R., Marta, M. S. & Laura, G. G.-M.) (Elsevier, 2018).

  10. Stradiotto, N. R., Yamanaka, H. & Zanoni, M. V. B. Electrochemical sensors: a powerful tool in analytical chemistry. J. Brazi. Chem. Soc. (2003).

  11. Walper, S. A. et al. Detecting biothreat agents: from current diagnostics to developing sensor technologies. ACS Sens. 3, 1894–2024 (2018).

    Article  Google Scholar 

  12. Shah, J. & Wilkins, E. Electrochemical biosensors for detection of biological warfare agents. Electroanalysis 15, 157–167 (2003).

    Article  Google Scholar 

  13. Rowland, C. E., Brown, C. W., Delehanty, J. B. & Medintz, I. L. Nanomaterial-based sensors for the detection of biological threat agents. Mater. Today 19, 464–477 (2016).

    Article  Google Scholar 

  14. Liu, S., Moayeri, M. & Leppla, S. H. Anthrax lethal and edema toxins in anthrax pathogenesis. Trends Microbiol. 22, 317–325 (2014).

    Article  Google Scholar 

  15. Ravenel, M. P. Anthrax in Humans and Animals 4th edn, 299–300 (World Health Organization, 2008).

  16. Jamie, W. E. Anthrax: diagnosis, treatment, prevention. Prim. Care Update Ob. Gyns. 9, 117–121 (2002).

    Article  Google Scholar 

  17. Qin, L. et al. “Gold rush” in modern science: fabrication strategies and typical advanced applications of gold nanoparticles in sensing. Coord. Chem. Rev. 359, 1–31 (2018).

    Article  Google Scholar 

  18. Das, R., Goel, A. K., Sharma, M. K. & Upadhyay, S. Electrochemical DNA sensor for anthrax toxin activator gene atxA-detection of PCR amplicons. Biosens. Bioelectron. (2015).

  19. Puranik, N., Tripathi, N. K., Pal, V. & Goel, A. K. Enhanced production and purification of recombinant surface array protein (Sap) for use in detection of Bacillus anthracis. 3 Biotech 8, 1–5 (2018).

    Article  Google Scholar 

  20. Sharma, M. K. et al. Ultrasensitive electrochemical immunoassay for surface array protein, a Bacillus anthracis biomarker using Au-Pd nanocrystals loaded on boron-nitride nanosheets as catalytic labels. Biosens. Bioelectron. (2016).

  21. Li, R. et al. Non-covalent surface modification of boron nitride nanotubes for enhanced catalysis. Chem. Commun. 50, 225–227 (2014).

    Article  Google Scholar 

  22. Lin, Y. & Connell, J. W. Advances in 2D boron nitride nanostructures: Nanosheets, nanoribbons, nanomeshes, and hybrids with graphene. Nanoscale 4, 6908–6939 (2012).

    Article  Google Scholar 

  23. Mazzaracchio, V. et al. A label-free impedimetric aptasensor for the detection of Bacillus anthracis spore simulant. Biosens. Bioelectron. (2019).

  24. Magriñá, I. et al. Duplex electrochemical DNA sensor to detect bacillus anthracis CAP and PAG DNA targets based on the incorporation of tailed primers and ferrocene-labeled dATP. ACS Omega 4, 21900–21908 (2019).

    Article  Google Scholar 

  25. Asadian, E., Ghalkhani, M. & Shahrokhian, S. Electrochemical sensing based on carbon nanoparticles: a review. Sens. Actuators B Chem. 293, 183–209 (2019).

    Article  Google Scholar 

  26. Yáñez-Sedeño, P., Pingarrón, J. M., Riu, J. & Rius, F. X. Electrochemical sensing based on carbon nanotubes. Trends Anal. Chem. 29, 939–953 (2010).

    Article  Google Scholar 

  27. Bhat, V. S., S., S. & Hegde, G. Review—biomass derived carbon materials for electrochemical sensors. J. Electrochem. Soc. 167, 037526 (2020).

    Article  Google Scholar 

  28. Angione, M. D. et al. Carbon based materials for electronic bio-sensing. Mater. Today 14, 424–433 (2011).

    Article  Google Scholar 

  29. Ait Lahcen, A., Arduini, F., Lista, F. & Amine, A. Label-free electrochemical sensor based on spore-imprinted polymer for Bacillus cereus spore detection. Sens. Actuators B Chem. (2018).

  30. Wang, H. et al. A sandwiched electroanalysis method for probing Anthrax DNAs based on glucose-induced gold growth and catalytic coupling of tyramine using gold-mineralized glucose oxidase. Sens. Actuators B Chem. (2018).

  31. Sharma, M. K., Narayanan, J., Upadhyay, S. & Goel, A. K. Electrochemical immunosensor based on bismuth nanocomposite film and cadmium ions functionalized titanium phosphates for the detection of anthrax protective antigen toxin. Biosens. Bioelectron. (2015).

  32. Ziółkowski, R. et al. Toward fluorimetric-paired-emitter-detector-diode test for Bacillus anthracis DNA based on graphene oxide. Microchem. J. (2020).

  33. Ting, P. T. & Freiman, A. The story of Clostridium botulinum: from food poisoning to Botox. Clin. Med. (2004).

  34. Dhaked, R. K., Singh, M. K., Singh, P. & Gupta, P. Botulinum toxin: Bioweapon & magic drug. Indian Journal of Medical Research 132, 489–503 (2010).

    Google Scholar 

  35. Osterbauer, P. J. & Dobbs, M. R. Neurobiological weapons. In Clinical Neurotoxicology Syndromes, Substances, Environments 631–645 (Elsevier, 2009).

  36. Bleck, T. P. Botulism as a potential agent of bioterrorism. In Bioterrorism and Infectious Agents: A New Dilemma for the 21st Century (eds Fong, I. W. & Alibek, K.) (Springer Science & Business Media, 2009).

  37. Danzig, R. et al. Aum Shinrikyo: Insights Into How Terrorists Develop Biological and Chemical Weapons 1–68 (Center for a New American Security, 2011).

  38. Halliwell, J., Savage, A. C., Buckley, N. & Gwenin, C. Electrochemical impedance spectroscopy biosensor for detection of active botulinum neurotoxin. Sens. Bio-Sensing Res. (2014).

  39. Weingart, O. G. et al. The case of botulinum toxin in milk: experimental data. Appl. Environ. Microbiol. 76, 3293–3300 (2010).

    Article  Google Scholar 

  40. Chen, S. & Barbieri, J. T. Association of botulinum neurotoxin serotype a light chain with plasma membrane-bound SNAP-25. J. Biol. Chem. 286, 15067–15072 (2011).

    Article  Google Scholar 

  41. Savage, A. C., Buckley, N., Halliwell, J. & Gwenin, C. Botulinum neurotoxin serotypes detected by electrochemical impedance spectroscopy. Toxins (Basel). (2015).

  42. Chan, C. Y. et al. A reduced graphene oxide-Au based electrochemical biosensor for ultrasensitive detection of enzymatic activity of botulinum neurotoxin A. Sens. Actuators B Chem. (2015).

  43. Narayanan, J. et al. Electrochemical immunosensor for botulinum neurotoxin type-E using covalently ordered graphene nanosheets modified electrodes and gold nanoparticles-enzyme conjugate. Biosens. Bioelectron. (2015).

  44. Abbas, A. et al. Impedimetric immunosensor for the label-free and direct detection of botulinum neurotoxin serotype A using Au nanoparticles/graphene-chitosan composite. Biosens. Bioelectron. 93, 124–131 (2017).

    Article  Google Scholar 

  45. Berche, P. The threat of smallpox and bioterrorism. Trends Microbiol. 9, 15–18 (2001).

    Article  Google Scholar 

  46. Riley, J. C. Smallpox and American Indians revisited. J. Hist. Med. Allied Sci. 65, 445–477 (2010).

    Article  Google Scholar 

  47. Alibek, K. Smallpox: a disease and a weapon. Int. J. Infect. Dis. 8, 3–8 (2004).

    Article  Google Scholar 

  48. Hall, A. The global eradication of smallpox. Final report of the Global Commission for the Certification of Smallpox Eradication. Postgrad. Med. J. 58, 734–735 (1982).

    Article  Google Scholar 

  49. Gani, R. & Leach, S. Transmission potential of smallpox in contemporary populations. Nature 414, 748–751 (2001).

    Article  Google Scholar 

  50. Komarova, E., Aldissi, M. & Bogomolova, A. Direct electrochemical sensor for fast reagent-free DNA detection. Biosens. Bioelectron. (2005).

  51. Sarkar, J. K., Mitra, A. C. & Mukherjee, M. K. Duration of virus excretion in the throat of asymptomatic household contacts of smallpox patients. IndianJournal of Medical Research 62, 1800–1803 (1974).

    Google Scholar 

  52. D’Ortenzio, E. et al. Plague: bridging gaps towards better disease control. Med. Mal. Infect. 48, 307–317 (2018).

    Article  Google Scholar 

  53. Pechous, R. D., Sivaraman, V., Stasulli, N. M. & Goldman, W. E. Pneumonic plague: the darker side of yersinia pestis. Trends Microbiol. 24, 190–197 (2016).

    Article  Google Scholar 

  54. Ansari, I., Grier, G. & Byers, M. Deliberate release: plague—a review. J. Biosaf. Biosecurity 2, 10–22 (2020).

    Article  Google Scholar 

  55. Ditchburn, J.-L. & Hodgkins, R. Yersinia pestis, a problem of the past and a re-emerging threat. Biosaf. Heal. 1, 65–70 (2019).

    Article  Google Scholar 

  56. Tieh, T. H., Landaue, E., Miyaga, F., Kobayashi, G. & Okayasu, G. Primary pneumonic plague in Mukden, 1946, and report of 39 cases with 3 recoveries. J. Infect. Dis. 82, 52–58 (1948).

    Article  Google Scholar 

  57. Zhao, Y., Zhang, P., Wang, J., Zhou, L. & Yang, R. A novel electro-driven immunochromatography assay based on upconversion nanoparticles for rapid pathogen detection. Biosens. Bioelectron. (2020).

  58. Komarova, E., Reber, K., Aldissi, M. & Bogomolova, A. New multispecific array as a tool for electrochemical impedance spectroscopy-based biosensing. Biosens. Bioelectron. (2010).

  59. Perng, G. C. & Solbrig, M. V. Viral hemorrhagic fevers. In Viral Infections of the Human Nervous System. Birkhäuser Advances in Infectious Diseases (ed. Jackson, A.) (Springer, Basel, 2013).

  60. Drosten, C., Kümmerer, B. M., Schmitz, H. & Günther, S. Molecular diagnostics of viral hemorrhagic fevers. Antivir. Res. 57, 61–87 (2003).

    Article  Google Scholar 

  61. Gonzalez, J.-P., Souris, M. & Valdivia-Granda, W. Global spread of hemorrhagic fever viruses: predicting pandemics. 3–31 (2018).

  62. Hidalgo, J., Richards, G. A., Jiménez, J. I. S., Baker, T. & Amin, P. Viral hemorrhagic fever in the tropics: report from the task force on tropical diseases by the World Federation of Societies of Intensive and Critical Care Medicine. J. Crit. Care 42, 366–372 (2017).

    Article  Google Scholar 

  63. Malvy, D., McElroy, A. K., de Clerck, H., Günther, S. & van Griensven, J. Ebola virus disease. Lancet (2019).

  64. Lo, T. Q., Marston, B. J., Dahl, B. A. & De Cock, K. M. Ebola: anatomy of an epidemic. Annu. Rev. Med. 68, 359–370 (2017).

    Article  Google Scholar 

  65. Garske, T. et al. Heterogeneities in the case fatality ratio in the west African Ebola outbreak 2013–2016. Philos. Trans. R. Soc. B Biol. Sci. 372, 1–9 (2017).

    Article  Google Scholar 

  66. Kosack, C. S., Page, A. L. & Klatser, P. R. A guide to aid the selection of diagnostic tests. Bull. World Health Organ. (2017).

  67. Carinelli, S., Kühnemund, M., Nilsson, M. & Pividori, M. I. Yoctomole electrochemical genosensing of Ebola virus cDNA by rolling circle and circle to circle amplification. Biosens. Bioelectron. (2017).

  68. Ilkhani, H. & Farhad, S. A novel electrochemical DNA biosensor for Ebola virus detection. Anal. Biochem. (2018).

  69. Chen, Y. et al. Field-effect transistor biosensor for rapid detection of Ebola antigen. Sci. Rep. 7, 4–11 (2017).

    Article  Google Scholar 

  70. Wu, Z. et al. Ultrasensitive Ebola virus detection based on electroluminescent nanospheres and immunomagnetic separation. Anal. Chem. 89, 2039–2048 (2017).

    Article  Google Scholar 

  71. Ciftci, S. et al. The sweet detection of rolling circle amplification: glucose-based electrochemical genosensor for the detection of viral nucleic acid. Biosens. Bioelectron. (2020).

  72. Bauer, M. P., Timen, A., Vossen, A. C. T. M. & van Dissel, J. T. Marburg haemorrhagic fever in returning travellers: an overview aimed at clinicians. Clin. Microbiol. Infect. 21, e28–e31 (2019).

    Article  Google Scholar 

  73. Van Paassen, J. et al. Acute liver failure, multiorgan failure, cerebral oedema, and activation of proangiogenic and antiangiogenic factors in a case of Marburg haemorrhagic fever. Lancet Infect. Dis. 12, 635–642 (2012).

    Article  Google Scholar 

  74. McFee, R. B. Viral hemorrhagic fever viruses. Dis. Mon. 59, 410–425 (2013).

    Article  Google Scholar 

  75. Litvoc, M. N., Novaes, C. T. G. & Lopes, M. I. B. F. Yellow fever. Rev. Assoc. Med. Bras. 64, 106–113 (2018).

    Article  Google Scholar 

  76. Guarner, J. & Hale, G. L. Four human diseases with significant public health impact caused by mosquito-borne flaviviruses: West Nile, Zika, dengue and yellow fever. Semin Diagn Pathol. (2019).

  77. Jácome, R. et al. A yellow flag on the horizon: the looming threat of yellow fever to North America. Int. J. Infect. Dis. (2019).

  78. Jentes, E. S. et al. The revised global yellow fever risk map and recommendations for vaccination, 2010: consensus of the Informal WHO Working Group on Geographic Risk for Yellow Fever. Lancet Infect. Dis. (2011).

  79. Lim, J. M. et al. An electrochemical peptide sensor for detection of dengue fever biomarker NS1. Anal. Chim. Acta. (2018).

  80. Rashid, S., Nawaz, M. H., Marty, J. L. & Hayat, A. Label free ultrasensitive detection of NS1 based on electrochemical aptasensor using polyethyleneimine aggregated AuNPs. Microchem. J. (2020).

  81. Navakul, K. et al. A novel method for dengue virus detection and antibody screening using a graphene-polymer based electrochemical biosensor. Nanomed. Nanotechnol. Biol. Med. (2017).

  82. Hirschmann, J. V. From squirrels to biological weapons: the early history of Tularemia. Am. J. Med. Sci. 356, 319–328 (2018).

    Article  Google Scholar 

  83. Foley, J. E. & Nieto, N. C. Tularemia. Vet. Microbiol. 140, 332–338 (2010).

    Article  Google Scholar 

  84. Cunliffe, W. H. Select Documents on Japanese War Crimes and Japanese Biological Warfare 1934–2006 (U.S. National Archives, 2006).

  85. Dennis, D. T. et al. Tularemia as a biological weapon: medical and public health management. J. Am. Med. Assoc. (2001).

  86. Spehar-Délèze, A. M. et al. Electrochemiluminescence (ECL) immunosensor for detection of Francisella tularensis on screen-printed gold electrode array. Anal. Bioanal. Chem. (2016).

  87. del Río, J. S., Yehia Adly, N., Acero-Sánchez, J. L., Henry, O. Y. F. & O’Sullivan, C. K. Electrochemical detection of francisella tularensis genomic DNA using solid-phase recombinase polymerase amplification. Biosens. Bioelectron. (2014).

  88. Dulay, S. B., Gransee, R., Julich, S., Tomaso, H. & O’Sullivan, C. K. Automated microfluidically controlled electrochemical biosensor for the rapid and highly sensitive detection of Francisella tularensis. Biosens. Bioelectron. (2014).

  89. Pöhlmann, C., Bellanger, L., Drevinek, M. & Elßner, T. Multiplex detection of biothreat agents using an automated electrochemical ELISA platform. Procedia Technol. (2017).

  90. Elsholz, B. et al. Electrical microarrays for highly sensitive detection of multiplex PCR products from biological agents. Biosens. Bioelectron. (2009).

  91. Spehar-Délèze, A. M. et al. Electrochemiluminescence DNA sensor array for multiplex detection of biowarfare agents. Anal. Bioanal. Chem. (2015).

  92. Stoddard, R. A. et al. Detection of anthrax protective antigen (PA) using europium labeled anti-PA monoclonal antibody and time-resolved fluorescence. J. Immunol. Methods 408, 78–88 (2014).

    Article  Google Scholar 

  93. Huang, J. et al. Pyrene-excimer probes based on the hybridization chain reaction for the detection of nucleic acids in complex biological fluids. Angew. Chem. 123, 421–424 (2011).

    Article  Google Scholar 

  94. Singh, A. K., Stanker, L. H. & Sharma, S. K. Botulinum neurotoxin: where are we with detection technologies? Crit. Rev. Microbiol. 39, 43–56 (2013).

    Article  Google Scholar 

  95. Ferreira, J. L. Comparison of amplified ELISA and mouse bioassay procedures for determination of botulinal toxins A, B, E, and F. J. AOAC Int. 84, 85–88 (2001).

    Article  Google Scholar 

  96. Sofi Ibrahim, M. et al. Real-time PCR assay to detect smallpox virus. J. Clin. Microbiol. 41, 3835–3839 (2003).

    Article  Google Scholar 

  97. Yen, C.-W. et al. Multicolored silver nanoparticles for multiplexed disease diagnostics: distinguishing dengue, yellow fever, and Ebola viruses. Lab Chip 15, 1638–1641 (2015).

    Article  Google Scholar 

  98. Dulay, S. B., Julich, S., Tomaso, H. & O’Sullivan, C. K. Development of an immunosensor for the detection of Francisella tularensis antibodies. Anal. Bioanal. Chem. 406, 4685–4690 (2014).

    Article  Google Scholar 

  99. Nasirian, H. Crimean-Congo hemorrhagic fever (CCHF) seroprevalence: a systematic review and meta-analysis. Acta Trop. 196, 102–120 (2019).

    Article  Google Scholar 

  100. Wilke, A. B. B., Beier, J. C. & Benelli, G. Complexity of the relationship between global warming and urbanization—an obscure future for predicting increases in vector-borne infectious diseases. Curr. Opin. Insect Sci. 35, 1–9 (2019).

    Article  Google Scholar 

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Financial support from the UNB Accelerated Master Award and the New Brunswick Innovation Foundation (grant number RAI2019-010) programs is greatly acknowledged.

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C.O. and K.V. wrote, researched, and structured the manuscript. A.I. provided her expertise on sensing platforms and provided editing.

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Correspondence to Connor O’Brien or Anna Ignaszak.

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O’Brien, C., Varty, K. & Ignaszak, A. The electrochemical detection of bioterrorism agents: a review of the detection, diagnostics, and implementation of sensors in biosafety programs for Class A bioweapons. Microsyst Nanoeng 7, 16 (2021).

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