Abstract
Sepsis, the syndrome of infection complicated by acute organ dysfunction, is a serious and growing global problem, which not only leads to enormous economic losses but also becomes one of the leading causes of mortality in the intensive care unit. The detection of sepsis-related pathogens and biomarkers in the early stage plays a critical role in selecting appropriate antibiotics or other drugs, thereby preventing the emergence of dangerous phases and saving human lives. There are numerous demerits in conventional detection strategies, such as high cost, low efficiency, as well as lacking of sensitivity and selectivity. Recently, the aptamer-based biosensor is an emerging strategy for reasonable sepsis diagnosis because of its accessibility, rapidity, and stability. In this review, we first introduce the screening of suitable aptamer. Further, recent advances of aptamer-based biosensors in the detection of bacteria and biomarkers for the diagnosis of sepsis are summarized. Finally, the review proposes a brief forecast of challenges and future directions with highly promising aptamer-based biosensors.
Keywords: Aptamer-based biosensors, Nanomaterials, Diagnosis, Sepsis
Introduction
Sepsis, the syndrome of multiple organ dysfunction caused by immune disorders, is one of the most critical global issues in medicine due to the unacceptably high mortality rate [1–3]. Sepsis is an inflammatory disease mediated by the activation of the innate immune system which was induced by bacterial invasion either directly or indirectly [4, 5]. In particular, the most popular gram-positive isolates are Staphylococcus aureus (S. aureus) and Streptococcus pneumoniae. Meanwhile, Escherichia coli (E. coli), Klebsiella, and Pseudomonas aeruginosa dominate among gram-negative isolates [6, 7]. An epidemic international study of infection and sepsis containing more than 14,000 patients in 1265 participating intensive care units (ICUs) from 75 countries showed that 62% of the positive isolates were gram-negative organisms, 47% were gram-positive, and 19% were fungi [8]. The massive invasion of bacteria makes immunocytes activate and release kinds of cytokines. Some pathogenic components, such as lipopolysaccharide (LPS), can interact with the toll-like receptors (TLRs) of monocytes to activate transcription factor NF-kB which can promote the release of pro-inflammatory cytokines, such as tumor necrosis factor α (TNF-α) and interleukin 6 (IL-6) [9]. C-reactive protein (CRP), an acute-phase protein released by macrophages, remains the most frequently used biomarker for both infection and inflammation diagnosis in clinical practice [10].
According to a primary extrapolation of data from high-income countries, there are 19.4 million cases of severe sepsis annually around the world among 31.5 million cases of sepsis, with potentially 5.3 million death each year [11]. Although overall mortality decreases due to preventive measures, a more rapidly increasingly overall incidence rate of sepsis is revealed, demonstrating a continuing challenge [5]. However, the initial symptoms of sepsis are atypical and nonspecific, which is a clinical syndrome defined by a series of signs, symptoms, laboratory abnormalities, and characteristic pathophysiological derangements, resulting in a delayed diagnosis [5]. As research reported in Critical Care Medicine, over one-third of septic patients with atypical symptoms of infection are more likely to have a higher possibility to delay antibiotic administration and a higher risk of mortality [12]. The potential survival rate of sepsis falls dramatically up to 7.6% per hour without effective antibiotic treatment [13]. It is necessary to achieve the early diagnosis of sepsis to prevent the development of the disease. Sequential Sepsis-related Organ Failure Assessment (SOFA) score and bedside clinical score termed qSOFA (for quick SOFA) are recommended for early identification of sepsis [14]. Clinically, it is necessary to determine the species of pathogenic bacteria in time for the diagnosis of sepsis but conventional methods, such as blood cultures and molecular techniques, require multi-steps, resulting in time-consuming and demanding. They display low sensitivity which delays extremely the treatment of sepsis. The polymerase chain reaction (PCR), based on the detection of bacterial DNA, has the potential to reduce the diagnosis time to hours, but it still fails to detect the low-level blood infection [15–17]. Additionally, these methods are laboratory-based, and trained personnel for operation are needed a lot. In addition, blood biomarkers provide a valuable auxiliary role in the clinical status assessment of sepsis as the markers reflecting the severity of organism after infection and inflammation. Therefore, a rapid and sensitive method to diagnose sepsis in early stages is required urgently to ensure the rapid administration of appropriate antibiotics and prevent the occurrence of severe disease conditions, thereby saving human lives.
Recently, the occurrence of aptamer-based sensors has attracted considerable attention for the diagnosis of sepsis owing to the dramatic efficiency for targets and the accuracy for detection [18]. Nucleic acid aptamers, identified by an in-vitro selection procedure called Systematic Evolution of Ligands by EXponential enrichment (SELEX), are single-stranded oligonucleotides (DNA or RNA) molecules that can bind to targets with high specificity and affinity [19, 20]. The aptamer is becoming increasingly popular nowadays because of the stability, easy accessibility, affordable prices, and minimal immune response compared with antibodies. Interestingly, a drug based on modified RNA aptamer, called Macugen (pegaptanib), has been approved by the Food and Drug Administration (FDA) for the treatment of age-related macular degeneration, showing the first successful commercial commodity [21]. Aptamers composed of nucleic acids can be modified easily by fluorescent dyes to achieve the detection visually [22]. In addition, aptamers are also used in homogenous assays which do not need to separate or wash because they bind to the target directly in a sequence-specific manner [23–25]. Recently, nucleic acid aptamers have been used widely as affinity receptors in combination with various signal transduction strategies based on nanomaterials in different kinds of biosensing platforms, including colorimetry, chemiluminometry, electrochemistry, fluorometry, and fluorescence anisotropy [26–31]. The aptamer-based biosensors have high detection sensitivity because aptamer can easily integrate with the signal amplification strategies, such as rolling circle amplification, CRISPR technology, PCR technology, LAMP technology, and magnetic separation technology. Xu et al. reported a dramatic increase in the sensitivity of bacteria detection through the combination of dual-functional aptamer and CRISPR-Cas12a assisted RCA [32]. Furthermore, the specificity of biosensing platforms comes from aptamer which can interact with the target by the unique structure transformation property of nucleic acid. The stability of aptamers has been improved significantly through the post-selection modification of aptamers and the direct selection of aptamers from libraries bearing modified backbones or nucleobases to ensure the stable functions of aptamer-based sensors [21, 33]. In addition, their inherent physicochemical characteristics of nanomaterials, including ultra-small size, high reactivity, and tunable surface modification, have enabled them to overcome some of the limitations and achieve the expected diagnostic and therapeutic effect [34–42]. The biosensors consist of (nano)biointerface and aptamer have been explored widely to detect bacteria and biomarkers, such as gold nanoparticles (NPs), graphene oxide, and carbon nanotubes, which play an indispensable role in improving the sensitivity and shortening the time in the detection for the target [22, 29, 30, 43]. The VOSviewer bibliometric visualization software was used to analyze co-occurrences on aptamer and (nano)biointerface (Fig. 1).
In this review, the selection method of the nucleic acid aptamer is introduced briefly in the first. Also, recent advances of aptamer-based biosensors (Fig. 2) in the detection of bacteria and biomarkers (Table 1) for the diagnosis of sepsis are summarized. Finally, we summarize the mechanism and notable advantages or disadvantages of aptamer-based sensors in sepsis diagnosis (Table 2).
Table 1.
Targets | Aptamer sequences | Nanomaterials | Sensor type/method | Type of aptamer | Length (nt)a) | Limit of detection (LOD) | References |
---|---|---|---|---|---|---|---|
S. aureus |
I: 5’-TCC CTA CGG CGC TAA CCC CCC CAG TCC GTC CTC CCA GCC TCA CAC CGC CAC CGT GCT ACA AC-3’ II: 5’-TCC CTA CGG CGC TAA CCT CCC AAC CGC TCC ACC CTG CCT CCG CCT CGC CAC CGT GCT ACA AC-3’ |
AuNPs | Aptamer-conjugated GNPs and a resonance light-scattering detection system | DNA | 40 | – | [44] |
I: 5’-TCC CTA CGG CGC TAA CCC CCC CAG TCC GTC CTC CCA GCC TCA CAC CGC CAC CGT GCT ACA ACT TTT TTT TT-3’ II: 5’-TCC CTA CGG CGC TAA CCC CCC CAG TCC GTC CTC CCA GCC TCA CAC CGC CAC CGT GCT ACA ACT TTT TTT T-3’ |
Fe3O4@mTiO2 | Capture platform based on Fe3O4@mTiO2 modified with target aptamer | DNA | 71 | 10–2000 CFU/mL | [45] | |
apt: 5’-GCA ATG GTA CGG TAC TTC CTC GGC ACG TTC TCA GTA GCG CTC GCT GGT CAT CCC ACA GCT ACG TCA AAA GTG CAC GCT ACT TTG CTA A-3’ | – | Vertical capacitance apta-sensors | DNA | 88 |
100 CFU/mL Biofilm: 20% of the area |
[46] | |
apt: 5’-GCA ATG GTA CGG TAC TTC CTC GGC ACG TTC TCA GTA GCG CTC GCT GGT CAT CCC ACA GCT ACG TCA AAA GTG CAC GCT ACT TTG CTA A-3’ | – | Electrical antimicrobial susceptibility test (e-AST) system | DNA | 88 | – | [47] | |
MASA | – | Streptavidin Magnetic Beads | CRISPR-Cas12a assisted RCA | – | – | 102–106 CFU/mL | [32] |
E. coli | apt: 5’-ATC CGT CAC ACC TGC TCT ACT GGC CGG CTC AGC ATG ACT AAG AAG GAA GTT ATG TGG TGT TGG CTC CCG TAT TTT TTT TTT-3’ | Fe3O4@mTiO2 | – | DNA | 81 | [45] | |
apt: 5’-GCA ATG GTA CGG TAC TTC CCC ATG AGT GTT GTG AAA TGT TGG GAC ACT AGG TGG CAT AGA GCC GCA AAA GTG CAC GCT ACT TTG CTA A-3’ | – | Vertical capacitance ap-tasensors | DNA | 88 |
100 CFU/mL Biofilm: 20% of the area |
[46] | |
apt: 5’-GCA ATG GTA CGG TAC TTC CCC ATG AGT GTT GTG AAA TGT TGG GAC ACT AGG TGG CAT AGA GCC GCA AAA GTG CAC GCT ACT TTG CTA A-3’ | – | Electrical antimicrobial susceptibility test (e-AST) system | DNA | 88 | – | [47] | |
Peptidoglycan |
I: 5’-TCG CGC GAG TCG TCT GGG GAC AGG GAG TGC GCT GCT CCC CCC GCA TCG TCC TCC C-3’ II: 5’-TCG CGC GAG TCG TCT GGG GGA CTA GAG GAC TTG TGC GGC CCC GCA TCG TCC TCC C-3’ |
– | – | DNA | I/II: 55 | – | [48] |
OMVs |
I: 5’-ATA CCA GCT TAT TCA ATT GGG TGA GGG GGG GTT CAC AAC GTT AAA GAT AGA CGG GGG AAG ATA GTA AGT GCA ATC T-3’ II: 5’-ATA CCA GCT TAT TCA ATT CCG AGT CCA GAC TCA CCG CCG CCT CCT CAA GAC GTG CTG GAG ATA GTA AGT GCA ATC T-3’ |
– | Enzyme-linked aptamer assay | DNA | I/II: 76 |
E. coli DH5α: 0.13 ± 0.01 μg/mL E. coli K12: 3.70 ± 0.98 μg/mL S.marcescens: 0.23 ± 0.16 μg/m |
[49] |
P.aeruginosa | apt: 5’-CCC CCG TTG CTT TCG CTT TTC CTT TCG CTT TTG TTC GTT TCG TCC CTG CTT CCT TTC TTG-3’ | – | Vertical capacitance aptasensors | DNA | 60 |
100 CFU/mL Biofilm: 20% of the area |
[46] |
apt: 5’-CCC CCG TTG CTT TCG CTT TTC CTT TCG CTT TTG TTC GTT TCG TCC CTG CTT CCT TTC TTG-3’ | – | Electrical antimicrobial susceptibility test (e-AST) system | DNA | 60 | – | [47] | |
K.pneumoniae | apt: 5’-GCA ATG GTA CGG TAC TTC C(N45)-CAA AAG TGC ACG CTA CTT TGC TAA-3’ | – | Electrical antimicrobial susceptibility test (e-AST) system | DNA | 44 | – | [47] |
E. faecalis | apt: 5’-ATC CAG AGT GAC GCA GCA CGA CAC GTT AGG TTG GTT AGG TTG GTT AGT TTC TTG TGG ACA CGG TGG CTT A-3’ | – | Electrical antimicrobial susceptibility test (e-AST) system | DNA | 70 | – | [47] |
LPS | apt: 5’ -CTT CTG CCC GCC TCC TTC C-(45 N)-GGA GAC GAG ATA GGC GGA CAC T-3’ | Gold disk electrodes | Electrochemical | DNA | 86 | 0.01–1 ng/mL | [50] |
Gra AuNPs |
Electrochemical |
8.7 fg/mL 10–50 fg/mL |
[51] | ||||
Gold atomic cluster | Electrochemical | 7.94 × 10–21 M and 0.01aM–1 pM | [52] | ||||
RGO/AuNPs | Electrochemical | 1 fg/mL | [53] | ||||
RGO/AuNPs | Electrochemical | 0.2 fg/mLand 0.001–0.01 pg/mL | [54] | ||||
MoS2 AuNPs RGO | Voltammetric biosensor | 3.01 × 10–5 ng/mL and 5.0 × 10−5 ng/mL to 2.0 × 10–2 ng/mL | [55] | ||||
– | Optical sensor | 5.5 pg/mL– 100 ng/mL | [56] | ||||
SLG | Acoustic wave biosensor |
3.53 ng/mL 0–100 ng/mL |
[57] | ||||
GO | Fluorescence quenching efficiency |
15.7 ng/mL and 25–1600 ng/mL |
[58] | ||||
RGO |
Fluorescence quenching efficiency Continuous Injection-Electrostacking |
8.3 fM | [59] | ||||
IL-6 |
Model number: ATW0082 ATW0077 |
AuNPs | Optical approach | – | – | 1.95 μg/mL | [60] |
apt: 5′-GTC TCT GTG TGC GCC AGA GAC ACT GGG GCA GAT ATG GGC CAG CAC AGA ATG AGG CCC-3′ | AuNPs | Electrochemical | – | – | 1.6 pg/ml | [61] | |
Model number: ATW0077 | Carbon nanotube | Microfluidic-based approach | – | – | 1 pg/mL–10 ng/mL | [62] | |
apt: 5’- GGT GGC AGG AGG ACT ATT TAT TTG CTT TTC T -3’ | GR | Field-Effect Transistor-Based Approach | – | – | 139 fM | [63] | |
– | GR | Field-Effect Transistor-Based Approach | – | – | 618 fM | [64] | |
CRP | apt: 5’-GGC AGG AAG ACA AAC ACG ATG GGG GGG TAT GAT TTG ATG TGG TTG TTG CAT GAT CGT GGT CTG TGG TGC TGT-3’ | – | Optical fiber sensor | DNA | 72 | 2–20 mg/mL | [65] |
apt: 5’-GCC UGU AAG GUG GUC GGU GUG GCG AGU GUG UUA GGA GAG AUU GC-3’ | – | Luminex xMAP technology | RNA | 44 | 0.4 mg/L | [66] | |
apt: 5’-CGA AGG GGA TTC GAG GGG TGA TTG CGT GCT CCA TTT GGT G- 3’ | AuNPs | Optical nanosensor | DNA | 40 | 1.77 pM | [67] |
Table 2.
Sensor Type/Method | Mechanism of Action | Comments | References |
---|---|---|---|
Aptamer-conjugated GNPs and a resonance light-scattering detection system | Aptamers are combined onto GNPs followed by bead-based amplification, one bacterial cell was capable of generating more than 104 GNPs after amplification, and amplified GNPs could be detected by the light-scattering–sensing system | Very short detection time. The detection of a single cell can be reached within 1.5 h without complicated equipment such as thermal cyclers or centrifuges | [44] |
CRISPR-Cas12a assisted RCA | The specificity based on the dual functionalized aptamers can initiate bioconjugation to specifically recognize the protein targets and can also convert the protein recognition to nucleic acid signals | Accurate identification and high-sensitive detection of MRSA. Dual amplification of the nucleic acid signal | [32] |
Capture platform based on Fe3O4@mTiO2 modified with target aptamer | First, the complex was incubated with blood samples and the aptamer would connect with the target bacteria. After that, the bacteria captured by Apt-Fe3O4@mTiO2 NPs were concentrated with the help of the magnetic field | High bacterial-captured efficiency of about 80%, short detection time within 2 h, and little cross-react with the nontarget components in blood | [45] |
Fe3O4-Ce6-Apt nanosystem | Simultaneous blood bacterial species identification and enrichment can be achieved in a single step, and then, enriched bacteria can be detected with fluorescence microscopic determination | Identify and enrich the bacteria in the sepsis blood sample for 1 h. Blood disinfection | [68] |
Enzyme-linked aptamer assay | Construct ELAA | High sensitivity to bacterial OMVs as low as 25 ng/mL. A new possibility for the development of cell-free bacterial sensors using bacterial OMVs instead of living bacterial cells | [49] |
Vertical capacitance aptasensors | Some bacteria, culture in blood culture media comprising blood (0.2 mL) and culture media (0.8 mL), the biofilm formation and bacterial growth could be detected by measuring capacitance changes at f = 0.5 and 10 kHz, respectively. After treated with antibiotics, the sensitivity of bacteria to antibiotics can be judged by this change | Short AST time within 12 h | [46] |
e-AST system | The e-AST system is composed of 60 aptamer-functionalized capacitance sensors, of which 2 sensors were used for the negative control, 3 sensors for positive control, and other 55 sensors for the determination of antibiotic sensitivity to 11 antibiotics at 5 different concentrations | Short AST time within 6 h | [47] |
Voltammetric biosensor | After using aptamers immobilized by RGO, and MoS2 is also applied as the matrix of the biosensor with the application of RGO and AuNPs | Simplified operation sequence with fast response and high recovery rate. PEI-rGO-MoS2 nanocomposite with a larger specific surface area, thermal stability and electrical conductivity increases the sensitivity of the sensor | [55] |
Acoustic wave biosensor | The SLG film first connects with CS, and then the amino groups in the CS react with the aldehyde in GA to form C = N bonds. After that, the aldehydes groups in GA react with the amine-functionalized aptamer, which is ready for the specific detection of endotoxin | Rapid, simple operations and low costs. Excellent stability from the air phase to the liquid phase | [57] |
Microfluidic-based approach | Real-time response of the sensor conductance is monitored with increasing concentration of IL-6, exposure to the sensing surface in buffer solution, and clinically relevant spiked blood samples | Sensitive detection of IL-6 at low concentrations | [62] |
Luminex xMAP technology | xMAP assays typically employ a sandwich-type format using antibodies for the capture. For this assay, an RNA aptamer that binds CRP is conjugated to beads to act as the capture agent | The number and type of analytes by using aptamers alone or in conjunction with antibodies expand and the use of sample volumes is low | [66] |
Optical sensor | The signal output mode is an optical image, small changes can be converted into optical signals for output | Compatibility to a wide range of surface modifications. The detection limit of the sensor slightly changed with increased use. Some cross-reactivity towards the unspiked human serum | [56, 60, 65, 67] |
Fluorescence quenching efficiency | The concentration of LPS can be quantitatively analyzed by observing fluorescence changes | Little consumption of sample. Low recovery of serum sample | [58, 59] |
Field-Effect Transistor-Based Approach | The graphene surface immobilized aptamer is unfolded without IL-6 and it would fold after binding with the target. These aptamer structural changes bring the negative charges in IL-6 to the proximity of the graphene-liquid interface | Low-voltage operation (< 1 V), inherent gain amplification, biocompatibility and miniaturization | [63, 64] |
Electrochemical | Electrochemical sensors are constructed using various nanomaterials |
Gold disk electrodes: Short detection time and little cross-interaction reactivity to plasmid DNA, RNA, proteins, saccharides, and/or lipids which are most likely to coexist with LPS assay Gra AuNPs: Overcome the disadvantage of limited nicking endonuclease recognition and integrate molecular biological technology and nano-biotechnology with electrochemical detection to cascade signal amplification, which can detect target LPS down to the femtogram level Gold atomic cluster: Simple sensor fabrication compared with other electrochemical sensors for LPS RGO/AuNPs: Short LPS detection time within 35 min. Enhanced electrode performance and low LOD down to femtomolar level AuNPs: Label-free detection, simple experimental protocol, high selectivity and low limit of detection |
[50–54, 61] |
The SELEX of aptamer
Nowadays, the selection of aptamers is on the basis of systematic evolution of ligands by SELEX which is a gold-standard strategy that can select specific and sensitive aptamers from random single-stranded nucleic acid sequence library [69]. In 1990, Ellington and Szostak successfully screened out oligonucleotides and named the “aptamer”, which is the first time to get aptamer from RNA library through this method [19, 20]. Briefly, there are three steps included in the selection cycle for DNA [70]. First of all, targets are incubated with the library containing randomized sequences, obtaining a complex of target and sequences. Secondly, nonspecific aptamers and the targets are separated respectively, and bound sequences are preserved. Finally, the proper sequences will be amplified through PCR. The selection cycle is then repeated until the sequence of the desired affinity is enriched. In every selection round, more affiliative aptamers are selected (Fig. 3). There are tiny differences of the SELEX for RNA aptamers that RNA should reverse transcription into DNA first and homologous DNA is transcribed into RNA after the selection.
However, there are some demerits in the traditional methods, such as time-consuming and huge costs [71]. Nowadays, some new methods based on traditional SELEX have been developed to overcome shortcomings, like cell SELEX, magnetic bead-based SELEX, in vivo SELEX, in Silico SELEX and so on, which aims to save time, use expediently and raise efficiency [69, 70, 72].
Aptamer-based detection of pathogenic bacteria
Sepsis, a serious infection syndrome that can cause tissue damage and multisystem organ failure, is usually due to the presence of pathogenic bacteria in the bloodstream, resulting in high mortality in the world [73]. Importantly, sepsis has a high mortality rate due to the inability to quickly identify pathogens in the early stages of infection. Conventionally, blood culture, called the “gold standard”, is mostly used for bacteria detection in clinical, hence time-consuming, costly, and trained personnel for the operation needed in great demand.
Therefore, the rapid, accurate, and easy detection of bacteria is required urgently for the early diagnosis and therapy of sepsis. Aptamer-based sensors have a great potential to solve this problem because of sensitivity, specificity, and rapidity. Here, we discuss some articles about the detection of sepsis-related bacteria through aptamer-based sensors.
Aptamer-based detection of a single type of pathogenic bacteria
This section pays attention to sensors designed for detecting pathogenic whole cells that can be targeted by aptamers. The first example of aptamer-based sensors that will be introduced was created to detect S. aureus, a common pathogen of sepsis [44, 74]. First of all, SA17 and SA61, two DNA aptamers that showing high specificity and nanomolar affinity with S. aureus, were modified on magnetic beads and gold nanoparticles (GNPs) separately. After that, quantitative PCR (qPCR) was used to quantify the number of aptamers or aptamer-conjugated GNPs linked with single S. aureus cells. To improve the sensitivity of detection to S. aureus, aptamers were attached with NPs followed by amplification based on magnetic beads (Fig. 4). Using this ingenious way, a single S. aureus cell could be detected within 1.5 h without expensive equipment.
In another study, Xu et al. realized the detection for Methicillin-Resistant Staphylococcus aureus (MRSA) using dual-functional aptamer and CRISPR-Cas12a assisted RCA[32]. Different from the recognition of the whole cell, the aptamer recognizes MRSA depending on the penicillin-binding proteins2a (PBP2a), which shows a low affinity for β-lactam antibiotics. The biosensing process could be divided into two steps: bacteria isolation based on the protein A aptamer (Apt A) and signal amplification. Protein A is a membrane protein shared by both MRSA and S. aureus. In the first step, Streptavidin Magnetic Beads (SMBs) were mixed with Apt A to get the capture complex (SMBs-Apt A), and the protein A positive bacteria could be enriched by the SMBs-Apt A complex via the aptamer-protein interaction for the next step. The second aptamer (Apt B) was made of PBP2a specific aptamer and a Blocker. The Blocker was released from Apt B to touch off the following RCA when the Apt B connected with PBP2a on the surface of MRSA. Via the integration of attached RCA and CRISPR-Cas12a assisted trans-cleavage, dual amplification of the nucleic acid signal was obtained. Furthermore, the output above was consistent with the traditional colony count in the four groups of serum samples, which proved the feasibility of this method for clinical sample detection.
There are some studies that specific target aptamers and magnetic NPs were used together to identify and collect pathogenic bacteria in blood samples with low bacterial concentrations and achieved the rapid qualitative or quantitative detection of bacteria. Shen et al. created a capture platform that consisted of a mesoporous TiO2 coated magnetic NP and modified with target aptamer (Apt-Fe3O4@mTiO2) to reduce the time of detection [45]. First, the complex was incubated with blood samples and the aptamer would connect with target bacteria by folding into the sequence-defined unique structure when it was exposed to bacteria. After that, the bacteria captured by Apt-Fe3O4@mTiO2 NPs were concentrated with the help of the magnetic field to recognize pathogenic bacteria (Fig. 5A). Compared with the control group, the number of S. aureus decreased markedly in the supernatant after captured by a bar magnet within 2 min (Fig. 5B). Meanwhile, the Apt-Fe3O4@mTiO2 nanosensor had a higher efficiency (2 h) than conventional blood culture (8 h) to capture bacteria when 104 CFU/mL bacteria were spiked into blood (Fig. 5C). To verify the reliability of the capture platform at low bacterial concentrations, two representative bacteria, S. aureus and E. coli, were used as model bacteria and the results showed that bacterial capture was up to 80% (10–2000 CFU/mL) (Fig. 5D). In addition to bacterial capture for diagnosis, Wang et al. accomplished efficient extracorporeal blood disinfection taking advantage of magnetic NPs functionalized with chlorin e6 molecules and bacterial species-identifiable aptamers (Fe3O4-Ce6-Apt) (Fig. 5E) [68]. Fe3O4-Ce6-Apt nanosystem could identify and enrich the bacteria through incubated with sepsis blood sample for 1 h and the enriched bacteria were imaged by fluorescence microscopy to quantitatively evaluate the number (Fig. 5F). After near-infrared (NIR) laser irradiation for 5 min (660 nm, 0.8 W/cm2), the agar plate showed a few bacteria (Fig. 5G). Through the conditions of the mice, the treatment for sepsis therapy based on blood disinfection by Fe3O4-Ce6-Apt was evaluated preliminarily (Fig. 5H). Although this aptamer-based sensor has shown advantages in the detection and therapy of sepsis, there is still much unknown about long-term safety in the human body.
Aptamer-based detection of several types of pathogenic bacteria
In clinical practice, sepsis is commonly caused by the infection of a variety of bacteria, therefore, some scholars have constructed aptamers aiming at common components of bacteria, such as peptidoglycan and membrane vesicles [48, 49]. Compared with detecting one type of bacteria, these kinds of aptamers can simultaneously detect the existence of multiple types of sepsis-related bacteria, enabling patients to be diagnosed in an early and timely manner, guiding the use of antibiotics and reducing the mortality rate of patients.
Peptidoglycan is a kind of cell wall polymer shared by both gram-positive and gram-negative bacteria, which plays a critical role in the survival of bacteria and is closely related to the pathogenicity of bacteria [75, 76]. Ana et al. developed adapters that could recognize bacterial peptidoglycans, called Antibac1 (AT1) and Antibac2 (AT2), and found that both AT1 and AT2 have a high affinity for E. coli and S. aureus [77]. In subsequent work, they went on to explore the ability of AT1 and AT2 to bind to causative agents of bacterial-borne sepsis [48]. The results showed that these aptamers bound with high efficiency to the main agents of bacterial sepsis, including four gram-positive and seven gram-negative bacterial, and the affinity of AT1 and AT2 to bacteria was assessed by real-time quantitative PCR. This work demonstrated that ssDNA aptamers targeting bacterial peptidoglycan can recognize multiple types of septic pathogens and can be used to develop universal biosensor probes, which is of great significance for the rapid and sensitive detection of sepsis in clinical practice.
Gram-negative bacteria are the main pathogenic bacteria leading to clinical sepsis. Their outer membrane produces and secretes outer membrane vesicles (OMVs) that can carry several virulence biomolecules and endotoxins [78]. OMVs are known to be important pathogenic agents that improve bacterial survival and trigger immune responses in host cells [79]. Therefore, Shin et al. developed a kind of broadly cross-reactive aptamers for the OMVs from gram-negative bacteria and built an Enzyme-linked aptamer assay (ELAA) (Fig. 6) [49]. The results showed that ELAA successfully detected OMVs from a variety of gram-negative bacteria, which provides a new possibility for the development of cell-free bacterial sensors using bacterial OMVs instead of living bacterial cells. Detection of live bacteria in the blood is difficult due to the immunomodulatory nature of host cells and the bactericidal activity of serum, suggesting that detecting bacterial OMVs in clinical blood samples may be more effective than detecting bacterial cells.
Real-time monitoring of bacterial growth and AST
It is well-known that the survival rate of sepsis falls by an average of 7.6% for every hour of delay ineffective antibiotic treatment [13]. Patients’ survival could be highly improved if they received timely and effective antibiotic treatment, but antimicrobial susceptibility test (AST) results usually require more than three days with conventional methods [80–82]. In addition to the quantitative and qualitative detection of bacteria, the aptamer sensor can monitor the real-time growth of bacteria and biofilm, which continuously and timely evaluate the internal infections and the effectiveness of antibiotics [46, 47]. For instance, Song et al. developed a vertical capacitance aptamer-functionalized sensor (Fig. 7) that significantly shorten the AST time to within 12 h [46]. They found that when bacteria, including E. coli, S. aureus, and Pseudomonas aeruginosa, were cultured in blood culture media comprising blood (0.2 mL) and culture media (0.8 mL), the biofilm formation and bacterial growth could be detected by measuring capacitance changes at f = 0.5 and 10 kHz, respectively. After treated with antibiotics, the sensitivity of bacteria to antibiotics could be judged by this change. This study demonstrated that an aptamer-functionalized sensor could be used as an alternative tool for detecting bacteria and rapid AST in positive blood culture without the need for sub-culturing.
Furthermore, Lee et al. developed an electrical AST (e-AST) system, which shortens the AST time to only 6 h [47]. The e-AST system was composed of 60 aptamer-functionalized capacitance sensors, of which 2 sensors were used for the negative control, 3 sensors for positive control, and other 55 sensors for the determination of antibiotic sensitivity to 11 antibiotics at 5 different concentrations. To evaluate the performance of the e-AST system, 4,554 tests were conducted on 30 clinical strains isolated from septic patients. The results showed an estimated 97% classification agreement between the e-AST system and the gold standard broth microdilution (BMD) test, indicating its great potential for clinical application. Although the diagnosis of sepsis with e-AST may be more expensive, it is significant to save patients suffering from sepsis.
Aptamer-based detection of sepsis-related biomarkers
In addition to the successful detection of pathogenic bacteria in the early period of sepsis, it is necessary to monitor the biomarkers timely which are helpful to judge the occurrence and stage of sepsis and observe systematic conditions [83]. Biomarkers, especially from the blood, make significant changes of content when inflammatory responses occur in the early time with the happening of two molecular patterns [84]. Changes in their levels indicate a state of inflammatory response in the body that cannot be provided by the methods of diagnosing pathogens. However, it is still a challenge to find an accurate and quantitative way to detect biomarkers in the human blood. Compared with frequently-used methods of detecting biomarkers like mass spectrometry (MS) and antibody-based technologies, aptamer-based sensors have shown a huge potential in recent years because of their superiorities like low costs, wide detection ranges, low immunogenicity, and sufficient sensitivity [85–87]. Several biomarkers are associated with the occurrence and development of sepsis, such as LPS, IL-6, and CRP [88]. In the following sub-section, some aptamer-based sensors for detecting sepsis-related serum biomarkers are discussed.
LPS
LPS, called endotoxins, are the major glycolipid molecule in the cell walls of gram-negative bacteria which is the main difference between gram-negative and gram-positive bacteria [89]. Many investigations have highlighted the impact of LPS in the development of sepsis and LPS interacts with the special cellular receptors such as Toll-like receptor-4/MD2 and CD14 to produce inflammatory cytokines [90]. The release of LPS can cause a series of cascading inflammatory pathological reactions, which lead to the occurrence of sepsis. Therefore, LPS is considered an important biomarker for the diagnosis of sepsis.
Over the last few decades, the detection methods of LPS have been continuously developed. Previous methods, such as the rabbit pyrogen test (RPT) [91], the Limulus amoebocyte lysate (LAL) [92], the monocyte activation test (MAT) [93], the recombinant factor C (rFC) [94], and the EndoLISA [95], cannot be routinely used to analyze clinical sepsis samples because of their disadvantages of temperature dependence, high cost, inconsistent, and long testing time. However, studies have shown that the LPS test methods based on aptamers were used for the early diagnosis of sepsis in the past few years, which have the advantages of sensitivity, specificity, high affinity, low cost, and time-saving.
To capture LPS, electrodes have been modified by graphene oxide (GO) and GNPs to detect LPS. Kim et al. used a method based on the nonequilibrium capillary electrophoresis of equilibrium mixtures to identify LPS [50]. It did not include the systematic evolution of ligands by exponential enrichment (NECEEM-based non-SELEX) method. This method constructed an electrochemical aptamer sensor on a gold electrode with a high-affinity LPS binder B2. The linear detection range of the electrochemical aptamer sensor for LPS was from 0.01 to 1 ng/mL. Compared with the traditional strategy of diagnosing sepsis, the time of this method was significantly shorter, however, the extensive application of this aptamer sensor was limited by its low sensitivity. To improve their sensitivity, signal amplification strategies should be considered. Bai et al. designed a new type of aptamer-based electrochemical platform through the combination of two typical signal amplification strategies to achieve the ultra-sensitive detection of LPS [51]. Firstly, the three-way DNA junction-aided enzymatic recycling could increase the electrical signal by increasing the number of capture probes. Besides, the GO nanocomposite material further enhanced the electrochemical signal. The sensitivity of this method was down to femtogram level (8.7 fg/mL), with a linear range of 6 orders of magnitude (from 10 fg/mL to 50 ng/mL). This method obtained better sensitivity compared with the previous study, but the complex manufacturing process of the aptamer sensor would limit its clinical application. Interestingly, Posha and co-workers reported an ultrasensitive electrochemical biosensor that does not require additional signal amplification strategies [52]. Gold clusters were used as electrodes because of their excellent merits, such as fast electron transfer and good water solubility, and then the strong affinity of 5' end amino groups of the aptamer was fixed on the surface of the gold electrode. An electrochemical biosensor could be produced to monitor the concentration of LPS by using the allowed or blocked electron transfer in the surface-assembled molecule. Aptamers immobilized by gold atomic cluster were mediated in this biosensor. The lower detection limit of this sensor was 7.94 × 10–21 M, which was at the attomolar level. And the linear range was from 0.01 aM to 1 pM, which was with a linear response of 9 orders of magnitude (Fig. 8). Therefore, this aptamer biosensor had higher sensitivity, simple structure and preparation process, and had a broad application prospect in the detection of LPS in sepsis.
Besides, in the last few years, RGO and AuNPs have been used to immobilize aptamers. Compared with GO, RGO has higher electrical conductivity, better ductility, thermal stability, and has received more attention in the biological analysis [96]. For example, Pourmadadi et al. modified aptamers on the surface of a glassy carbon electrode (GCE) via RGO and AuNPs, which were successfully used in the analysis of serum of patients and normal people [53]. In another case, the research by Yazdian et al. used RGO-Au NPs to modify electrodes to immobilize thiolated aptamer that specifically binds to endotoxin [54]. After using aptamers immobilized by RGO, the nanomaterial with better performance enabled the aptamer sensor to possess higher sensitivity in LPS detection. The detection lower limit and dynamic range of the sensor were 0.2 fg/mL and 0.001–0.01 pg/mL, respectively. Further, molybdenum disulfide (MoS2) was also applied as the matrix of the biosensor with the application of RGO and AuNPs (Fig. 9) [55]. The high electrical conductivity and large specific surface area of the new nanocarrier can greatly amplify the electrochemical signal and enhance the sensitivity of the aptamer sensor. It was linear in the range of 5.0 × 10−5 to 2.0 × 10–2 ng/mL, and the lower LOD was 3.01 × 10−5 ng/mL. In addition, the method had a good recovery rate for serum samples and a broad application prospect in the field of trace analysis of LPS in sepsis diagnosis. The label-free aptamer sensor in this study could simplify the operation sequence and had a fast response speed. Some studies by An et al. and Ji et al. also used label-free aptamer sensors to detect LPS [56, 57].
Also, there were some studies using aptamers labeled with 6-carboxyfluorescein (6-FAM) to detect LPS. For instance, Zhang et al. designed a 6-FAM labeled aptamer as a fluorescent probe to detect LPS, by combining the advantages of the aptamer's specific binding ability and the fluorescence quenching effect of GO [58]. However, the linear range of this probe for LPS was 25–1600 ng/mL and the lower LOD was 15.7 ng/mL. Therefore, the detection sensitivity was low, and the study did not mention whether this method could be effectively applied in clinical practice. There was a significant improvement in Niu et al. [59]. Based on the fluorescence quenching effect in the study, they designed a microfluidic chip based on the continuous injection-electrostacking to couple RGO and FAM-aptamer so that the aptamer could be combined with LPS to achieve the purpose of detection. The detection limit of this method was 8.3 fM (8.3 × 10–4 Eu/mL) and the sensitivity is higher. This aptamer-based biosensor can detect LPS in injections and serum of human and sepsis model mice, and can quickly distinguish between gram-negative bacteria from gram-positive bacteria and fungus (Fig. 10). Taken together, this method is simple, sensitive and specific, and has a good correlation with the gold-standard LAL assay. As a practical application, it can be used for the detection of sepsis in the clinic.
IL-6
IL-6 is a cytokine that takes part in many immune and inflammatory responses [97]. It plays an important role in the process of the hepatic protein during acute inflammation[98]. In addition, the high level of the IL-6 is a symbol of the high risk of death especially in intra-abdominal sepsis [99]. Compared with a low concentration of IL-6 in the normal condition (lower than 10 pg/mL), the level of IL-6 rises rapidly (even more than 1 pg/ml) when sepsis occurs in adults [100]. Therefore, detecting the change of IL-6 concentration is of great significance for the early diagnosis of sepsis.
To detect IL-6 rapidly, aptamers are usually combined with NPs, such as AuNPs, graphene, nanotubes, to construct sensor systems.
For instance, to develop an optical sensor, Giorgi-Coll et al. combined many aptamers with gold nanoclusters, which was called “sandwich-style” (Fig. 11) [60]. When aptamers recognized and attached IL-6, the gold nanoclusters were aggregated and made the color of the solution change from red to pink in few minutes, which could be measured by a spectrophotometer or a plate reader. It provided a fast method for detecting the concentration of IL-6 in human serum albumin by an optical sensor, which contributes to diagnosing sepsis quickly in clinical.
Tertis et al. developed an electrochemical sensor that was made up of glassy carbon electrodes coated with GNPs and aptamers fixed via gold-sulfur bonds [61]. The designed sensors could test the concentration of IL-6 from 5 pg/mL to 100 ng/mL with a detection limit of 1.6 pg/mL. The sensor could be re-used and be applied to detect other biomarkers in the clinic, which was helpful to diagnose sepsis.
For another sensor like microfluidic sensor, Khosravi et al. modified aptamers conjugated 1-Pyrenebutanoic Acid Succinimidyl Ester (PASE) on the nanotube biosensors [62]. The conductance was reduced with the increase of IL-6 concentration, which caused the change of the electrical signal. This was the first time to use the PASE conjugated aptamers to detect IL-6 and the strategy not only achieved label-free techniques but also completed 10 pg/mL sensitivity in serum.
Hao et al. combined the aptamer with a graphene-based field-effect transistor (GFET) to build the aptameric graphene-based based field-effect transistor(A-GFET) [63]. By relying on online signal processing circuits, the detection of IL-6 was carried out in ten minutes with the limit of 140 fM. In addition, the transistor could detect IL-6 which was stored for a long time. After that, they improved the A-GFET by using PASE as a linker, which caused the range of detection was extended to 618 fM and the sensing performance of A-GFET was improved [64].
CRP
CRP is an acute-phase protein produced by the liver, which is a common biomarker for the diagnosis of infection and inflammation in clinical treatment. The levels of CRP are elevated after infection and inflammation [101]. The level of CRP mostly depends on the amount of tissue damage currently occurring, and it can rise 1000-fold after infection or tissue damage within 24 to 48 h [102]. Elevated serum CRP concentration indicates a potential risk of organ failure and sepsis [103]. Besides, CRP has been widely used as biomarker of neonatal sepsis [104]. Therefore, detecting CRP is of great significance for the early diagnosis of sepsis.
Previous detection techniques, such as antibody-based tests [105] and enzyme-linked immunosorbent assay (ELISA) [106], have been proven to successfully detect CRP, however, some limitations are present. For example, antibody activity is not stable, and different animals have various immune responses, which leads to different specificity and sensitivity to CRP. ELISA can also cause inaccurate results by the color and composition of the medium used in assays [107].
Recently, aptamers have been applied in the detection of CRP. With the rapid development of optical fiber technology, the research of optical fiber sensors (OFS) received increasing attention. Generally, OFS works by detecting changes in light propagation caused by external stimuli. Compared with traditional sensor technologies, OFS is resistant to electromagnetic interference and high temperatures [108]. In addition, OFS has already been used to monitor pH, respiration rate, heart rate, and body temperature in the biomedical fields [109, 110]. Zamarreño and co-workers prepared a biosensor for rapid response and real-time monitoring of sepsis [65]. In this assay, researchers used a layer-by-layer (LbL) technique to combine CRP aptamer film with a fiber optic refractometer based on lossy mode resonances (LMRs). As aptamers bound to CRP, the refractive index of the sensitive coating changed (Fig. 12). The developed sensor could measure CRP in the range of 2–20 mg/L in less than 15 min. This experiment provided a new direction of diagnosis for early sepsis.
Besides, Luminex xMAP technology for clinical diagnosis is a hot topic in the field of bioscience. It allows simultaneous detection of multiple analytes, using a lower sample size and shorter culture time. Furthermore, multiple types of aptamers can be incorporated into this technology [111]. Porschewski et al. reported the use of aptamers in the xMAP technology [112]. To expand the application of aptamers, Bernard et al. coupled an RNA aptamer that binds CRP to beads to act as the trapping agent [66]. Biotinylated anti-CRP antibody coupled to fluorescently labeled streptavidin was used to quantify CRP. An assay for the detection of CRP was successfully established with the detection limit of 0.4 mg/L in diluted serum.
In the last few years, NPs have been used to detect CRP in sepsis. Ghosh et al. reported an optical nanosensor using DNA aptamer as the main sensing element [67]. This biosensor combined a deoxyribonucleic acid aptamer with a quantum dot on the 5’ terminus and a GNPs on the 3’ terminus. When the aptamer bound to CRP, the photoluminescence intensity decreased based on the principle of fluorescence resonance energy transfer (FRET) (Fig. 13). The nanosensor was highly specific for CRP and the minimum detection limit was 1.77 pM. This detection system was synthesized by the wet chemical method and was simple in design. By using specific DNA aptamers, it could also be applied to detect other molecules.
CRP is also a generic biomarker for inflammation, cancer, cardiovascular, and neurological diseases. Currently, several aptamer-based detection strategies have been constructed, e.g., surface plasmon resonance [113], electrochemical [114], Photoelectrochemical (PEC) [115], etc.
Conclusions and perspectives
Diagnosing sepsis at the early stage is of great significance, which could guide doctors to use effective symptomatic and antibiotic treatment. Aptamer-based biosensors may be a powerful complement to the traditional diagnostic method "blood culture" because of their accessibility, rapidity, and stability. The review summarized the recent progress of aptamer-based biosensors in the detection of bacteria and biomarkers for the diagnosis of sepsis. It is highly expected that innovative aptamer-based applications will emerge through rational design and development to achieve an excellent clinical performance.
Although some preliminary success has been achieved in the area of sepsis diagnosis by taking advantage of aptamer-based nano-biosensing systems, some challenges still remain for advancing this technology.
First, many aptamers have been selected against the sepsis-related targets, but only a tiny minority of aptamers’ properties have been investigated. The safety of most aptamers has not been demonstrated, which limits their biological/clinical applications. In addition, the aptamer secondary and tertiary structures can be easily affected by temperature. To maintain its spatial configuration, the aptamers used for sepsis diagnosis should be selected according to the temperature at the time of clinical testing. Cold storage may also change their optimal folded conformation, which leads to lower detection accuracy. Thus, it is very important to develop a technique to avoid such potential thermally-induced conformational issues. Besides, the binding performance of aptamers may be affected in complex matrices. Therefore, it is necessary to keep aptamers' normal function in working matrices, such as using chemical modifications to enhance their stability, and testing the performance of aptamer-based biosensor in its specific working environment is also needed.
Second, although numerous work has been reported for proof-of-concept, there is still no available kits that can be applied at clinical or industrial level. Developing more efficient platforms, which may remedy the cost and inconvenience of aptamer-based nano-biosensing systems, will accelerate the translation from the bench to the clinic. Therefore, aptamer-integrated high-throughput analysis platforms could offer an ideal strategy to detect multiple pathogens and biomarkers from human biofluids that are commonly involved in the occurrence and development of clinical sepsis.
Third, it is critical to have the ability to design an aptamer-based nano-biosensor to offer ultra-high sensitivity and reproducibility with a large dynamic range simultaneously, because the signals of the sensor could be interfered from the biological molecules and aptamer are susceptible to degradation in biological media. A promising strategy may be the appropriate chemical modification in aptamer-based nanosensors, e.g., using polyethylene glycol to enhance resistance to exonucleases.
Fourth, it was reported that some specific aptamers have potential applications in the treatment of sepsis. Integration of the diagnosis and treatment in sepsis could be a promising strategy in the future research direction.
Overall, the aptamer-based sensor systems have a great potential for the early diagnosis of sepsis due to their excellent merits, such as high sensitivity, fast detection speed, wide detection range, easy mass production, etc. The specificity of this type of detecting technique makes it possible to detect different targets only by changing the type of aptamers. In addition to detect pathogens and biomarkers, it can monitor the real-time growth of bacteria and biofilms and also conduct drug sensitivity tests. With the continuous development of interdisciplinary research, it is predictable that the aptamer sensor system will become a crucial diagnostic tool for sepsis.
Acknowledgements
The authors acknowledge Yanjing Ji for the discussion.
Authors' contributions
LL and ZH collected literatures and wrote the original draft. FA, XG, and CZ wrote the original draft and prepared the table. WZ and LM prepared the figures. QZ conceived the idea and revised the manuscript. All authors read and approved the final manuscript.
Funding
The authors are very grateful for the financial support of by the National Natural Science Foundation of China (Grant No. 31900957), Shandong Provincial Natural Science Foundation (Grant No. ZR2019QC007), Innovation and technology program for the excellent youth scholars of higher education of Shandong province (Grant No. 2019KJE015), China Postdoctoral Science Foundation (Grant No. 2019M652326), and National College Students Innovation and Entrepreneurship Training Program of China (S202011065031).
Availability of data and materials
Without restrictions.
Declarations
Ethics approval and consent to participate
Not applicable.
Consent for publication
All authors gave their consent for publication.
Competing interests
The authors declare that they have no competing interests.
Footnotes
Publisher's Note
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Lubin Liu and Zeyu Han contributed equally to this work
References
- 1.Hotchkiss RS, Karl IE. The pathophysiology and treatment of sepsis. N Engl J Med. 2003;348:138–150. doi: 10.1056/NEJMra021333. [DOI] [PubMed] [Google Scholar]
- 2.Cohen J. The immunopathogenesis of sepsis. Nature. 2002;420:885–891. doi: 10.1038/nature01326. [DOI] [PubMed] [Google Scholar]
- 3.Bone RC. The pathogenesis of sepsis. Ann Intern Med. 1991;115:457–469. doi: 10.7326/0003-4819-115-6-457. [DOI] [PubMed] [Google Scholar]
- 4.Kanashiro A, Sônego F, Ferreira RG, Castanheira FVS, Leite CA, Borges VF, et al. Therapeutic potential and limitations of cholinergic anti-inflammatory pathway in sepsis. Pharmacol Res. 2017;117:1–8. doi: 10.1016/j.phrs.2016.12.014. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 5.Hotchkiss RS, Moldawer LL, Opal SM, Reinhart K, Turnbull IR, Vincent JL. Sepsis and septic shock. Nat Rev Dis Prim. 2016 doi: 10.1038/nrdp.2016.45. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 6.Thompson BT. Drotrecogin alfa (activated) did not reduce mortality at 28 or 90 days in patients with septic shock. Ann Intern Med. 2012;157:24774. doi: 10.7326/0003-4819-157-4-201208210-02011. [DOI] [PubMed] [Google Scholar]
- 7.Opal SM, Garber GE, LaRosa SP, Maki DG, Freebairn RC, Kinasewitz GT, et al. Systemic host responses in severe sepsis analyzed by causative microorganism and treatment effects of drotrecogin alfa (activated) Clin Infect Dis. 2003;37:50–58. doi: 10.1086/375593. [DOI] [PubMed] [Google Scholar]
- 8.Vincent JL, Rello J, Marshall J, Silva E, Anzueto A, Martin CD, Moreno R, Lipman J, Gomersall C. International study of the prevalence and outcomes of infection in intensive care units. JAMA. 2009;302:2323–2329. doi: 10.1001/jama.2009.1754. [DOI] [PubMed] [Google Scholar]
- 9.Zhang G, Ghosh S. Molecular mechanisms of NF-κB activation induced by bacterial lipopolysaccharide through Toll-like receptors. J Endotoxin Res. 2000;6:453–457. doi: 10.1179/096805100101532414. [DOI] [PubMed] [Google Scholar]
- 10.Lin KH, Wang FL, Wu MS, Jiang BY, Kao WL, Chao HY, et al. Serum procalcitonin and C-reactive protein levels as markers of bacterial infection in patients with liver cirrhosis: A systematic review and meta-analysis. Diagn Microbiol Infect Dis. 2014;80:72–78. doi: 10.1016/j.diagmicrobio.2014.03.029. [DOI] [PubMed] [Google Scholar]
- 11.Fleischmann C, Scherag A, Adhikari NKJ, Hartog CS, Tsaganos T, Schlattmann P, et al. Assessment of global incidence and mortality of hospital-treated sepsis current estimates and limitations. Am J Respir Crit Care Med. 2016;193:259–272. doi: 10.1164/rccm.201504-0781OC. [DOI] [PubMed] [Google Scholar]
- 12.Filbin MR, Lynch J, Gillingham TD, Thorsen JE, Pasakarnis CL, Nepal S, et al. Presenting symptoms independently predict mortality in septic shock: Importance of a previously unmeasured confounder. Crit Care Med. 2018;46:1592–1599. doi: 10.1097/CCM.0000000000003260. [DOI] [PubMed] [Google Scholar]
- 13.Kumar A, Ellis P, Arabi Y, Roberts D, Light B, Parrillo JE, et al. Initiation of inappropriate antimicrobial therapy results in a fivefold reduction of survival in human septic shock. Chest. 2009;136:1237–1248. doi: 10.1378/chest.09-0087. [DOI] [PubMed] [Google Scholar]
- 14.Singer M, Deutschman CS, Seymour C, Shankar-Hari M, Annane D, Bauer M, et al. The third international consensus definitions for sepsis and septic shock (sepsis-3) JAMA. 2016;315:801–810. doi: 10.1001/jama.2016.0287. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 15.Ottesen EA, Hong JW, Quake SR, Leadbetter JR. Microfluidic digital PCR enables multigene analysis of individual environmental bacteria. Science. 2006;314:1464–1467. doi: 10.1126/science.1131370. [DOI] [PubMed] [Google Scholar]
- 16.Burtscher C, Wuertz S. Evaluation of the use of PCR and reverse transcriptase PCR for detection of pathogenic bacteria in biosolids from anaerobic digestors and aerobic composters. Appl Environ Microbiol. 2003;69:4618–4627. doi: 10.1128/AEM.69.8.4618-4627.2003. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 17.Pechorsky A, Nitzan Y, Lazarovitch T. Identification of pathogenic bacteria in blood cultures: comparison between conventional and PCR methods. J Microbiol Methods. 2009;78:325–330. doi: 10.1016/j.mimet.2009.07.008. [DOI] [PubMed] [Google Scholar]
- 18.Park KS. Nucleic acid aptamer-based methods for diagnosis of infections. Biosens Bioelectron. 2018;102:179–188. doi: 10.1016/j.bios.2017.11.028. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 19.Tuerk C, Gold L. Systematic evolution of ligands by exponential enrichment: RNA ligands to bacteriophage T4 DNA polymerase. Science. 1990;249:505–510. doi: 10.1126/science.2200121. [DOI] [PubMed] [Google Scholar]
- 20.Ad E, Jw S. In vitro selection of RNA molecules that bind specific ligands. Nature. 1990;346:818–822. doi: 10.1038/346818a0. [DOI] [PubMed] [Google Scholar]
- 21.Meek KN, Rangel AE, Heemstra JM. Enhancing aptamer function and stability via in vitro selection using modified nucleic acids. Methods. 2016;106:29–36. doi: 10.1016/j.ymeth.2016.03.008. [DOI] [PubMed] [Google Scholar]
- 22.Zhou S, Lu C, Li Y, Xue L, Zhao C, Tian G, et al. Gold nanobones enhanced ultrasensitive surface-enhanced raman scattering aptasensor for detecting Escherichia coli O157:H7. ACS Sens. 2020;5:588–596. doi: 10.1021/acssensors.9b02600. [DOI] [PubMed] [Google Scholar]
- 23.Deng B, Lin Y, Wang C, Li F, Wang Z, Zhang H, et al. Aptamer binding assays for proteins: the thrombin example-A review. Anal Chim Acta. 2014;837:1–15. doi: 10.1016/j.aca.2014.04.055. [DOI] [PubMed] [Google Scholar]
- 24.Sung TC, Chen WY, Shah P, Chen CS. A replaceable liposomal aptamer for the ultrasensitive and rapid detection of biotin. Sci Rep. 2016;6:1–8. doi: 10.1038/s41598-016-0001-8. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 25.He JL, Wu ZS, Zhou H, Wang HQ, Jiang JH, Shen GL, et al. Fluorescence aptameric sensor for strand displacement amplification detection of cocaine. Anal Chem. 2010;82:1358–1364. doi: 10.1021/ac902416u. [DOI] [PubMed] [Google Scholar]
- 26.Fan Y, Zhang W, Liu Y, Zeng Z, Quan X, Zhao H. Three-dimensional branched crystal carbon nitride with enhanced intrinsic peroxidase-like activity: a hypersensitive platform for colorimetric detection. ACS Appl Mater Interfaces. 2019;11:17467–17474. doi: 10.1021/acsami.9b04320. [DOI] [PubMed] [Google Scholar]
- 27.Li N, Ho CM. Aptamer-based optical probes with separated molecular recognition and signal transduction modules. J Am Chem Soc. 2008;130:2380–2381. doi: 10.1021/ja076787b. [DOI] [PubMed] [Google Scholar]
- 28.Lautner G, Balogh Z, Bardóczy V, Mészáros T, Gyurcsányi RE. Aptamer-based biochips for label-free detection of plant virus coat proteins by SPR imaging. Analyst. 2010;135:918–926. doi: 10.1039/b922829b. [DOI] [PubMed] [Google Scholar]
- 29.Simeonov Y, Weber U, Penchev P, Ringbæk TP, Schuy C, Brons S, et al. 3D range-modulator for scanned particle therapy: development, Monte Carlo simulations and experimental evaluation. Phys Med Biol. 2017;62:7075–7096. doi: 10.1088/1361-6560/aa81f4. [DOI] [PubMed] [Google Scholar]
- 30.Beiranvand ZS, Abbasi AR, Dehdashtian S, Karimi Z, Azadbakht A. Aptamer-based electrochemical biosensor by using Au-Pt nanoparticles, carbon nanotubes and acriflavine platform. Anal Biochem Elsevier Ltd. 2017;518:35–45. doi: 10.1016/j.ab.2016.10.001. [DOI] [PubMed] [Google Scholar]
- 31.Mok W, Li Y. Recent progress in nucleic acid aptamer-based biosensors and bioassays. Sensors. 2008;8:7050–7084. doi: 10.3390/s8117050. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 32.Xu L, Dai Q, Shi Z, Liu X, Gao L, Wang Z, et al. Accurate MRSA identification through dual-functional aptamer and CRISPR-Cas12a assisted rolling circle amplification. J Microbiol Methods. 2020;173:105917. doi: 10.1016/j.mimet.2020.105917. [DOI] [PubMed] [Google Scholar]
- 33.Zhou J, Bobbin ML, Burnett JC, Rossi JJ. Current progress of RNA aptamer-based therapeutics. Front Genet. 2012;3:1–14. doi: 10.3389/fgene.2012.00234. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 34.Yang L, Pijuan-Galito S, Rho HS, Vasilevich AS, Eren AD, Ge L, et al. High-throughput methods in the discovery and study of biomaterials and materiobiology. Chem Rev. 2021 doi: 10.1021/acs.chemrev.0c00752. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 35.Zhou Q, Chen J, Luan Y, Vainikka PA, Thallmair S, Marrink SJ, et al. Unidirectional rotating molecular motors dynamically interact with adsorbed proteins to direct the fate of mesenchymal stem cells. Sci Adv. 2020 doi: 10.1126/sciadv.aay2756. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 36.Zhou Q, Zhao Z, Zhou Z, Zhang G, Chiechi RC, van Rijn P. Directing mesenchymal stem cells with gold nanowire arrays. Adv Mater Interfaces. 2018;5:1–8. [Google Scholar]
- 37.Ji Y, Han Z, Ding H, Xu X, Wang D, Zhu Y, et al. Enhanced eradication of bacterial/fungi biofilms by glucose oxidase-modified magnetic nanoparticles as a potential treatment for persistent endodontic infections. ACS Appl Mater Interfaces. 2021 doi: 10.1021/acsami.1c01748. [DOI] [PubMed] [Google Scholar]
- 38.Fan Y, Liu Y, Zhou Q, Du H, Zhao X, Ye F, et al. Catalytic hairpin assembly indirectly covalent on Fe3O4@C nanoparticles with signal amplification for intracellular detection of miRNA. Talanta. 2021;223:121675. doi: 10.1016/j.talanta.2020.121675. [DOI] [PubMed] [Google Scholar]
- 39.Yu Z, Li Q, Wang J, Yu Y, Wang Y, Zhou Q, et al. Reactive oxygen species-related nanoparticle toxicity in the biomedical field. Nanoscale Res Lett. 2020;15:1–14. doi: 10.1186/s11671-019-3237-y. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 40.Yao J, Yang M, Duan Y. Chemistry, biology, and medicine of fluorescent nanomaterials and related systems: New insights into biosensing, bioimaging, genomics, diagnostics, and therapy. Chem Rev. 2014;114:6130–6178. doi: 10.1021/cr200359p. [DOI] [PubMed] [Google Scholar]
- 41.Biju V. Chemical modifications and bioconjugate reactions of nanomaterials for sensing, imaging, drug delivery and therapy. Chem Soc Rev. 2014;43:744–764. doi: 10.1039/C3CS60273G. [DOI] [PubMed] [Google Scholar]
- 42.Smith BR, Gambhir SS. Nanomaterials for in vivo imaging. Chem Rev . 2017;117:901–986. doi: 10.1021/acs.chemrev.6b00073. [DOI] [PubMed] [Google Scholar]
- 43.Zu G, Cao Y, Dong J, Zhou Q, van Rijn P, Liu M, et al. Development of an Aptamer-Conjugated Polyrotaxane-Based Biodegradable Magnetic Resonance Contrast Agent for Tumor-Targeted Imaging. ACS Appl Bio Mater. 2019;2:406–416. doi: 10.1021/acsabm.8b00639. [DOI] [PubMed] [Google Scholar]
- 44.Chang YC, Yang CY, Sun RL, Cheng YF, Kao WC, Yang PC. Rapid single cell detection of Staphylococcus aureus by aptamer-conjugated gold nanoparticles. Sci Rep. 2013;3:1–7. doi: 10.1038/srep01863. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 45.Shen H, Wang J, Liu H, Li Z, Jiang F, Wang FB, et al. Rapid and Selective Detection of Pathogenic Bacteria in Bloodstream Infections with Aptamer-Based Recognition. ACS Appl Mater Interfaces. 2016;8:19371–19378. doi: 10.1021/acsami.6b06671. [DOI] [PubMed] [Google Scholar]
- 46.Song JH, Lee SM, Park IH, Yong D, Lee KS, Shin JS, et al. Vertical capacitance aptasensors for real-time monitoring of bacterial growth and antibiotic susceptibility in blood. Biosens Bioelectron. 2019;143:111623. doi: 10.1016/j.bios.2019.111623. [DOI] [PubMed] [Google Scholar]
- 47.Lee KS, Lee SM, Oh J, Park IH, Song JH, Han M, et al. Electrical antimicrobial susceptibility testing based on aptamer-functionalized capacitance sensor array for clinical isolates. Sci Rep . 2020;10:1–9. doi: 10.1038/s41598-019-56847-4. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 48.Graziani AC, Stets MI, Lopes ALK, Schluga PHC, Marton S, Ferreira IM, et al. High efficiency binding aptamers for a wide range of bacterial sepsis agents. J Microbiol Biotechnol. 2017;27:838–843. doi: 10.4014/jmb.1611.11004. [DOI] [PubMed] [Google Scholar]
- 49.Shin HS, Gedi V, Kim JK, Lee DK. Detection of Gram-negative bacterial outer membrane vesicles using DNA aptamers. Sci Rep. 2019;9:1–8. doi: 10.1038/s41598-019-49755-0. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 50.Kim SE, Su W, Cho M, Lee Y, Choe WS. Harnessing aptamers for electrochemical detection of endotoxin. Anal Biochem. 2012;424:12–20. doi: 10.1016/j.ab.2012.02.016. [DOI] [PubMed] [Google Scholar]
- 51.Bai L, Chai Y, Pu X, Yuan R. A signal-on electrochemical aptasensor for ultrasensitive detection of endotoxin using three-way DNA junction-aided enzymatic recycling and graphene nanohybrid for amplification. Nanoscale. 2014;6:2902–2908. doi: 10.1039/c3nr05930h. [DOI] [PubMed] [Google Scholar]
- 52.Posha B, Nambiar SR, Sandhyarani N. Gold atomic cluster mediated electrochemical aptasensor for the detection of lipopolysaccharide. Biosens Bioelectron. 2018;101:199–205. doi: 10.1016/j.bios.2017.10.030. [DOI] [PubMed] [Google Scholar]
- 53.Pourmadadi M, Shayeh JS, Omidi M, Yazdian F, Alebouyeh M, Tayebi L. A glassy carbon electrode modified with reduced graphene oxide and gold nanoparticles for electrochemical aptasensing of lipopolysaccharides from Escherichia coli bacteria. Microchim Acta Microchimica Acta. 2019;186:2–9. doi: 10.1007/s00604-018-3107-9. [DOI] [PubMed] [Google Scholar]
- 54.Yazdian F, Rashedi H. Applying reduced graphene oxide-gold nanoparticles for the electrochemical detection of endotoxin. In: Proceedings of the 7th international conference on innovation in science and technology. 2020. p. 280–94.
- 55.Yuan Y, Li L, Zhao M, Zhou J, Bai L. An aptamer based voltammetric biosensor for endotoxins using a functionalized graphene and molybdenum disulfide composite as a new nanocarrier. Anal R Soc Chem. 2018;144:1253–1259. doi: 10.1039/c8an02139b. [DOI] [PubMed] [Google Scholar]
- 56.An Z, Jang CH. Simple and label-free liquid crystal-based optical sensor for highly sensitive and selective endotoxin detection by aptamer binding and separation. ChemistrySelect. 2019;4:1416–1422. doi: 10.1002/slct.201803774. [DOI] [Google Scholar]
- 57.Ji J, Pang Y, Li D, Huang Z, Zhang Z, Xue N, et al. An aptamer-based shear horizontal surface acoustic wave biosensor with a CVD-grown single-layered graphene film for high-sensitivity detection of a label-free endotoxin. Microsyst Nanoeng. 2020 doi: 10.1038/s41378-019-0118-6. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 58.Zhang Z, Yang J, Pang W, Yan G. An aptamer-based fluorescence probe for facile detection of lipopolysaccharide in drinks. RSC Adv R Soc Chem. 2017;7:54920–54926. doi: 10.1039/C7RA10710B. [DOI] [Google Scholar]
- 59.Niu J, Hu X, Ouyang W, Chen Y, Liu S, Han J, et al. Femtomolar detection of lipopolysaccharide in injectables and serum samples using aptamer-coupled reduced graphene oxide in a continuous injection-electrostacking biochip. Anal Chem. 2019;91:2360–2367. doi: 10.1021/acs.analchem.8b05106. [DOI] [PubMed] [Google Scholar]
- 60.Giorgi-Coll S, Marín MJ, Sule O, Hutchinson PJ, Carpenter KLH. Aptamer-modified gold nanoparticles for rapid aggregation-based detection of inflammation: an optical assay for interleukin-6. Microchim Acta Microchimica Acta. 2020;187:1–11. doi: 10.1007/s00604-019-3921-8. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 61.Tertis M, Leva PI, Bogdan D, Suciu M, Graur F, Cristea C. Impedimetric aptasensor for the label-free and selective detection of Interleukin-6 for colorectal cancer screening. Biosens Bioelectron. 2019;137:123–132. doi: 10.1016/j.bios.2019.05.012. [DOI] [PubMed] [Google Scholar]
- 62.Khosravi F, Loeian SM, Panchapakesan B. Ultrasensitive label-free sensing of IL-6 based on PASE functionalized carbon nanotube micro-arrays with RNA-aptamers as molecular recognition elements. Biosensors. 2017;7:1–13. doi: 10.3390/bios7020017. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 63.Hao Z, Pan Y, Huang C, Wang Z, Zhao X. Sensitive detection of lung cancer biomarkers using an aptameric graphene-based nanosensor with enhanced stability. Biomed Microdevices . 2019;21:1–9. doi: 10.1007/s10544-019-0409-6. [DOI] [PubMed] [Google Scholar]
- 64.Hao Z, Pan Y, Huang C, Wang Z, Lin Q, Zhao X, et al. Modulating the linker immobilization density on aptameric graphene field effect transistors using an electric field. ACS Sensors. 2020;5:2503–2513. doi: 10.1021/acssensors.0c00752. [DOI] [PubMed] [Google Scholar]
- 65.Zamarreño CR, Ardaiz I, Ruete L, Muñoz FJ, Matias IR, Arregui FJ. C-reactive protein aptasensor for early sepsis diagnosis by means of an optical fiber device. Proc IEEE Sensors 2013. 2013; p. 4–7.
- 66.Bernard ED, Nguyen KC, DeRosa MC, Tayabali AF, Aranda-Rodriguez R. Development of a bead-based aptamer/antibody detection system for C-reactive protein. Anal Biochem. 2015;472:67–74. doi: 10.1016/j.ab.2014.11.017. [DOI] [PubMed] [Google Scholar]
- 67.Ghosh S, Metlushko A, Chaudhry S, Dutta M, Stroscio MA. Detection of c-reactive protein using network-deployable DNA aptamer based optical nanosensor. In: 2019 IEEE EMBS International Conference on Biomedical & Health Informatics (BHI). 2019. p. 1–4.
- 68.Wang J, Wu H, Yang Y, Yan R, Zhao Y, Wang Y, et al. Bacterial species-identifiable magnetic nanosystems for early sepsis diagnosis and extracorporeal photodynamic blood disinfection. Nanoscale. 2018;10:132–141. doi: 10.1039/C7NR06373C. [DOI] [PubMed] [Google Scholar]
- 69.Saito S. SELEX-based DNA aptamer selection: a perspective from the advancement of separation techniques. Anal Sci. 2021;37:17–26. doi: 10.2116/analsci.20SAR18. [DOI] [PubMed] [Google Scholar]
- 70.Zhuo Z, Yu Y, Wang M, Li J, Zhang Z, Liu J, et al. Recent advances in SELEX technology and aptamer applications in biomedicine. Int J Mol Sci. 2017;18:1–19. doi: 10.3390/ijms18102142. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 71.Darmostuk M, Rimpelova S, Gbelcova H, Ruml T. Current approaches in SELEX: an update to aptamer selection technology. Biotechnol Adv. 2014;33:1141–1161. doi: 10.1016/j.biotechadv.2015.02.008. [DOI] [PubMed] [Google Scholar]
- 72.Kaur H. Recent developments in cell-SELEX technology for aptamer selection. Biochim Biophys Acta Gen Subj. 2018;1862(1):2323–2329. doi: 10.1016/j.bbagen.2018.07.029. [DOI] [PubMed] [Google Scholar]
- 73.Khilnani P. Severe sepsis and septic shock. In: Chawla R, Todi S, editors. ICU Protoc A stepwise approach. India: Springer; 2012. pp. 703–707. [Google Scholar]
- 74.Cross AS, Zierdt CH, Roup B, Almazan R, Swan JC. A hospital-wide outbreak of septicemia due to a few strains of Staphylococcus aureus. Am J Clin Pathol. 1983;79:598–603. doi: 10.1093/ajcp/79.5.598. [DOI] [PubMed] [Google Scholar]
- 75.Vollmer W, Blanot D, De Pedro MA. Peptidoglycan structure and architecture. FEMS Microbiol Rev. 2008;32:149–167. doi: 10.1111/j.1574-6976.2007.00094.x. [DOI] [PubMed] [Google Scholar]
- 76.Schumann P. Peptidoglycan structure. Methods Microbiol. Elsevier Ltd. 2011;38:101–129. doi: 10.1016/B978-0-12-387730-7.00005-X. [DOI] [Google Scholar]
- 77.Ferreira IM, de Souza Lacerda CM, de Faria LS, Corrêa CR, de Andrade ASR. Selection of peptidoglycan-specific aptamers for bacterial cells identification. Appl Biochem Biotechnol. 2014;174:2548–2556. doi: 10.1007/s12010-014-1206-6. [DOI] [PubMed] [Google Scholar]
- 78.Beveridge TJ. Structures of gram-negative cell walls and their derived membrane vesicles. J Bacteriol. 1999;181:4725–4733. doi: 10.1128/JB.181.16.4725-4733.1999. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 79.Jan AT. Outer Membrane Vesicles (OMVs) of gram-negative bacteria: a perspective update. Front Microbiol. 2017;8:1–11. doi: 10.3389/fmicb.2017.01053. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 80.Khan ZA, Siddiqui MF, Park S. Current and emerging methods of antibiotic susceptibility testing. Diagnostics. 2019 doi: 10.3390/diagnostics9020049. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 81.Syal K, Mo M, Yu H, Iriya R, Jing W, Guodong S, et al. Current and emerging techniques for antibiotic susceptibility tests. Theranostics. 2017;7:1795–1805. doi: 10.7150/thno.19217. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 82.Behera B, Anil Vishnu GK, Chatterjee S, Sitaramgupta VVSN, Sreekumar N, Nagabhushan A, et al. Emerging technologies for antibiotic susceptibility testing. Biosens Bioelectron. 2019;142:111552. doi: 10.1016/j.bios.2019.111552. [DOI] [PubMed] [Google Scholar]
- 83.Kumar A, Roberts D, Wood KE, Light B, Parrillo JE, Sharma S, et al. Duration of hypotension before initiation of effective antimicrobial therapy is the critical determinant of survival in human septic shock*. Crit Care Med. 2006;34:1589–1596. doi: 10.1097/01.CCM.0000217961.75225.E9. [DOI] [PubMed] [Google Scholar]
- 84.Song J, Moon S, Park DW, Cho H, Kim JY, Park J, et al. Biomarker combination and SOFA score for the prediction of mortality in sepsis and septic shock. Medicine (Baltimore) 2020 doi: 10.1097/MD.0000000000020495. [DOI] [PubMed] [Google Scholar]
- 85.Bauer M, Strom M, Hammond DS. Anything You Can Do, I Can Do Better : can aptamers replace antibodies in clinical diagnostic applications? Molecules. 2019;24:1–13. doi: 10.3390/molecules24234377. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 86.Alizadeh N, Yousef M, Reza S. Aptamer-assisted novel technologies for detecting bacterial pathogens. ScienceDirect. 2017;93:737–745. doi: 10.1016/j.biopha.2017.07.011. [DOI] [PubMed] [Google Scholar]
- 87.Gold L, Ayers D, Bertino J, Bock C, Bock A, Brody EN, et al. Aptamer-based multiplexed proteomic technology for biomarker discovery. Nat Preced. 2010 doi: 10.1371/journal.pone.0015004. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 88.Liu Y, Hou J, Li Q, Chen K, Wang SN, Wang J. Biomarkers for diagnosis of sepsis in patients with systemic inflammatory response syndrome : a systematic review and meta—analysis. Springerplus. 2016 doi: 10.1186/s40064-016-3591-5. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 89.Preston A, Mandrell RE, Gibson BW, Apicella MA. The lipooligosaccharides of pathogenic gram-negative bacteria. Crit Rev Microbiol. 1996;22:139–180. doi: 10.3109/10408419609106458. [DOI] [PubMed] [Google Scholar]
- 90.Rosadini CV, Kagan JC. Early innate immune responses to bacterial LPS. Curr Opin Immunol . 2017;44:14–19. doi: 10.1016/j.coi.2016.10.005. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 91.Welch H. Herbert 0. Calvery WTM and CWP, The Method of Preparation and Test for Bacterial Pyrogen. J Am Pharm Assoc. 1949;71:2955–2957. [Google Scholar]
- 92.Iwanaga S, Miyata T, Tokunaga F, Muta T. Molecular mechanism of hemolymph clotting system in Limulus. Thromb Res. 1992;68(1):1–32. doi: 10.1016/0049-3848(92)90124-S. [DOI] [PubMed] [Google Scholar]
- 93.Franco E, Garcia-Recio V, Jiménez P, Garrosa M, Girbés T, Cordoba-Diaz M, et al. Endotoxins from a pharmacopoeial point of view. Toxins (Basel) 2018;10:1–9. doi: 10.3390/toxins10080331. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 94.Inoue KY, Ino K, Shiku H, Matsue T. Electrochemical detection of endotoxin using recombinant factor C zymogen. Electrochem commun. 2010;12:1066–1069. doi: 10.1016/j.elecom.2010.05.028. [DOI] [Google Scholar]
- 95.Demertzis N. Development of a multiplex sensing platform for the accurate and rapid diagnosis of Sepsis. (Doctoral dissertation, Cardiff University) 2020.
- 96.Lee BR, Kim JW, Kang D, Lee DW, Ko SJ, Lee HJ, et al. Highly efficient polymer light-emitting diodes using graphene oxide as a hole transport layer. ACS Nano. 2012;6:2984–2991. doi: 10.1021/nn300280q. [DOI] [PubMed] [Google Scholar]
- 97.Meyer C, Eydeler K, Magbanua E, Zivkovic T, Piganeau N, Lorenzen I, et al. Interleukin-6 receptor specific RNA aptamers for cargo delivery into target cells. RNA Biol. 2012;9:67–80. doi: 10.4161/rna.9.1.18062. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 98.Pfäfflin A, Schleicher E. Inflammation markers in point-of-care testing (POCT) Anal Bioanal Chem. 2009;393:1473–1480. doi: 10.1007/s00216-008-2561-3. [DOI] [PubMed] [Google Scholar]
- 99.Clinical C, Unit T, Hospital QE. Interleukin 6 is a prognostic indicator of outcome in severe intra-abdominal sepsis. Br J Surg. 1994;81:1306–1308. doi: 10.1002/bjs.1800810914. [DOI] [PubMed] [Google Scholar]
- 100.Hunter CA, Jones SA. IL-6 as a keystone cytokine in health and disease. Nat Immunol . 2015;16:448–457. doi: 10.1038/ni.3153. [DOI] [PubMed] [Google Scholar]
- 101.Kumar S, Tripathy S, Jyoti A, Singh SG. Recent advances in biosensors for diagnosis and detection of sepsis: a comprehensive review. Biosens Bioelectron. 2019;124–125:205–215. doi: 10.1016/j.bios.2018.10.034. [DOI] [PubMed] [Google Scholar]
- 102.Hencst JM. The role of C-Reaction protein in the evaluation and management of infants with suspected sepsis. Adv Neonatal Care. 2003;3:3–13. doi: 10.1053/adnc.2003.50010. [DOI] [PubMed] [Google Scholar]
- 103.Pierrakos C, Vincent JL. Sepsis biomarkers: a review. Crit Care. 2010;14:1–18. doi: 10.1186/cc8872. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 104.Yang AP, Liu J, Yue LH, Wang HQ, Yang WJ, Yang GH. Neutrophil CD64 combined with PCT, CRP and WBC improves the sensitivity for the early diagnosis of neonatal sepsis. Clin Chem Lab Med. 2016;54:345–351. doi: 10.1515/cclm-2015-0277. [DOI] [PubMed] [Google Scholar]
- 105.Meyer MHF, Hartmann M, Keusgen M. SPR-based immunosensor for the CRP detection—a new method to detect a well known protein. Biosens Bioelectron. 2006;21:1987–1990. doi: 10.1016/j.bios.2005.09.010. [DOI] [PubMed] [Google Scholar]
- 106.Dominici R, Luraschi P, Franzini C. Measurement of C-reactive protein: two high sensitivity methods compared. J Clin Lab Anal. 2004;18:280–284. doi: 10.1002/jcla.20038. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 107.Zubiate P, Zamarreño CR, Sánchez P, Matias IR, Arregui FJ. High sensitive and selective C-reactive protein detection by means of lossy mode resonance based optical fiber devices. Biosens Bioelectron . 2017;93:176–181. doi: 10.1016/j.bios.2016.09.020. [DOI] [PubMed] [Google Scholar]
- 108.Correia R, James S, Lee SW, Morgan SP, Korposh S. Biomedical application of optical fibre sensors. J Opt. 2018 doi: 10.1088/2040-8986/aac68d. [DOI] [Google Scholar]
- 109.Shao LY, Yin MJ, Tam HY, Albert J. Fiber optic pH sensor with self-assembled polymer multilayer nanocoatings. Sensors (Switzerland) 2013;13:1425–1434. doi: 10.3390/s130201425. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 110.Fajkus M, Nedoma J, Martinek R, Vasinek V, Nazeran H, Siska P. A non-invasive multichannel hybrid fiber-optic sensor system for vital sign monitoring. Sensors (Switzerland) 2017;17:1–17. doi: 10.3390/s17010111. [DOI] [PMC free article] [PubMed] [Google Scholar]
- 111.Wendt M, Cappuccilli G. Generating conformation and complex-specific synthetic antibodies. Methods Mol Biol. 2017;1575:303–322. doi: 10.1007/978-1-4939-6857-2_19. [DOI] [PubMed] [Google Scholar]
- 112.Porschewski P, Grättinger MAM, Klenzke K, Erpenbach A, Blind MR, Schäfer F. Using aptamers as capture reagents in bead-based assay systems for diagnostics and hit identification. J Biomol Screen. 2006;11:773–781. doi: 10.1177/1087057106292138. [DOI] [PubMed] [Google Scholar]
- 113.Wu B, Jiang R, Wang Q, Huang J, Yang X, Wang K, et al. Detection of C-reactive protein using nanoparticle-enhanced surface plasmon resonance using an aptamer-antibody sandwich assay. Chem Commun. 2016;52:3568–3571. doi: 10.1039/C5CC10486F. [DOI] [PubMed] [Google Scholar]
- 114.Jarczewska M, Rębiś J, Górski Ł, Malinowska E. Development of DNA aptamer-based sensor for electrochemical detection of C-reactive protein. Talanta. 2018;189:45–54. doi: 10.1016/j.talanta.2018.06.035. [DOI] [PubMed] [Google Scholar]
- 115.Zhang X, Chi KN, Li DL, Deng Y, Ma YC, Xu QQ, et al. 2D-porphrinic covalent organic framework-based aptasensor with enhanced photoelectrochemical response for the detection of C-reactive protein. Biosens Bioelectron. 2019;129:64–71. doi: 10.1016/j.bios.2019.01.009. [DOI] [PubMed] [Google Scholar]
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