**3. Fullerene-modified sensors and biosensors**

Sensor and biosensor technology is an important start line in the development of miniature analyzers. This technology is divided into two classes depending on the interaction of the sensor and analyte molecule: if the analyte molecule is transformed on the sensor surface called as catalytic based and if the analyte interacts with the surface called affinity-based sensors and biosensors [5]. The measurement can be performed electrochemically, optically, and piezoelectrically. In electrochemical sensors, electrodes are used as transducers. Different types of electrodes can be used according to the modification and measurement principle. The electrodes can be gold, carbon, platinum, and their derivatives. It is desired to create a modification layer over self-assembly monolayer; thiol containing chemicals can be used for gold and gold derivative electrodes [15]. Carbon derivative electrodes can be used for polymer production and adsorption type studies [16]. Thus, measurement is carried out with electrodes modified with the immobilized recognition agent. If the recognition agent is a catalytic agent (enzyme or nanoparticle), the electroactive species are released as a result of the target molecule that is transformed by recognition receptor. The method of measurement may also vary depending on the type of these species. For example, an amperometric technique is used if an electroactive species is formed, or a potentiometric measurement method is used if an ion is formed. In addition, interaction-based measurement is desired without a reaction between the analyte molecule and the recognition receptor on the electrode surface (DNA, antibody, MIP, polymer, etc.), and impedimetric techniques can be used [15, 17, 18].

Optically designed sensor and biosensor systems use optic systems with optic sensitivity as transducers or surface plasmon resonance systems, which are a highly sensitive system that is used quite frequently today with laser canteen systems. The photons detected by the transducer with chemical reaction light sensing capability that occurs in optic systems can be converted into meaningful signals. In cantilever systems, measurement is performed by creating differences in the angle of the reflected laser signal as a result of the analyte molecule, which is attached to the surface of the cantilever, whose laser signal is reflected under a lever, changes the oscillation of the lever [19]. In surface plasmon resonance type sensors, the laser signal reflected behind the gold bit surface changes with the binding of the target molecule to the dielectric constant of this gold surface [20]. Here, too, the main purpose is the interaction between the analyte molecule and the recognizing receptor. If there is a catalytic effect, a photon sensing transducer, if there is an affinity-based measurement, cantilever or SPR sensor systems are used.

Apart from these two techniques, piezoelectric systems, which are mass detection systems, can be designed as affinity-based instead of catalytic in biosensor and sensor systems. The method principle is the analyte molecule interacts with piezoelectric crystals used as transducers can generate signals by changing the oscillation of the piezoelectric systems [21].

In conclusion, the interaction between the target molecule and the recognition receptor on sensor and biosensor systems can be measured with electrical, optic, and piezoelectric systems. The important point in these measurements is the characteristic of the modification layer on which the recognizing receptor is immobilized. As we mentioned above, the usage of nanomaterials in biosensor and sensor systems is to increase the surface area and electrical conductivity, to create more stable layer for immobilization, and to use nanomaterials catalytically by generating electroactive signals from the electrical characteristics of nanomaterials. With the advantages of these materials, more sensitive and selective sensor and biosensor systems can be developed.

#### **3.1 Fullerene-modified sensors**

As we mentioned above, sensor systems can use molecularly imprinted polymers, nanocomposites, and other polymeric or dendrimer materials as recognition agent, instead of a biomolecule from biological source, and measurement basis can be formed with it. In this section, examples of this type of sensor technologies are given with the use or modifications of fullerene nanoparticles.

Zhong and colleagues performed the fullerene nanoparticles for catalytic activities, fullerenes were covalently modified with cysteine, and then palladium nanoparticles were added to this spherical structure to create Pd@Cys-C60 structure (**Figure 4**) to glucose detection without enzyme [22]. Firstly, the fullerene covalently bonded with the alpha amino group of cysteine on the nucleophilic attack basis in the medium containing the nanoparticles NaOH and EtOH. Then palladium cation was added, and Pd@Cys-C60 nanocomposite material was obtained. As is known, palladium is highly effective catalytic material in nano form. In this way, the researchers modified the glassy carbon electrode with this nanocomposite and developed a sensor system that can measure glucose between 2.5 μM and 1 mM, at the lowest detection limit of 1 μM. In selectivity studies, it gave 4.8% signal to substances such as fructose and ascorbic acid. As a result, sensitive and stable signals were obtained with fullerene, such as glucose sensors modified with previously made palladium nanoparticles [23].

Anusha et al. used fullerene nanomaterials with bimetallic nanoparticles to develop electrochemical sensors for vitamin D3 determination [24]. Copper and nickel metal nanoparticles were used in this study. Glassy carbon electrode was used as the working electrode, and this electrode was modified by dropping C60 in toluene. The C60 was further reduced in the solution KOH solution and then to the solutions containing CuNPs, NiNPs, and nanoparticles were deposited electrochemically on this electrode, respective electrodeposition steps. Modifying the electrode with these nanoparticles is due to their surface area enhancing and catalytic effects. VitD3 was measured by cyclic voltammetry by the electrochemical oxidation on NiNPs-CuNPs-C60-GCE. With the development of the method, 1.25–475 μM

**67**

**Figure 5.**

*C60-acry modified fullerene material.*

*Fullerene Based Sensor and Biosensor Technologies DOI: http://dx.doi.org/10.5772/intechopen.93316*

linearity and 0.0025 μM LOD values were achieved. As a result of the study, a more

Saha and Das have developed a moisture sensor with C60 nanoparticles that immobilized on thick alumina layer [29]. In this study, they created nano-sized cavities on the sensor surface with the use of fullerene nanoparticles. With these gaps, they have improved the surface area and have developed a sensor that can detect even trace amount of moisture not in literature by fullerene advantage. The sensor was briefly prepared by heating a ceramic layer at 900° after being modified with fullerene, alumina, and polyvinyl alcohol, respectively. The sensor enables capacitive measurements to detect moisture at the ppm levels, in the range of 1–25 ppm. Supported with fullerene has the potential to be used successfully in the gas, oil, and food drying industries, due to the small pore sizes, a highly selective

Shetti and colleagues have developed a fullerene-modified GCE biosensor for electrochemical acyclovir (ACV) determination [30]. The GCE modification with fullerene was carried out according to the drying process on the previously mentioned GCE method. In this study, fullerene was dissolved in dichloromethane instead of toluene, dried by dropping on GCE and reduced in KOH. Afterwards, the electrode was immersed in ACV and the accumulation of ACV on the electrode surface was carried out electrochemically. ACV measurement was carried out with DPV, and real sample experiments were carried out by adding ACV to the real samples as spike. With this sensor, ACV linear measurement was achieved between 90 nM and 6 μM and 1.48 nM lower limit. The sensor gave more sensitive results compared to other ACV measurement methods by modification with fullerene [31–35]. Tartaric acid made the most interference on the sensor with 11.6%. In real

Ertuğrul Uygun and colleagues have developed an impedimetric sensor system modified with cortisol-imprinted polymers on fullerene for the determination of cortisol in saliva [36]. In this study, fullerene C60 was dispersed in dimethylformamide and dried on a carbon screen printed electrode. COOH groups were then formed on fullerene by oxidation process in 2 M H2SO4. Afterwards, acrylamide was polymerized with APS around cortisol via these COOH groups, and cortisolimprinted polymers were synthesized on the electrode surface. After removing cortisol with acetic acid, the CE-C60-polyAcry sensor is ready for the determination of cortisol (**Figure 5**). In this study, which was performed in real saliva samples and compared with tandem mass spectrometry, the cortisol measurement was performed between 0.5 and 64 nM and the lowest detection limit of 0.14 nM was achieved. Modification of fullerene with carboxyl groups facilitated the synthesis

sensitive method was developed than similar methods [25–28].

sensor has been developed for other volatile liquids.

sample experiments, a matrix effect of less than 3% is observed.

**Figure 4.** *Palladium nanoparticles and cysteine-modified fullerene particles (Pd@Cys-C60).*

#### *Fullerene Based Sensor and Biosensor Technologies DOI: http://dx.doi.org/10.5772/intechopen.93316*

*Smart Nanosystems for Biomedicine, Optoelectronics and Catalysis*

with the use or modifications of fullerene nanoparticles.

biosensor systems can be developed.

made palladium nanoparticles [23].

**3.1 Fullerene-modified sensors**

immobilized. As we mentioned above, the usage of nanomaterials in biosensor and sensor systems is to increase the surface area and electrical conductivity, to create more stable layer for immobilization, and to use nanomaterials catalytically by generating electroactive signals from the electrical characteristics of nanomaterials. With the advantages of these materials, more sensitive and selective sensor and

As we mentioned above, sensor systems can use molecularly imprinted polymers, nanocomposites, and other polymeric or dendrimer materials as recognition agent, instead of a biomolecule from biological source, and measurement basis can be formed with it. In this section, examples of this type of sensor technologies are given

Zhong and colleagues performed the fullerene nanoparticles for catalytic activities, fullerenes were covalently modified with cysteine, and then palladium nanoparticles were added to this spherical structure to create Pd@Cys-C60 structure (**Figure 4**) to glucose detection without enzyme [22]. Firstly, the fullerene covalently bonded with the alpha amino group of cysteine on the nucleophilic attack basis in the medium containing the nanoparticles NaOH and EtOH. Then palladium cation was added, and Pd@Cys-C60 nanocomposite material was obtained. As is known, palladium is highly effective catalytic material in nano form. In this way, the researchers modified the glassy carbon electrode with this nanocomposite and developed a sensor system that can measure glucose between 2.5 μM and 1 mM, at the lowest detection limit of 1 μM. In selectivity studies, it gave 4.8% signal to substances such as fructose and ascorbic acid. As a result, sensitive and stable signals were obtained with fullerene, such as glucose sensors modified with previously

Anusha et al. used fullerene nanomaterials with bimetallic nanoparticles to develop electrochemical sensors for vitamin D3 determination [24]. Copper and nickel metal nanoparticles were used in this study. Glassy carbon electrode was used as the working electrode, and this electrode was modified by dropping C60 in toluene. The C60 was further reduced in the solution KOH solution and then to the solutions containing CuNPs, NiNPs, and nanoparticles were deposited electrochemically on this electrode, respective electrodeposition steps. Modifying the electrode with these nanoparticles is due to their surface area enhancing and catalytic effects. VitD3 was measured by cyclic voltammetry by the electrochemical oxidation on NiNPs-CuNPs-C60-GCE. With the development of the method, 1.25–475 μM

*Palladium nanoparticles and cysteine-modified fullerene particles (Pd@Cys-C60).*

**66**

**Figure 4.**

linearity and 0.0025 μM LOD values were achieved. As a result of the study, a more sensitive method was developed than similar methods [25–28].

Saha and Das have developed a moisture sensor with C60 nanoparticles that immobilized on thick alumina layer [29]. In this study, they created nano-sized cavities on the sensor surface with the use of fullerene nanoparticles. With these gaps, they have improved the surface area and have developed a sensor that can detect even trace amount of moisture not in literature by fullerene advantage. The sensor was briefly prepared by heating a ceramic layer at 900° after being modified with fullerene, alumina, and polyvinyl alcohol, respectively. The sensor enables capacitive measurements to detect moisture at the ppm levels, in the range of 1–25 ppm. Supported with fullerene has the potential to be used successfully in the gas, oil, and food drying industries, due to the small pore sizes, a highly selective sensor has been developed for other volatile liquids.

Shetti and colleagues have developed a fullerene-modified GCE biosensor for electrochemical acyclovir (ACV) determination [30]. The GCE modification with fullerene was carried out according to the drying process on the previously mentioned GCE method. In this study, fullerene was dissolved in dichloromethane instead of toluene, dried by dropping on GCE and reduced in KOH. Afterwards, the electrode was immersed in ACV and the accumulation of ACV on the electrode surface was carried out electrochemically. ACV measurement was carried out with DPV, and real sample experiments were carried out by adding ACV to the real samples as spike. With this sensor, ACV linear measurement was achieved between 90 nM and 6 μM and 1.48 nM lower limit. The sensor gave more sensitive results compared to other ACV measurement methods by modification with fullerene [31–35]. Tartaric acid made the most interference on the sensor with 11.6%. In real sample experiments, a matrix effect of less than 3% is observed.

Ertuğrul Uygun and colleagues have developed an impedimetric sensor system modified with cortisol-imprinted polymers on fullerene for the determination of cortisol in saliva [36]. In this study, fullerene C60 was dispersed in dimethylformamide and dried on a carbon screen printed electrode. COOH groups were then formed on fullerene by oxidation process in 2 M H2SO4. Afterwards, acrylamide was polymerized with APS around cortisol via these COOH groups, and cortisolimprinted polymers were synthesized on the electrode surface. After removing cortisol with acetic acid, the CE-C60-polyAcry sensor is ready for the determination of cortisol (**Figure 5**). In this study, which was performed in real saliva samples and compared with tandem mass spectrometry, the cortisol measurement was performed between 0.5 and 64 nM and the lowest detection limit of 0.14 nM was achieved. Modification of fullerene with carboxyl groups facilitated the synthesis

**Figure 5.** *C60-acry modified fullerene material.*

of polymers and increased surface area. Sensor regression analysis compared to tandem mass spectrometry was found to be 0.9778.

Another sensor study developed the preparation of molecularly imprinted polymers by making them more advantageous with fullerene for the determination of ATP by Sharma and his colleagues [37]. In this study, fullerene C60 nanomaterials were primarily modified with amide derivatives. After this modification, fullerene derivatives assembled around ATP by crosslinking them with Pd nanoparticles (**Figure 6**). The fullerene derivatives used herein are amide, carboxyl, and uracil functionalized fullerene nanomaterials. This sensor is characterized by complex measuring systems. Concentration determination was carried out capacitive, and characterization of the polymer layer was performed piezoelectrically and voltammetrically. The ATP measurement was carried out piezoelectrically. 0.062 to 1.0 mM linear ATP was measured capacitively, and the lowest detection limit was 0.31 mM.

#### **3.2 Fullerene-modified biosensors**

Biosensor systems use biorecognition agents from biological origin as the recognizing agent. These systems can also be catalytic and affinity-based just as mentioned before. Enzymes are used in catalytic biosensors. The important point here is a catalytic biosensor system can measure the electroactive species or mediators released by enzymatic reaction. In affinity-based biosensors, the basis of the measurement is based on the measurement of the interaction between the biorecognition receptor and the target molecule. These interactions are DNA-DNA, DNAprotein, antigen-antibody, or protein-ligand. In this section, fullerene-modified biosensor systems are discussed.

Pan and Shih fullerenes have developed a piezoelectric-based immunosensor system with C60 nanomaterials [38]. In this system, piezoelectric quartz crystals were modified by spin-coating the toluene solution containing polyvinyl chloride and fullerene onto these crystals. An adsorption type modification was carried out by adding anti-immunoglobulin G on this modification. In this biosensor, IgG determination reached the determination range between 0.0001 and 0.01 mg/mL

**69**

**Figure 7.**

*SH and NH2 modified PTC-NH2-C60.*

*Fullerene Based Sensor and Biosensor Technologies DOI: http://dx.doi.org/10.5772/intechopen.93316*

selectivity.

a 2% matrix effect [40–45].

and the lowest detection limit below 0.0001 mg/mL and has shown a very high

Suresh and colleagues have developed another C60 modified immunosensor [39]. With this sensor, prostate specific antigen was determined, and the lower measurement limit of 0.002 ng/mL was reached. The biosensor can detect PSA in a measuring range from 0.005 to 20 ng/mL. GCE was used as the working electrode in the study. The C60 dissolved in toluene and dried on GCE. CuNPs were then deposited electrochemically on fullerene which was electrochemically reduced in NaOH. Then, the electrode was immersed in hydroquinone (HQ ) solution and electrochemically bound to surface by the application of potential. After that, HQ-modified electrode was activated with EDC/NHS, and anti-PSA was covalently immobilized to this surface. PSA was determined by measuring the hydrogen peroxide reduction of HRP by forming a layer-by-layer on electrode by blocking the active ends exposed with BSA and the secondary antibody labeled with PSA and HRP, respectively. Electrochemical characterization was performed by CV and EIS. The measurement was carried out with the CV method by the principle of measuring the reduction of the HQ. The biosensor in serum showed a more sensitive result than similar studies with its fullerene modification, showing

Zhou et al. performed an ultra-trace amount of miRNA-141 measurement in another fullerene-modified biosensor study [46]. In this study, a new method has been developed that provides a double signal increase. G-quadruplex, which is complementary with miRNA-141, was combined to form the DNA-RNA hybrid. The DNA fragment was then cut with a duplex-specific nuclease, and miRNA-141 was released to triggering the next step and measuring. The reason of the system's ultra-sensitivity is that by C60-modified gold electrodes modified with amino and thiol groups. The fullerene dissolved in toluene, then passed to the water phase by removing toluene. PTC-NH2 was obtained by adding anhydrous ethylenediamine to the solution containing 3,4,9,10-perylenetetracarboxylic dianhydride (PTCDA) (**Figure 7**). PTC-NH2 was mixed with the fullerene in the aqueous phase to form amid groups on the fullerene. Afterwards, more active groups were formed by adding EDC/NHS on C60 by activated Cys. Gold electrode modification

**Figure 6.** *Amide, carboxyl, and uracil modified fullerene polymers for ATP imprinted sensor.*

*Fullerene Based Sensor and Biosensor Technologies DOI: http://dx.doi.org/10.5772/intechopen.93316*

*Smart Nanosystems for Biomedicine, Optoelectronics and Catalysis*

tandem mass spectrometry was found to be 0.9778.

of polymers and increased surface area. Sensor regression analysis compared to

Another sensor study developed the preparation of molecularly imprinted polymers by making them more advantageous with fullerene for the determination of ATP by Sharma and his colleagues [37]. In this study, fullerene C60 nanomaterials were primarily modified with amide derivatives. After this modification, fullerene derivatives assembled around ATP by crosslinking them with Pd nanoparticles (**Figure 6**). The fullerene derivatives used herein are amide, carboxyl, and uracil functionalized fullerene nanomaterials. This sensor is characterized by complex measuring systems. Concentration determination was carried out capacitive, and characterization of the polymer layer was performed piezoelectrically and voltammetrically. The ATP measurement was carried out piezoelectrically. 0.062 to 1.0 mM linear ATP was measured capacitively, and the lowest detection limit was

Biosensor systems use biorecognition agents from biological origin as the recognizing agent. These systems can also be catalytic and affinity-based just as mentioned before. Enzymes are used in catalytic biosensors. The important point here is a catalytic biosensor system can measure the electroactive species or mediators released by enzymatic reaction. In affinity-based biosensors, the basis of the measurement is based on the measurement of the interaction between the biorecognition receptor and the target molecule. These interactions are DNA-DNA, DNAprotein, antigen-antibody, or protein-ligand. In this section, fullerene-modified

Pan and Shih fullerenes have developed a piezoelectric-based immunosensor system with C60 nanomaterials [38]. In this system, piezoelectric quartz crystals were modified by spin-coating the toluene solution containing polyvinyl chloride and fullerene onto these crystals. An adsorption type modification was carried out by adding anti-immunoglobulin G on this modification. In this biosensor, IgG determination reached the determination range between 0.0001 and 0.01 mg/mL

*Amide, carboxyl, and uracil modified fullerene polymers for ATP imprinted sensor.*

**68**

**Figure 6.**

0.31 mM.

**3.2 Fullerene-modified biosensors**

biosensor systems are discussed.

and the lowest detection limit below 0.0001 mg/mL and has shown a very high selectivity.

Suresh and colleagues have developed another C60 modified immunosensor [39]. With this sensor, prostate specific antigen was determined, and the lower measurement limit of 0.002 ng/mL was reached. The biosensor can detect PSA in a measuring range from 0.005 to 20 ng/mL. GCE was used as the working electrode in the study. The C60 dissolved in toluene and dried on GCE. CuNPs were then deposited electrochemically on fullerene which was electrochemically reduced in NaOH. Then, the electrode was immersed in hydroquinone (HQ ) solution and electrochemically bound to surface by the application of potential. After that, HQ-modified electrode was activated with EDC/NHS, and anti-PSA was covalently immobilized to this surface. PSA was determined by measuring the hydrogen peroxide reduction of HRP by forming a layer-by-layer on electrode by blocking the active ends exposed with BSA and the secondary antibody labeled with PSA and HRP, respectively. Electrochemical characterization was performed by CV and EIS. The measurement was carried out with the CV method by the principle of measuring the reduction of the HQ. The biosensor in serum showed a more sensitive result than similar studies with its fullerene modification, showing a 2% matrix effect [40–45].

Zhou et al. performed an ultra-trace amount of miRNA-141 measurement in another fullerene-modified biosensor study [46]. In this study, a new method has been developed that provides a double signal increase. G-quadruplex, which is complementary with miRNA-141, was combined to form the DNA-RNA hybrid. The DNA fragment was then cut with a duplex-specific nuclease, and miRNA-141 was released to triggering the next step and measuring. The reason of the system's ultra-sensitivity is that by C60-modified gold electrodes modified with amino and thiol groups. The fullerene dissolved in toluene, then passed to the water phase by removing toluene. PTC-NH2 was obtained by adding anhydrous ethylenediamine to the solution containing 3,4,9,10-perylenetetracarboxylic dianhydride (PTCDA) (**Figure 7**). PTC-NH2 was mixed with the fullerene in the aqueous phase to form amid groups on the fullerene. Afterwards, more active groups were formed by adding EDC/NHS on C60 by activated Cys. Gold electrode modification

**Figure 7.** *SH and NH2 modified PTC-NH2-C60.*

#### **Figure 8.**

*Modification layers of the fullerene-PAMAM modified anti-Fetuin-A biosensor (red indicated nitrogen groups represent the active immobilization residue).*


#### **Table 1.**

*Comparison of the fullerene-modified sensor and biosensor technology.*

was carried out by forming the Au-SH bond of SH groups on the modified C60. Electrochemical characterization of the biosensor was carried out by EIS and CV, and differential pulse voltammetry (DPV) was used as the method of analysis. The

**71**

*Fullerene Based Sensor and Biosensor Technologies DOI: http://dx.doi.org/10.5772/intechopen.93316*

have reached a very low detection limit.

**4. Conclusions**

**Acknowledgements**

**Conflict of interest**

Au gold

Authors have no conflict of interest.

4-ATP 4-aminothiophenol APS ammonium persulfate

**Acronyms and abbreviations**

program.

target miRNA-141 was determined with this biosensor to measure between 0.1 pM and 100 nM, and the lowest detection limit of 7.78 fM was achieved. As a result of increasing the surface area with fullerene on developed biosensor, the researchers

Uygun et al. have developed an impedimetric Fetuin-A biosensor, modified with Fullerene-PAMAM (G5) [15]. In this study, the gold electrode, as a working electrode, was first modified by forming self-assembly mono layer of 4-aminothiophenol (4-ATP). Then, activated by EDC/NHS poly-hydroxylated fullerene was firstly dropped to this surface. Au-4ATP-C60-OH was modified by PAMAM (G5) dropped to the surface and anti-Fetuin-A antibodies were dropped to the surface, respectively (**Figure 8**). The biosensor compared to ELISA provided linear measurement between 5 and 400 ng/mL and the lowest 1.44 ng/mL measurement opportunity. The fullerene-PAMAM modification has shown that the biosensor is more advantageous than ELISA due to its three-minute determination and high surface area.

Chuang et al. measured glucose with the piezoelectric system using C60 modified with glucose oxidase enzyme [47]. After the enzyme fullerene and glucose oxidase was incubated for 70 hours, it was immobilized on the piezoelectric crystal. In the sensor system where glucose was measured, LOD was found to be 39 μM. It is stated that in the system, which has a linear glucose measurement between 100 μM and

Sensor and biosensor studies have shown that the use of fullerene has been an advantage in these systems. It is summarized in **Table 1** with the complete example.

Nanomaterials are becoming more important and interesting day by day and their usage areas are increasing. In this book section where the sensor and biosensor systems modified with fullerene are explained, how the fuller is adapted to these systems and how it is modified is explained with examples. As a result, fullerene has successfully completed the task and contributed significantly to the development of these systems. The use of fullerene enabled the development of sensitive sensors by increasing the surface area. At the same time, its contribution to being an indestruc-

This chapter was dedicated to our lovely son Bora Metin UYGUN. All figures were created by using https://chemdrawdirect.perkinelmer.cloud/rest/online

tible immobilization material and providing durability cannot be ignored.

10 mM, glucose measurement can be made in real samples.

*Fullerene Based Sensor and Biosensor Technologies DOI: http://dx.doi.org/10.5772/intechopen.93316*

*Smart Nanosystems for Biomedicine, Optoelectronics and Catalysis*

**Analytical method Modification Analyte Linear** 

CuNPs-C60

C60-polyacrylamide

carboxyl-C60, uracil-C60

PVA-C60

HQ-anti-PSA

4ATP- C60 polyOH-PAMAM-anti-FetuinA

*Comparison of the fullerene-modified sensor and biosensor technology.*

Cyclic voltammetry NiNPs-

*represent the active immobilization residue).*

Capacitive Amide-C60,

Piezoelectric Anti-IgG-

Cyclic voltammetry C60-CuNPs-

Differential pulse voltammetry

**Figure 8.**

Electrochemical impedance spectroscopy

Differential pulse voltammetry

Electrochemical impedance spectroscopy

**detection range**

ACV-C60 Acyclovir 90 nM–6 μ M 1.48 nM [30]

IgG 0.0001–0.01

mg/mL

C60-PTC-Cys miRNA-141 0.1 pM–100 nM 7.78 fM [46]

Vitamin D3 1.25–475 μM 0.0024 μM [24]

Cortisol 0.5–64 nM 0.14 nM [36]

ATP 0.062–1 mM 0.31 mM [37]

PSA 0.005–20 ng/mL 0.002 ng/mL [39]

Fetuin A 5–400 ng/mL 1.44 ng/mL [15]

Chronoamperometry Pd@Cys-C60 Glucose 2.5 μM–1 mM 1 μM [22]

*Modification layers of the fullerene-PAMAM modified anti-Fetuin-A biosensor (red indicated nitrogen groups* 

Capacitive C60−Alumina Moisture 1–25 ppm 1 ppm [29]

**LOD Reference**

0.0001 mg/mL [38]

**70**

**Table 1.**

was carried out by forming the Au-SH bond of SH groups on the modified C60. Electrochemical characterization of the biosensor was carried out by EIS and CV, and differential pulse voltammetry (DPV) was used as the method of analysis. The

Piezoelectric C60-GOx Glucose 100 μM–10 mM 39 μM [47]

target miRNA-141 was determined with this biosensor to measure between 0.1 pM and 100 nM, and the lowest detection limit of 7.78 fM was achieved. As a result of increasing the surface area with fullerene on developed biosensor, the researchers have reached a very low detection limit.

Uygun et al. have developed an impedimetric Fetuin-A biosensor, modified with Fullerene-PAMAM (G5) [15]. In this study, the gold electrode, as a working electrode, was first modified by forming self-assembly mono layer of 4-aminothiophenol (4-ATP). Then, activated by EDC/NHS poly-hydroxylated fullerene was firstly dropped to this surface. Au-4ATP-C60-OH was modified by PAMAM (G5) dropped to the surface and anti-Fetuin-A antibodies were dropped to the surface, respectively (**Figure 8**). The biosensor compared to ELISA provided linear measurement between 5 and 400 ng/mL and the lowest 1.44 ng/mL measurement opportunity. The fullerene-PAMAM modification has shown that the biosensor is more advantageous than ELISA due to its three-minute determination and high surface area.

Chuang et al. measured glucose with the piezoelectric system using C60 modified with glucose oxidase enzyme [47]. After the enzyme fullerene and glucose oxidase was incubated for 70 hours, it was immobilized on the piezoelectric crystal. In the sensor system where glucose was measured, LOD was found to be 39 μM. It is stated that in the system, which has a linear glucose measurement between 100 μM and 10 mM, glucose measurement can be made in real samples.

Sensor and biosensor studies have shown that the use of fullerene has been an advantage in these systems. It is summarized in **Table 1** with the complete example.
