Enzymes as Tools in MIP-Sensors

Abstract

Molecularly imprinted polymers (MIPs) have the potential to complement antibodies in bioanalysis, are more stable under harsh conditions, and are potentially cheaper to produce. However, the affinity and especially the selectivity of MIPs are in general lower than those of their biological pendants. Enzymes are useful tools for the preparation of MIPs for both low and high-molecular weight targets: As a green alternative to the well-established methods of chemical polymerization, enzyme-initiated polymerization has been introduced and the removal of protein templates by proteases has been successfully applied. Furthermore, MIPs have been coupled with enzymes in order to enhance the analytical performance of biomimetic sensors: Enzymes have been used in MIP-sensors as “tracers” for the generation and amplification of the measuring signal. In addition, enzymatic pretreatment of an analyte can extend the analyte spectrum and eliminate interferences.

1. Introduction

Biological receptors such as antibodies and enzymes are widely used in affinity technology, in applications where specific molecular recognition is required. These include biosensors, assays, bioseparation, but also applications in the biomedical field, such as medical treatment or drug delivery. However, these biomacromolecules have some drawbacks that limit their use in technology, in particular their limited stability and availability.

In order to substitute antibodies and enzymes by fully synthetic materials in the above-mentioned applications, the concept of molecularly imprinted polymers (MIPs) has been created: Monomers are polymerized in the presence of the target analyte or a derivative thereof, resulting in cross-linked polymer networks with cavities that mimic the active sites of biopolymers, e.g., antibodies, enzymes, or hormone receptors [1,2,3,4]. Molecularly imprinted polymers are more stable under harsh conditions such as high temperature, extreme pH, and organic solvents, and they are potentially cheaper to produce compared to their biological pendants. However, the affinity and especially the selectivity of MIPs are in general lower than those of their biological counterparts, with some honorable exceptions. This research area is therefore raising increasing interest; at present, more than 1200 papers on MIPs are published per year [5,6,7,8,9]. Some ten percent of MIP papers describe artificial receptors for proteins [7,10,11,12,13], including enzymes [13,14,15,16,17,18,19,20,21].

Molecularly imprinted polymers have been mostly developed for binding of targets, thus mimicking the function of antibodies. In addition to these “plastic antibodies”, synthetic catalysts have been created which mimic the substrate conversion by enzymes. Stable analogs of the postulated transition state of the catalyzed reaction are used as the template of the MIP to mimic the active center of the enzyme [22,23,24]. Redox enzymes have been mimicked by integrating metal ions or metal complexes into the polymer matrix of MIPs [25,26,27,28,29]. Moreover, catalytic MIPs have been obtained for reactions for which no natural enzyme catalyst exists [30].

On the other hand, enzymes are useful tools for the preparation of surface-imprinted MIPs and for the optimization of signal transduction in MIP-sensors. Both aspects have not yet been comprehensively discussed in the literature. This article aims to demonstrate the potential of enzymes in the workflow of MIP preparation and for enhancing the analytical performance of MIP-sensors. The following approaches are presented:

• Enzyme-initiated polymerization has been introduced as a green alternative to the well-established chemical polymerization and electrosynthesis.
• Removal of protein templates has been achieved under mild conditions by proteases, especially proteinase K.

Furthermore, MIPs have been coupled with enzymes in order to enhance the analytical performance of biomimetic sensors:

• Enzyme-labeled “tracers” have been used in analogy to competitive immunoassays in MIP sensors.
• The measuring signal of MIP-sensors has been amplified by electro-enzymatic recycling of the redox marker ferricyanide using horseradish peroxidase (HRP).
• The enzymatic pretreatment of the analyte allowed the interference-free electrochemical measurement or the conversion of a non-binding analyte into a target analog of the MIP.

2. Enzymes in the Workflow of the Preparation of Surface-Imprinted MIPs

2.1. Preparation of Surface Imprinted MIPs

MIPs for low-molecular weight targets are often prepared by classical bulk-imprinting techniques. However, for biomacromolecular targets such as proteins, this still remains challenging due to their large size, high surface complexity, and conformational flexibility. Better accessibility of large target molecules can be achieved by generating the binding sites directly at the surface [31]. Various so-called surface-imprinting techniques were developed in the past few years employing in particular (photo)chemical polymerization, electrochemical synthesis, self-polymerization of dopamine by ambient oxygen, as well as enzyme-initiated polymerization (see Scheme 1).

2.1.1. Photo- and Chemically Initiated Polymerization

The initiation of polymerization reactions by the addition of a chemical compound, in combination with UV-irradiation, is a common technique in polymer chemistry and was also applied to the production of MIPs. One approach that combines this technique with the concept of surface-imprinting is the synthesis of MIP nanoparticles (NPs).

In the case of core-shell MIP nanoparticles, the polymer layer is deposited by emulsion or grafting on a preformed support nanosphere. By choosing the appropriate support material, the particle size can be easily varied and specific properties such as fluorescence or magnetism of the core can be beneficial for separation or readout [32]. In this way, MIP nanoparticles for small molecules, e.g., cholesterol [33] but also for proteins, e.g., bovine hemoglobin [34] were prepared.

In 2013, Poma et al. described an approach for the solid-phase synthesis of MIP nanoparticles using a reusable template [35]. Low-molecular weight targets were immobilized on glass beads serving as the solid-phase. Using thermoresponsive polymers, the washing and release of high-affinity MIP nanoparticles from the solid phase could be controlled by temperature changes. In the same year, Ambrosini et al. proposed a comparable approach with elution at lower temperatures compatible with the use of proteinaceous templates [11]. These were immobilized in an oriented way by using affinity ligands in order to improve the binding site homogeneity of the imprinted nanoparticles. Trypsin was chosen as the template, which was later extended to the enzymes kallikrein and ribonuclease A [12]. Metal-chelates served as affinity ligands for surface-bound histidines while the use of the competitive inhibitor p-aminobenzamidine as a ligand enabled the polymerization in close proximity of the protein’s recognition site. In an earlier work by Cutivet et al., the latter approach was used to prepare the first MIP microgels acting as potent trypsin inhibitors [13].

2.1.2. Electropolymerization

Electropolymerization is an elegant way to prepare MIPs directly on the conducting surface of a transducer, e.g., electrodes or quartz crystal micro balance (QCM) and surface plasmon resonance (SPR) chips. Three different methods have been developed with a clear dominance of the last one: Electrochemical generation of the “active” initiator of the radical chain reaction [36], generation of a pH change by water electrolysis to trigger the deposition of the polymer, e.g., chitosan, at the electrode surface [37], and polymer synthesis by anodic oxidation of functional monomers.

The first successful attempts to electrosynthesize MIPs were performed by Malitesta et al. [38] using o-phenylenediamine (o-PD) for glucose, and in the same year Panasyuk et al. used phenol to synthesize a MIP for phenylalanine [39]. These studies initiated the development of a broad spectrum of electrosynthesized MIPs which are mostly based on pyrrole, derivatives of thiophene, phenylenediamines, and other derivatives of aniline. Most of the electropolymerizable monomers can be deposited from aqueous solutions and buffers can serve as supporting electrolytes. Compared to free radical polymerization initiated generally either thermally or by UV light, electropolymerization most often requires no initiator. Electrically conducting polymers can be grown by the electrochemical oxidation of pyrrole and ethylenedioxythiophene (EDOT) monomers, reaching a thickness appropriate for three-dimensionally structured MIPs [40]. Polypyrrole can be overoxidized by applying high potentials which result in the formation of carboxyl groups and the loss of conductivity. EDOT as a functional monomer offers interactions with the target by hydrogen-bonds, electrostatic, and π-π interactions, and shows low nonspecific adsorption of proteins [41]. Aniline [42] and related compounds such as o-phenylenediamine [43,44] and o-aminophenol [45] bear functionalities that can participate in hydrogen-bonding, π-π-, and other types of interactions with the template. The most widespread electrochemical polymerization technique for MIPs is cyclic voltammetry (CV). By varying the number of scan cycles and the scan rate, the thickness and the compactness of the deposited polymer film can be controlled, respectively. Potentiostatic deposition lacks control over film compactness, but the film thickness can be precisely adjusted by the charge consumed during electropolymerization [46,47].

2.1.3. Self-Polymerization

Inspired by adhesive amino acids existing in the elastic byssus threads of mussels, Messersmith et al. were the first to present the spontaneous generation of thin polydopamine coatings (2–50 nm) on different organic and inorganic materials (noble metals, metal oxides, semiconductors, ceramics, and synthetic polymers) by self-polymerization of dopamine at alkaline pH (8.5) [48]. Dopamine was selected, since it combines the catechol (3,4-dihydroxy-l-phenylanaline) and amine (lysine) functionalities that were found in high amounts in secreted adhesive mussel proteins [49]. The polymerization reaction is assumed to be initiated by the oxidation of the catechol moiety via ambient oxygen to a quinone, resulting in layers whose thickness is dependent on the immersion time of the material to be coated and could therefore be adjusted to the dimensions of any proteinaceous target.

Zhou et al. introduced the self-polymerization of dopamine as a tool for the imprinting of proteins [50]. In a mixture containing dopamine, Fe₃O₄ nanoparticles, and human hemoglobin in slightly alkaline buffer (pH 8.0), the NPs were covered with a ca. 10 nm thin layer of polydopamine. After removal of the template they were capable of selectively recognizing hemoglobin with good binding capacity. Since then, the technique of self-polymerization has been employed in several studies for the imprinting of proteins on various platforms such as magnetic [51,52], gold [53], or silica nanoparticles [54,55], silicon nanowires [56], 4-vinylphenylboronic acid-based monolithic skeletons [57], gold electrodes [58,59], or multi-walled carbon nanotubes [60]. These studies showed that apart from the advantage of controllable thickness, MIPs comprised of polydopamine exhibit good to excellent binding properties, have high hydrophilicity, biocompatibility, as well as pH (3–11) and longtime stability [61].

2.1.4. Enzyme-Initiated MIP Synthesis

Enzymatic polymer synthesis is attractive for green polymer chemistry [62], as enzymes work at mild conditions and have good recyclability as well as biocompatibility. So far, three groups of enzymes have been used to initiate polymerization reactions: oxidoreductases (e.g., HRP, laccase), transferases (e.g., glycosyltransferase, acyltransferase), and hydrolases (cellulase, lipase) [63]. Oxidoreductases catalyze the oxidative polymerization of different organic compounds such as phenols or anilines under the consumption of hydrogen peroxide or other peroxides. In the context of vinyl-based and acrylic polymers, enzyme-initiated polymerization recently also stepped into focus. Thereby, oxidoreductases such as HRP [64] produce the radicals that then initiate radical polymerization.

Very recently, HRP-initiated radical polymerization has been introduced by Haupt's group as a tool for the preparation of MIPs for small molecules such as 2,4-dichlorophenoxyacetic acid (2,4-D) and salicylic acid, but also for the protein trypsin [10]. HRP with H₂O₂ as the substrate and a mediator molecule such as acetylacetone generates radicals that can initiate the polymerization of vinyl and acrylate monomers (see Scheme 2).

In order to execute the polymerization in aqueous media, the water-soluble cross-linker 1.4-bis(acryloyl)piperazine was applied. To prevent contamination of the MIP with HRP and to suppress the formation of a polymer shell around the initiator enzyme, a solid-phase synthesis approach was used where the HRP was immobilized on 0.1 mm glass beads. Using this system, MIP-nanogels with diameters between 50 and 300 nm were obtained. The possibility of re-using the glass beads with immobilized HRP to initiate more than one batch of polymer particles was demonstrated for 2,4-D imprinted nanoparticles: Four successive batches of MIP and NIP (non-imprinted polymer) were synthesized with the same immobilized HRP. After polymerization, the HRP-charged glass beads can be easily separated from the polymerization mixture and are washed to eliminate any residual unreacted monomers and polymers. The imprinted nanoparticles were characterized by dynamic light scattering and radioligand binding assays. Particle sizes and binding capacity were rather reproducible between different batches. Above six cycles, the nanogel yield started to decrease, indicating partial inactivation of the immobilized enzyme.

The MIP for 2,4-D showed imprinting factors (IF) of around 5 and good discrimination of structurally related compounds. The MIPs for salicylic acid had a particle size of 150 nm and a maximum IF of 3. For trypsin, the particles had a size of 25 nm and an IF of 4. Regarding their recognition properties, enzyme-initiated MIP nanoparticles were shown to be comparable to or even outperforming their photo-initiated counterparts [10].

2.2. Template Removal by Enzymes

The essential prerequisite for template removal is not to alter the binding sites and integrity of the polymer structure. In fact, the choice of regeneration conditions is a trade-off between complete removal of the target and preservation of the integrity of the binding sites. Methods applied include the application of chaotropic agents, extraction by organic solvents, the use of highly acidic or basic solutions and/or surfactants such as sodium dodecylsulfate (SDS) or Tween 20, sometimes at elevated temperatures [7], and electroelution [10,13,31].

For protein targets, an alternative to harsh solvent extraction is proteolytic digestion, e.g., by proteinase K or trypsin (see Scheme 1). Proteinase K is a serine protease with broad cleaving specificity. The predominant site of cleavage is the peptide bond adjacent to the carboxyl group of aliphatic and aromatic amino acids with blocked alpha amino groups [52]. It is still active even in the presence of some common chemicals which denature proteins, such as SDS, urea, and ethylenediaminetetraacetic acid (EDTA) [65,66]. Therefore, proteinase K is commonly used for nucleic acid isolation and for general protein degradation in cell lysates [65].

Proteinase K and trypsin have been used for template removal in protein imprinting. The process can be performed under mild conditions, which is favorable for retaining the polymer structure. Since after digestion protein fragments still remain in the binding sites of the MIP, intensive washing is required. Hawkins et al. achieved efficient removal of hemoglobin from a polyacrylamide-based MIP [67]. Proteinase K has been successfully used to remove myoglobin (16.7 kDa) from a polyaminophenol-layer [45], canceroembryonal antigen (CEA) from a polypyrrole based MIP [68], trypsin from methacryloylaminobenzamidine based microgels [13], as well as concanavalin A (ConA) (102 kDa) from a polyscopoletin-matrix [69]. In the latter case, proteinase K was used in combination with Tween 20.

3. Enzymes for the Enhancement of the Analytical Performance of MIP Sensors

3.1. Signal Amplification in Electrochemical MIP Sensors

In addition to the utilization in the synthesis of MIPs, electrochemical methods are also used for measuring the binding of both low and high molecular weight targets. Amperometry, differential pulse voltammetry (DPV), and impedance spectroscopy are more sensitive and simple compared to quartz crystal microbalance (QCM) or surface plasmon resonance (SPR). Electrochemical pulse methods offer the possibility to eliminate signals of easily oxidizable substances such as ascorbic acid and catecholamines by selecting the potential window, however at the expense of increased measuring times. Two major principles have been applied:

(i)

Electroactive targets, such as morphine, paracetamol, tamoxifen, and diclofenac can permeate through the cavities of the MIP to the electrode and an electrochemical signal can be generated by the conversion of the target using different electrochemical methods. This principle has been frequently used for drugs which contain phenolic structures but also for a few proteins which show direct electron transfer, e.g., cytochrome c, hemoglobin, and hexameric tyrosine-coordinated heme protein (HTHP) [21,70,71].

(ii)

Binding of the target modulates the diffusive permeation of redox markers in a concentration-dependent manner. This effect has been frequently applied to characterize each step of MIP preparation for electro-inactive targets, such as melamine, methyl parathion, phenobarbital, caffeine, 17β-estradiol, acetylsalicylic acid, and warfarin [72,73,74,75,76]. In addition, this method is frequently applied to quantify the binding of the target analyte. However, it supplies an indirect signal which integrates all changes of the MIP-layer. Using this approach, several papers claim measuring ranges over more than four decades of target concentration and lower limits of detection (LOD) in the sub-nanomolar range for both low- [77,78] and high-molecular weight targets [79,80,81]. Rebinding of the target in the pores of the MIP could be strong for small molecules. On the other hand, the film thickness for surface imprinted layers is lower than the dimension of macromolecular targets. Thus, affinity constants for non-covalent MIPs could hardly reach the sub-nanomolar region. From the practical point of view, it seems questionable to evaluate the tiny current decreases per concentration decade of the cyclic and differential pulse voltammograms.

Enzymes offer further possibilities to enhance the analytical performance and sensitivity of electrochemical MIP sensors as they can be used for signal amplification (see Scheme 3). Electro-enzymatic recycling of the redox marker was successfully applied by Lian et al. for signal amplification in the readout of the target binding of MIPs for the antibiotic kanamycin [82]. In the first system, the ferrocyanide which is formed at the MIP-covered electrode is enzymatically reoxidized by peroxide in the presence of HRP (see Scheme 4). The catalytic action of HRP leads to an increase of the reduction peak in the cyclic voltammogram and the concomitant decrease of the anodic peak. The enzymatic recycling by HRP results in an eight times larger signal for the same MIP system upon addition of peroxide. The authors claim that this signal amplification leads to a shift of the lower limit of detection by two orders of magnitude from 3.9 µM to 28 nM. The second system used the same polypyrrole-based MIP for kanamycin, but used 1,1′-ferrocenedicarboxylic acid as the redox marker and glucose oxidase (GOx). In the presence of glucose—the co-substrate of GOx—the LOD was shifted down to 23 nM, a value comparable with the HRP system. This highly effective principle may be extended for other analytes and the application of alternative electro-enzymatic recycling systems.

3.2. Enzyme-Labels in MIP-Based Affinity Sensors

In 1993, Mosbach and co-workers presented the development of the first molecularly imprinted sorbent assay for the detection of diazepam and theophylline [83]. This method is analogous to competitive immunoassays with the antibody replaced by a MIP. The latter is incubated in a mixture containing both the analyte and a labeled analyte, and the analyte concentration can be assessed from the tracer signal, which decreases with increasing analyte concentration. Since then, several publications have addressed the design and improvement of this technique employing, e.g., different labels and thus readout methods [84]. Besides radiochemical or fluorescent tracers, enzymes have been conjugated with the target molecule, thus facilitating the analyte quantification via an enzymatic reaction (see Scheme 3).

The first enzyme-labeled molecularly imprinted sorbent assay was reported by Surugiu et al. in 2000 [85]. The antigen 2,4-dichlorophenoxyacetic acid was coupled to tobacco peroxidase enabling colorimetric (o-PD/H₂O₂) as well as chemiluminescent (luminol/H₂O₂) detection with linear measuring ranges of 40–600 μg·mL⁻¹ and 1–200 μg·mL⁻¹, respectively. This setup was further developed by coating microtiter plates with imprinted polymer microspheres enabling analyses in a high-throughput format [86], as well as by coating glass capillaries enabling flow-injection competitive assays yielding a dynamic range of 5 pg/mL to 100 ng/mL in a discontinuous detection mode [87].

Piletsky et al. developed imprinted microplates for the detection of epinephrine and atrazine [88]. Here, the monomers were directly polymerized on the microplate walls in the presence of the template. The analytes were conjugated with HRP and the reaction with 2,2′-azino-bis(3-ethylbenzothiazoline-6-sulphonic acid (ABTS) and H₂O₂ was detected. A comparable approach was used by Wang et al. for the detection of estrone in environmental water [89] and by Chianella et al. for the detection of vancomycin in buffer and blood plasma [90]. The latter developed an assay with a high sensitivity and a detection limit of 2.5 pM, which even outperformed analogous immunoassays. Similarly high sensitivity was obtained for an isoproturon-MIP developed by Li et al. by applying electrochemical luminescence [91]. GOx was used as the tracer enzyme and the luminescence signal was detected after the addition of glucose and luminol, yielding a linear measuring range from 90 pM up to 5 nM and a detection limit of 4 pM.

An electrochemical readout has been used for the detection of oxytetracycline [92]. The analyte was labeled with HRP and the activity towards the oxidation of hydroquinone in the presence of H₂O₂ was detected by differential pulse voltammetry, yielding a detection limit of the sensor of 0.65 nM (see Scheme 5).

3.3. Combinations of MIPs with the Enzymatic Conversion of the Analyte

Pretreatment of the analyte by an enzyme can lead to a broadened analyte spectrum by the conversion of “non-target” substances into target analogs or to benefits regarding the measuring conditions (see Scheme 3). Additionally, integrated MIP/enzyme architectures can allow for the elimination of interferences.

A family of electrochemical MIP sensors for the non-steroidal antiestrogen tamoxifen (TAM) and the analgesic drugs paracetamol and aminopyrine was prepared by electropolymerization. For these three electroactive targets, the signal was generated by a redox marker and by the direct anodic oxidation of the target at the MIP-covered electrode. For improving the selectivity and to prevent fouling of the electrode surface, the target analyte was enzymatically converted before the interaction with the MIP-covered electrode.

Signal generation of the TAM sensor by the anodic oxidation of the target leads to a continuous signal decrease in a series of measurements. Obviously, an insulating film is formed from the oxidation products. In order to prevent this adverse effect, another electrode reaction was applied [93]. Pretreatment of the TAM solution with hydrogen peroxide in presence of HRP generated an oxidation product which can be reduced at 0 V. At this potential, fouling of the electrode by formation of a polymer film is circumvented. In the present stage of development, the enzymatic reaction has to be performed in solution because the harsh regeneration of the MIP is not compatible with the stability of the enzyme.

Different electrochemical sensors for paracetamol have been described in the literature [94,95,96,97,98,99] which indicate either the change of diffusional permeability of the MIP layer for a redox marker or the anodic oxidation of paracetamol (PAR). Both methods have severe problems: As described for TAM, the anodic oxidation of phenolic substances leads to an insulating cover and the decrease of the ferricyanide signal is prone to several interferences. To overcome these problems, PAR was enzymatically converted before interaction with the electrochemical MIP-sensor. Combinations of the MIP-electrode with different enzymatic reactions are presented in Scheme 6: The target paracetamol was pretreated with tyrosinase in order to indicate the product at low electrode potential, where electrochemical interferences by ascorbic acid are suppressed and the fouling of the electrode prevented.

The copper enzyme tyrosinase converts a broad spectrum of phenolic compounds using ambient oxygen as the electron acceptor [100,101,102,103,104]. Among them, PAR is converted in two consecutive one-electron oxidation steps into N-acetyl-p-benzoquinone (4-AOBQ) [105] (see Scheme 6). This product generates a cathodic current signal at potentials below −0.1 V [106]. Tyrosinase-catalyzed oxidation of paracetamol has been applied in both an amperometric biosensor for monitoring the degradation of paracetamol and the elimination of its interference in a glucose oxidase-based glucose electrode [107].

The treatment of PAR with tyrosinase resulted in the abolishment of the anodic current signal at 0.6 V and the formation of the cathodic signal at −0.1 V [108]. The current of the PAR-MIP electrode at −0.1 V increased linearly between 2.5 µM and 335 µM (R² = 0.9969) and approached saturation above 550 µM. Most important, the interfering signals for ascorbic acid and uric acid are completely absent, but also the signals for L-DOPA and catechol are reduced to only 20 percent of the signal for paracetamol.

Furthermore the extension of the analyte spectrum by enzymatic pretreatment of the sample has been demonstrated: Phenacetin—a drug which has been withdrawn from the market—is converted by a non-specific esterase to phenetidine [108] (see Scheme 6). Whilst phenacetin did not generate an oxidation current at 0.6 V, its treatment with esterase brought about concentration dependent signals. Control experiments with phenetidine showed in the DPVs a peak at the same potential [109]. The MIP did not discriminate the very similar substances paracetamol and p-phenetidine and showed comparable sensitivities for both substances. This result shows that the combination of the esterase catalyzed hydrolysis with the MIP-covered electrode allows the measurement of phenacetin.

As an alternative to the esterolytic conversion of phenacetin into an electroactive product, it was checked whether horseradish peroxidase catalyzes the O-dealkylation to paracetamol. Contrary to the effective catalysis of N-dealkylation of aminopyrine by HRP [110], the formation of an electroactive product was not observed.

Aminopyrine (AP) is metabolized by liver P450s and HRP to formaldehyde and aminoantipyrine (AAP), which is devoid of the two methyl groups at position N4. A MIP electrode for the target AAP recognized both AAP and AP with comparable sensitivity [110]. Both HRP and the mini-enzyme-Microperoxidase-11 (MP-11) were immobilized on top of the MIP for AAP. This new approach combines substrate conversion and the specificity of target recognition by a MIP sub-layer. In this hierarchical architecture, the peroxide dependent conversion of AP takes place in the layer on top of a product-imprinted electropolymer. In the peroxide dependent oxidation of AP (but not of AAP) catalyzed by both HRP and MP-11, an intermediate was formed which generated a cathodic current at 0 V at the glassy carbon electrode. Uric acid gave no response since it is not electroactive at 0 V. The contribution of ascorbic acid was also completely suppressed by the action of the MIP layer and oxidation with peroxide. Therefore, the enzyme/MIP-sensor indicates only AP (also in the presence of AAP) and prevents interferences by ascorbic acid or uric acid.

4. Conclusions

Up to now the field of MIP-sensors—both for low and high molecular weight analytes—has been dominated by electrochemical transducers which indicate mostly a redox marker or an electroactive analyte. Electrochemical methods have been successfully applied in MIP-sensors for drugs or environmental analysis. On the other hand, QCM and SPR are appropriate means for the indication of macromolecules. The application of enzymes in combination with MIP-sensors has the potential to “upgrade” their analytical performance. Up to now, the degree of applying enzymes in the preparation of MIPs and in signal generation for analyte recognition is at different levels of development.

Enzyme-initiated polymerization is still at the initial stage of development. Whether it will compete with the established methods such as electropolymerization, chemical nanoparticle synthesis, and self-polymerization still remains to be seen. The need of immobilizing the enzyme is an additional working step.

The application of enzymes in the removal of the template is presently restricted to proteinase K for removing proteins. For oligomeric proteins, splitting into subunits by chaotropic reagents seems more straightforward. On the other hand, the application of nucleases for nucleic acids, lipases for lipids, and glycosidases for carbohydrates may come in the near future.

Enzyme labels are the key in highly sensitive luminescence-based MIP-binding assays and in electro-enzymatic recycling for signal amplification.

The enzymatic pretreatment of a target analyte can generate a product which is indicated at a lower electrode potential or a “non-target” substance that can be converted into a target analog. Integrated MIP/enzyme architectures allow for the elimination of interferences in the detection of drugs.