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Review

Zein Microparticles and Nanoparticles as Drug Delivery Systems

by
Iolanda De Marco
Department of Industrial Engineering, University of Salerno, Via Giovanni Paolo II, 132, 84084 Fisciano, Salerno, Italy
Polymers 2022, 14(11), 2172; https://doi.org/10.3390/polym14112172
Submission received: 9 May 2022 / Accepted: 24 May 2022 / Published: 27 May 2022
(This article belongs to the Special Issue Feature Papers in Polymer Applications)
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Abstract

:
Zein is a natural, biocompatible, and biodegradable polymer widely used in the pharmaceutical, biomedical, and packaging fields because of its low water vapor permeability, antibacterial activity, and hydrophobicity. It is a vegetal protein extracted from renewable resources (it is the major storage protein from corn). There has been growing attention to producing zein-based drug delivery systems in the recent years. Being a hydrophobic biopolymer, it is used in the controlled and targeted delivery of active principles. This review examines the present-day landscape of zein-based microparticles and nanoparticles, focusing on the different techniques used to obtain particles, the optimization of process parameters, advantages, disadvantages, and final applications.

1. Introduction

Zein is the major storage protein of corn first identified in the nineteenth century. It constitutes 44–79% of the endosperm protein depending on the variety of corn and the technique used for its extraction [1]. Being a natural material, it can be easily extracted from corn and is extensively available in nature [2]. Zein belongs to the category of prolamins and, from the biological point of view, it is a mixture of four components (α, β, γ, and δ) with different peptide chains, molecular size, and solubility [3]. Without any doubt, α-zein is the most abundant constituent of the mixture, accounting for about 70–80% of the whole zein, followed by γ-zein, which constitutes 10–20% [4,5]. It is the main component of commercially available zein, which is available in two forms, yellow and white zein. The former contains a high concentration of xanthophyll pigments and has a purity of about 90%. In contrast, white zein is obtained by decolorization of the yellow protein, has a negligible amount of xanthophylls, and has a purity higher than 96% [6]. Zein is a hydrophobic protein: it is poorly soluble in water alone and is soluble in aqueous ethanol, aqueous acetone, and some organic solvents [7].
The hydrophobicity, biodegradability, and biocompatibility of zein have been exploited in various fields, such as food coating [8] and packaging [9], adhesives [10], coatings [11], in the textile sector [12], in the biomedical sector and tissue engineering [13], and in the pharmaceutical industry [14]. Being a versatile polymer, zein is processed to obtain different shapes, such as particles [15], films [16], membranes [17], and scaffolds [18], which have been used for different applications. Zein films obtained by solvent casting, extrusion, or compression molding are generally used in the biomedical field, but because of the poor ability of zein to act as a water barrier, plasticizers or crosslinkers are necessary, or, in some cases, hybrid films are used incorporating other biopolymers [19,20]. Zein nanofibers produced by electrospinning are used to obtain scaffolds for tissue engineering [21] or food packaging applications [22].
Recently, zein has been utilized as a carrier for oral drug delivery systems [23] because it guarantees enhanced bioavailability, preparing sustained-release dosage forms, and targeting/protecting drugs [24]. Different reviews have been published on this topic, generally focused on the different morphologies obtained [13,24,25]; in some cases, the use of zein in combination with other substances has been deepened [7].
This review was focused on the attainment of zein in the form of micro and nanoparticles; unlike the previous reviews, the papers were classified according to the different processing techniques used to obtain the particles. The main limitation in the use of zein is that it is administered in the form of multiparticulate delivery systems associated with low drug loadings, high need of excipients, huge production costs, and use of advanced technologies [26].

2. Microparticles and Nanoparticles Production

Micronization processes are based on reducing the average diameter of a solid material. In the pharmaceutical sector, reducing dimensions down to the micro- or nanoscale is desirable since an increase in the bioavailability of the active ingredients is obtained in correspondence with a higher surface/volume ratio; in fact, active ingredients are often poorly soluble in water. The techniques used to obtain microparticles (MP) and nanoparticles (NP) can be classified into two main categories: top–down and bottom–up techniques [27,28]. In top–down processes, large particles are broken into smaller particles through milling, grinding, high-pressure homogenization, or other mechanochemical methods [29,30,31]. In bottom–up techniques, the active principle ingredient (API) is solubilized in an organic solvent and precipitates in the form of microparticles and nanoparticles by adding an antisolvent: the most commonly used techniques are the liquid antisolvent method, supercritical fluids processes, spray drying and emulsification, and solvent evaporation [32]. Bottom–up approaches are preferred in the case of thermolabile solutes, such as pharmaceuticals, because in top–down techniques, high energy input is involved, and a high amount of heat is generated, making the processing of thermolabile materials problematic. Almost all of the papers involving zein micronization consider bottom–up techniques.
In the last twenty years, research in the pharmaceutical sector has focused mainly on obtaining MPs and NPs of coprecipitates consisting of an API and a suitable polymeric carrier. In this way, it is possible to protect the active principle from light or oxidizing agents, mask unpleasant odors or tastes, and modulate the release of the active principle by suitably varying the type of carrier used and the polymer/drug ratio [33]. Zein alone or covered with other polymers was precipitated in some papers in the form of MPs and NPs [34,35,36,37,38,39]. The operating conditions were optimized to obtain the proper morphology, mean size, and particle size distribution. However, those papers were not analyzed in depth, considering that the present review paper was focused on the attainment of coprecipitated particles constituted by zein + API. This review is organized into subsections in which the published papers are classified as follows: (a) liquid antisolvent process; (b) supercritical antisolvent processes; (c) coacervation; (d) other techniques.

2.1. Liquid Antisolvent Process

The liquid antisolvent (LAS) process is the one mostly used to coprecipitate zein with an API in the form of microparticles and nanoparticles. In numerous cases, a co-carrier or a covering polymer has been used in combination with zein to confer the proper characteristics to the obtained material. The LAS process is based on the dissolution of zein and an API in a suitable organic solvent (generally aqueous ethanol), subsequently added to an aqueous phase containing a surfactant. The organic solvent is usually removed using rotary evaporation, stirring at high velocity, freeze-drying, or spray-drying. The main results obtained with the optimal operating conditions are schematized in Table 1.
From the results reported in Table 1, it is clear that zein + API powders are obtained almost in all cases in the form of nanoparticles using the LAS method. In some cases, particle size distributions are broad, but in other cases, monodisperse NPs are obtained. An exemplificative SEM image of monodisperse nanoparticles obtained using liquid antisolvent precipitation is reported in Figure 1. The particles are constituted by resveratrol, a polyphenol with antioxidant, antiaging, and anticancer properties, loaded into zein. The nanoparticles obtained are constituted by a homogeneous population of spherical particles with a smooth surface [95].
The dimensions of the particles are determined either with the aid of software based on image analysis or, more correctly, through dynamic light scattering (DLS). An exemplificative distribution obtained using a DLS particle size analyzer is reported in Figure 2.
The LAS technique has been used to process different materials with anti-inflammatory, chemotherapeutic, and antioxidant properties. In some cases, the in vitro cytotoxicity of the processed NPs against cancer cells was evaluated with encouraging results [44,46,62,68,70,85,93,99,102]. Moreover, in vivo studies on rats [74,92,95] or on human volunteers [97] were performed in some cases. When a comparative investigation of different carriers was attempted, zein showed a greater ability to retain the active compound effectively. Indeed, Gagliardi et al. [99] coprecipitated rutin, a polyphenolic bioflavonoid characterized by peculiar antioxidant properties, using poly(lactic-co-glycolic acid) (PLGA) or zein as the carrier. They observed that PLGA nanoparticles showed a poorer ability to retain rutin with respect to zein nanosystems.
Other authors compared the performance in terms of drug release of differently obtained systems based on the use of zein. Indeed, Chuacharoen and Sabliov [69] compared zein NPs covalently linked to folic acid (FA) (through the reaction between the carboxyl group of FA and the primary amino group of zein) and zein NPs with physically entrapped FA. In the former case, the particles were able to sustain the release of the active principle and target cancer cells overexpressing folate-binding receptors. In contrast, in the latter case, zein NPs controlled the release of the bioactive substance without targeting cancer cells. The proposed release mechanisms are sketched in Figure 3.
Contado et al. [98] coated resveratrol-loaded zein–pectin nanoparticles with Eudragit S100 to avoid the degradation of the dissolved drug in the gastrointestinal tract; they obtained nanoparticles with a mean diameter (MD) of 250 nm with targeted delivery in the colon tract. Indeed, it is well-known that Eudragit polymers are pH-sensitive polymers and, therefore, a specific Eudragit can be chosen depending on the type of desired drug release [103].
The main drawback of the LAS process is the presence of a high amount of ethanol; this can limit the use of the LAS technique because of the high costs related to the removal of the solvent itself and the residual solvent which can be contained in the precipitated powders.

2.2. Supercritical Antisolvent Process

An innovative process that has been used to coprecipitate a carrier with active principles is supercritical antisolvent precipitation (SAS) [104,105]. In this process, a liquid antisolvent is substituted with carbon dioxide in supercritical conditions. Therefore, this process is based on two prerequisites:
-
the carrier (zein) and the drug have to be soluble in an organic solvent but insoluble in the mixture formed by this organic solvent and supercritical carbon dioxide (scCO2);
-
the organic solvent and scCO2 have to be miscible under the process conditions.
Concerning the liquid antisolvent process, in the SAS process, the peculiarities of scCO2 can be exploited [106]. As a consequence, the size of the obtained particles can be easily controlled at the micro- and nanoscale by varying the process parameters, such as pressure, temperature, total concentration of the liquid solution, and ratio between the zein and the drug; moreover, complex post-process operations to separate the solvent and the antisolvent are not necessary, considering that in correspondence of the ambient conditions of temperature and pressure carbon dioxide is in the gaseous state whereas the organic solvent is a liquid. It was previously demonstrated that the use of different carriers in the SAS process leads to different drug releases: hydrophilic polymers such as polyvinylpyrrolidone can be used to obtain an increase in the drug dissolution rate, whereas hydrophobic carriers, such as zein, are the right choice to obtain a prolonged release of the active principle [107].
In Figure 4, a typical SAS plant is sketched. It comprises a carbon dioxide tank, a liquid solution burette, two pumps (one for CO2 and one for the liquid solution), a precipitation vessel, and a separator. The precipitation vessel is the heart of the plant and is equipped with an injector mounted in the top part of the chamber and a filter at the bottom from which the particles can be recovered after depressurization.
In Table 2, a list of the active ingredients coprecipitated with zein using the SAS process and the operating conditions chosen by the different research groups, and the main results obtained are reported.
It can be noted that using the SAS process, zein, in general, precipitates in the form of microparticles rather than nanoparticles and that the organic solvents most frequently used are DMSO or aqueous ethanol. The pressure ranges from 8.0 to 16.0 MPa, the temperature—from 30 to 55 °C. The zein/API weight ratio can vary in a wide range, but typically ratios in the range of 5:1–20:1 are preferred by different authors. The selected active principles belong to different categories, such as vitamins [109,113], antibiotics [108], anti-inflammatory drugs [111], anticancer drugs [112], or antihistamine drugs [110]. When the dissolution rate of the active principle coprecipitated with zein was compared with the dissolution rate of the pure API, a clear effect of prolonging the release was observed. For example, in the case of amoxicillin [108], complete API dissolution was achieved in almost 3 days and, therefore, the formulation can be used for “long-term antibiotic therapy”. In the case of 10-hydroxycamptothecin (HCPT) nanocrystals coprecipitated with zein microparticles [112], there was an initial burst corresponding to the fast release of the 50% of the drug in the first 10 h (attributed to the immediate dissolution and release of the HCPT located near the surface of the particles), followed by slow dissolution of the API corresponding to the release of the 70% of the drug in 82 h (because of the drug entrapped into the zein microspheres). A bimodal release was also observed in the case of antihistamines [110]: an immediate release of a small amount of the drug (22%) useful to rapidly relieve the symptoms associated with allergy, followed by a prolonged release of the remaining drug (that was completely dissolved in 36 h), which reduces the number of administrations throughout the day.
The SAS process has also been used to combine zein with other substances to deliver active principles. For example, Liu et al. [116] prepared nanospheres constituted by zein decorated with folic acid to obtain targeted delivery of HCPT. Indeed, HCPT is a promising natural anticancer ingredient characterized by poor aqueous solubility and in vitro and in vivo instability. The authors added folic acid to obtain a sustainable and targeted delivery system, enhancing the intracellular uptake of HCPT within cancerous cells. Compared to zein nanoparticles, folic acid/zein nanoparticles were smaller (in the range of 350–820 nm) and had a higher stability; moreover, folic acid/zein conjugates have the potential to selectively target tumor cells, with an associated reduction in nonspecific toxicity in the normal cells.
Palazzo et al. [117] used a supercritical-based process named supercritical assisted injection in a liquid antisolvent (SAILA) to entrap luteolin in zein microparticles. The process is based on the continuous injection of an expanded liquid constituted by an organic solvent, zein, API, and scCO2 in an aqueous solution, which has the role of the antisolvent. Therefore, unlike the SAS process in which scCO2 is the antisolvent, in the SAILA process, scCO2 is a co-solute. The authors identified the best operating conditions at a pressure of 10.0 MPa, a temperature of 40 °C, and a zein/luteolin ratio of 20:1. In correspondence with these conditions, they obtained microparticles with an MD of 1.20 μm and an entrapment efficiency of 82%.
The main advantage of the techniques based on the use of scCO2 lies in controlling the size of the particles as the operating conditions vary. In general, the particle size increases with increasing concentration of the liquid solution and decreasing pressure. Another significant advantage lies in the absence or presence of traces below the permitted limits of the solvent residue in the powders. On the other hand, the investment costs for the construction of plants and the operating costs of the processes themselves are higher than those of the LAS process due to high operating pressures.

2.3. Coacervation

The coacervation process involves no harsh solvents or high temperatures. The process consists of the separation of solutions into colloidal systems with two liquid phases: one, called coacervate, is rich in polymer and another phase is without the polymer. Coacervation can be simple when it involves the use of a single polymer or complex when two natural biopolymers of opposite charges are involved.
Simple coacervation has been used to prepare zein microspheres conjugated with different drugs, such as heparin [118], gitoxin [119], chemotherapeutic agents [120], and antigens for the preparation of vaccines [121,122] or DNA [123]. For example, Wang et al. [118] prepared a drug-eluting coating film containing zein + heparin microspheres with slow API release; indeed, about 55% of the entrapped heparin was released after 20 days. The film constituted by microparticles showed adequate anticoagulation and improved hemocompatibility. Susuki et al. [120] conjugated zein microspheres with some antitumor drugs, such as mitomycin C, daunomycin hydrochloride, and peplomycin sulfate, obtaining sustained API release systems to be used in selective cancer chemotherapy by oral or intratumoral administration. Regier et al. [123] prepared zein/DNA nanoparticles with an MD ranging from 158 to 397 nm depending on the zein/DNA ratio. The authors demonstrated a sustained plasmid release for at least 7 days, with a minimal initial burst. Zein/DNA nanospheres showed robust biocompatibility. They can be fine-tuned for specific applications including oral gene delivery, intramuscular delivery, and in the fabrication of tissue engineering scaffolds.
Complex coacervation has been used, for example, to prepare zein and chitosan coacervates, considering the zein/chitosan ratio, solid/liquid ratio, and pH. Indeed, Li et al. [123] studied the morphology and encapsulation efficiency of curcumin in the correspondence of different coacervation conditions. The in vitro release study showed that the stronger the zein–chitosan interaction was, the less the amount of curcumin released from the nanoparticles was. The API at the optimized operating conditions has a slight burst effect followed by a slow release.
The main advantages of coacervation are the rapidity of the process and the absence of solvents. In contrast, the drawbacks are the potential toxicity of the crosslinkers and the difficulty of controlling the coagulation step.

2.4. Other Techniques

Zein has also been processed using other techniques. In the emulsification and solvent evaporation method, an oily phase constituted by zein + API + organic solvent is emulsified into an aqueous phase in which a surfactant is dissolved. The system is continuously stirred to reduce the droplet size that forms the emulsion. Then, the organic solvent is evaporated under vacuum, and microparticles and nanoparticles precipitate in the second step. In Figure 5, a schematic representation of the process is reported.
For example, aceclofenac sodium, a nonsteroidal anti-inflammatory drug used extensively in treating rheumatoid arthritis and osteoarthritis, was processed with this technique [124]. The disperse phase was prepared by dissolving the drug and zein in 90% alcohol. This solution was added to the continuous phase (sesame oil) containing 0.5% Span 80 as an emulsifying agent. MPs with an MD in the range of 136–174 μm were obtained; the EE varied from 11.6 to 26.1% depending on the zein/drug ratio. In vitro release studies were attempted simulating gastric and intestinal fluids: a sustained release up to 72 h was detected. Biocompatibility of the zein microspheres was evaluated through in vitro cytotoxicity studies using fibroblast cells from the explant tissue. Karthikeyan et al. [125] used the same method to prepare zein microspheres charged with aceclofenac, metformin, and promethazine. The three active principles were chosen as examples of hydrophobic, hydrophilic, and amphiphilic drugs. The average particle size of the different zein/API microspheres was found to be 68–136 μm depending on the drug. The EE was around 20–25% depending on the zein/API ratio. The higher the ratio, the higher the EE.
A novel approach proposed by some authors is the preparation of zein microstructures by electrospinning and spray-drying (SD). For example, Coelho et al. [126] incorporated vitamin B12, the most chemically complex and the largest molecule among all the vitamins, into zein. The microparticles obtained by electrospinning had a size of around 3 μm and an EE of 91%. In contrast, wrinkled coprecipitated microparticles were obtained by SD with an average size of 6.4 μm and an EE of 95%. In vitro release tests revealed that a controlled release profile characterized the API and that vitamin B12-loaded zein microstructures produced by electrospinning have a slower release profile than the structures obtained by spray-drying. Mahalakshmi et al. [127] encapsulated β-carotene in zein at the microlevel using SD (with an MD in the range of 1.4–2.5 μm) and at the nanolevel using electrospraying (with an MD of 600–900 nm). Electrospraying proved to have higher encapsulation efficacy than SD. In vitro simulated gastrointestinal stability studies showed that the release of encapsulated β-carotene from NPs is faster than from MPs due to the larger surface area interacting with the release medium. SD was also used by Sousa et al. [128] to develop microspheres of PLGA and zein for amoxicillin and indomethacin delivery. In the case of amoxicillin, they obtained MPs with a mean diameter in the range of 9.4–38.3 μm depending on the PLGA/zein ratio with an EE up to 51%; in the case of indomethacin, the mean diameter varied in the range of 5.6–38.5 μm, and the EE was higher (up to 99%). In vitro release studies revealed a sustained-release pattern for all the formulations. De Sousa et al. [129] obtained tetracycline-loaded microparticles made of PLGA and zein using SD for teeth preservation therapy (chronic periodontitis). They obtained a product with a different EE depending on the PLGA/zein ratio. In vitro drug release studies showed a sustained release of tetracycline over 700 h in water (30 days), which is a period that would guarantee the treatment of a long course of periodontitis. The antimicrobial activity against Staphylococcus aureus was also evaluated.
Nanoprecipitation was successfully used by de Souza Tavares et al. [130] who nanoencapsulated ellagic acid, a compound with antioxidant and antimicrobial activities, into zein nanoparticles. They obtained spherical, non-aggregated, smooth-surface particles under 370 nm in diameter with relevant inhibitory and bactericide activity against S. aureus and P. aeruginosa. The obtained system can represent a suitable alternative to prevent and treat infectious attributed to Gram-positive and Gram-negative bacteria; moreover, it was demonstrated that the antioxidant effect was preserved for 24 h, such as required in skin repairing and topical treatments. Weissmueller et al. [131] used a flash nanoprecipitation process to encapsulate some APIs, such as vitamin E acetate and anticholera quorum-sensing modulator CAI-1 ((S)-3-hydroxytridecan-4-one). They obtained particles with a diameter less than 100 nm with high loading for both active principles. The stability of the obtained particles in the simulated intestinal fluid was demonstrated for 24 h. Zein nanoparticles incorporated with digoxin, a drug used to treat heart failure, were obtained by nanoprecipitation and then charged in an alginate film to prepare a buccal drug delivery system [132]. Digoxin was successfully encapsulated into zein nanoparticles with an EE of 91% and a mean size of 87 nm. It was also demonstrated that the mucoadhesive film incorporated with zein + API nanoparticles presented a controlled swelling profile and mechanical properties compatible with the application as a drug delivery system through the buccal mucosa.
Another process to reduce the use of organic solvents is acidification of a strong alkaline solution containing zein and an API, as proposed by Yuan et al. [133], who prepared pH-driven zein/tea saponin composite NPs containing curcumin. The process is based on the principle that the solubility of dissolved zein + API decreases during the acidification process and forms a sphere spontaneously to avoid the polar environment. The obtained spherical NP had an EE equal to 84% and high bioaccessibility with respect to free curcumin. Sabra et al. [134] synthesized amphiphilic protein copolymers via a carbodiimide coupling reaction for the tumor-targeted delivery of rapamycin and wogonin, two anticancer drugs. The nanoplatform was composed of a hydrophobic zein core to encapsulate drugs with high EE, a hydrophilic lactoferrin corona to enhance tumor targeting and prolong systemic circulation of nanocarriers, and glutaraldehyde crosslinking to reduce the particle size and improve micellar stability. The particle size of the micelles was around 260–290 nm and the EE was higher in the case of wogonin than for rapamycin. In vitro release profiles revealed that wogonin release from micelles was biphasic, characterized by initial fast release of about 64% of the drug during the first 6 h followed by the second phase of very slow release with about 67.59% of WOG released after 24 h. On the contrary, rapamycin showed a very slow release (<20% drug release after 72 h) without a considerable initial burst effect. Moreover, this combined nanodelivery system maximized synergistic cytotoxicity of the two drugs in terms of tumor inhibition in MCF-7 breast cancer cells.
In some cases, zein was not used as the carrier coprecipitated with the active principle but as the coating material. For example, Vozza et al. [135,136] used ionotropic gelation to encapsulate selenoamino acids (selenomethionine, methylselenocysteine, and selenocysteine) with antioxidant and anticancer properties into chitosan nanoparticles; the NPs were, then, coated with zein. At the best operating conditions in terms of the chitosan/zein ratio, they obtained particles with an MD of 271 nm and an encapsulation efficiency (EE) of 81% in the case of methylselenocysteine, particles with an MD of 377 nm in the case of selenomethionine and an EE of 80%, whereas in the case of selenocysteine, the MD was 262 nm and the EE was 79%. The analyses of the particles showed no cytotoxicity in Caco-2 cell lines and a sustained release of the APIs. Farris et al. [137] prepared chitosan/zein nano-in-microparticles constituted by a core of chitosan/DNA nanoparticles prepared by ionic gelation and further encapsulated in zein microparticles obtained using a water-in-oil emulsion. Well-defined micrometric particles were obtained, as reported in the FESEM image in Figure 6. Analyses such as DNA release profiles, site-specific degradation of the outer zein matrix, and in vivo transfection demonstrate that the formulated particles can improve oral gene delivery through enhanced protection and controlled release of the DNA cargo.

3. Conclusions

This review focused on the use of zein particles in the pharmaceutical field. Zein is a versatile polymer, which can be used alone, in blends with other polymers, and in shell–core systems constituting both the shell or the core polymer to obtain sustained-release drug delivery systems. Depending on the process and the operating conditions, zein is precipitated in the form of microparticles or nanoparticles. The liquid antisolvent process generally generates powders in the nanometric range, whereas supercritical antisolvent precipitation gives microparticles. The traditional and largely employed LAS method has the advantage of simplicity and low costs. Conversely, the SAS method is characterized by lower amounts of organic solvents and high costs; for this reason, it has been prevalently applied only at a laboratory scale. Other processes, such as coacervation, emulsification, and solvent evaporation, or electrospinning, have also been used to obtain sustained-release powders.

Funding

This research received no external funding.

Informed Consent Statement

Not applicable.

Data Availability Statement

Not applicable.

Conflicts of Interest

The author declares no conflict of interest.

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Polymers 14 02172 g001 550
Figure 1. Nanoparticles of zein/resveratrol. Adapted with permission from [95]. Copyright 2015 American Chemical Society.
Figure 1. Nanoparticles of zein/resveratrol. Adapted with permission from [95]. Copyright 2015 American Chemical Society.
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Figure 2. Particle size distribution of zein and zein ethanol-soluble polysaccharide NPs measured by DLS. Adapted with permission from [56]. Copyright (2022) Elsevier.
Figure 2. Particle size distribution of zein and zein ethanol-soluble polysaccharide NPs measured by DLS. Adapted with permission from [56]. Copyright (2022) Elsevier.
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Figure 3. Release mechanisms of FA from NPs: covalently linked (A) and physically entrapped (B). Reprinted with permission from [69]. Copyright 2017 Springer.
Figure 3. Release mechanisms of FA from NPs: covalently linked (A) and physically entrapped (B). Reprinted with permission from [69]. Copyright 2017 Springer.
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Figure 4. Sketch of a typical supercritical antisolvent precipitation plant.
Figure 4. Sketch of a typical supercritical antisolvent precipitation plant.
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Figure 5. Schematic representation of emulsification followed by solvent evaporation.
Figure 5. Schematic representation of emulsification followed by solvent evaporation.
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Figure 6. FESEM image of chitosan/zein nano-in-microparticles prepared by ionic gelation. Reprinted with permission from [137]. Copyright (2017) Elsevier.
Figure 6. FESEM image of chitosan/zein nano-in-microparticles prepared by ionic gelation. Reprinted with permission from [137]. Copyright (2017) Elsevier.
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Table
Table 1. Zein-based particles obtained using the liquid antisolvent process. AS/S, antisolvent/solvent; ATRA, all-trans-retinoic acid; β-CD, beta-cyclodextrin; Bor, bortezomib; BSA, bovine serum albumin; c, concentration in the liquid solution; C-28, human chondrocyte cells; CA, caffeic acid; Caco-2, human colon carcinoma cells; CS, chondroitin sulfate; CSA, carboxymethylated short-chain amylose; DOX, doxorubicin; DPPH, 2,2-diphenyl-1-picrylhydrazyl; DU145, prostate cancer cells; EC, ethyl cellulose; EE, encapsulation efficiency; EGCG, epigallocatechin gallate; ESP, ethanol-soluble polysaccharide; EtOH, ethanol; FA, folic acid; FD, freeze-drying; GA, gum arabic; GI, gastrointestinal; GLI, glibenclamide; Glim, glimepiride; GNA, gambogenic acid; GT, poly(anhydride)-thiamine conjugate; HA, hydroxyapatite; HAc, hyaluronic acid; HACAT, immortalized human keratinocyte cells; HeLa, highly stabilized immortalized tumor cells; HepG2, human liver cancer cells; HP-β-CD, 2-hydroxypropyl-beta-cyclodextrin; HT29, human colorectal adenocarcinoma cells; HT29-MTX, human colon cancer cells; Hya, hyaluronan; Indo, indomethacin; K562, chronic myelogenous leukemia cells; mPEG, methoxy poly(ethylene glycol); MCF-7, human breast cancer cells; MD, mean diameter; MP, microparticles; MW, molecular weight; NCTC2544, human keratinocyte cells; Nic, niclosamide; NCI/ADR-RES, ovarian tumor cells; NP, nanoparticles; PC3, prostate cancer cells; PDA, polydopamine; PEG, poly(ethylene glycol) 2000; PGA, propylene glycol alginate; PL, polydopamine–lecithin; PNS, Panax notoginseng saponins; PSA, polysialic acid; PTS, pterostilbene; Que, quercetagetin; Res, resveratrol; SC, sodium caseinate; SD, spray-drying; SGF, simulated gastric fluid; SIF, simulated intestinal fluid; SR, sustained release; Suc, succinic anhydride; SW480, colon cancer cells; T, temperature; Toc, tocopherol; TS, tea saponin; Vor, vorinostat; XG, xanthan gum; 4T1, mammary carcinoma cells; A549, human lung carcinoma cells.
Table 1. Zein-based particles obtained using the liquid antisolvent process. AS/S, antisolvent/solvent; ATRA, all-trans-retinoic acid; β-CD, beta-cyclodextrin; Bor, bortezomib; BSA, bovine serum albumin; c, concentration in the liquid solution; C-28, human chondrocyte cells; CA, caffeic acid; Caco-2, human colon carcinoma cells; CS, chondroitin sulfate; CSA, carboxymethylated short-chain amylose; DOX, doxorubicin; DPPH, 2,2-diphenyl-1-picrylhydrazyl; DU145, prostate cancer cells; EC, ethyl cellulose; EE, encapsulation efficiency; EGCG, epigallocatechin gallate; ESP, ethanol-soluble polysaccharide; EtOH, ethanol; FA, folic acid; FD, freeze-drying; GA, gum arabic; GI, gastrointestinal; GLI, glibenclamide; Glim, glimepiride; GNA, gambogenic acid; GT, poly(anhydride)-thiamine conjugate; HA, hydroxyapatite; HAc, hyaluronic acid; HACAT, immortalized human keratinocyte cells; HeLa, highly stabilized immortalized tumor cells; HepG2, human liver cancer cells; HP-β-CD, 2-hydroxypropyl-beta-cyclodextrin; HT29, human colorectal adenocarcinoma cells; HT29-MTX, human colon cancer cells; Hya, hyaluronan; Indo, indomethacin; K562, chronic myelogenous leukemia cells; mPEG, methoxy poly(ethylene glycol); MCF-7, human breast cancer cells; MD, mean diameter; MP, microparticles; MW, molecular weight; NCTC2544, human keratinocyte cells; Nic, niclosamide; NCI/ADR-RES, ovarian tumor cells; NP, nanoparticles; PC3, prostate cancer cells; PDA, polydopamine; PEG, poly(ethylene glycol) 2000; PGA, propylene glycol alginate; PL, polydopamine–lecithin; PNS, Panax notoginseng saponins; PSA, polysialic acid; PTS, pterostilbene; Que, quercetagetin; Res, resveratrol; SC, sodium caseinate; SD, spray-drying; SGF, simulated gastric fluid; SIF, simulated intestinal fluid; SR, sustained release; Suc, succinic anhydride; SW480, colon cancer cells; T, temperature; Toc, tocopherol; TS, tea saponin; Vor, vorinostat; XG, xanthan gum; 4T1, mammary carcinoma cells; A549, human lung carcinoma cells.
Active
Principle		Co-CarrierOrganic Solvent
(v/v)		Zein/API
(w/w)		Solvent RemovalResultsReference
5-fluorouracil–Aqueous EtOH
75%		From 2:1
to 16:1		Stirring + FDNPs with MD = 115 nm; EE up to 61%; burst release in the first 15 min + slow release for 24 h[40]
ArtemetherSCAqueous EtOH
50–90%		From 2.5:1
to 20:1		Stirring or rotavapor for 1–5 hNPs with MD = 142–201 nm depending on the c and zein/API ratio; EE up to 62%; burst release in the first 30 min + SR for 1.5 h; intravenous administration in rats revealed an extension of the API’s mean residence time[41]
Atorvastatin–Aqueous EtOH
80%		From 1:1
to 10:1		Stirring at 2000 rpm for 3 h + FD for 72 hNPs with MD = 223 nm at a low zein/API ratio; MPs with MD = 1.1 μm at a high zein/API ratio; EE up to 67%; dissolution profile with a burst in the first 4 h + a SR[42]
ATRA–Aqueous EtOH
66%		20:1Stirring at 600 rpm for 12 hNPs with MD = 103–401 nm depending on the c and kind of surfactant; EE up to 14%[43]
ATRAPhospholipidsAqueous EtOH
70%		From 5:1
to 20:1		Homogenization at 24,000 rpm for 2 min + stirring at 600 rpm for 12 h NPs with MD = 80–200 nm
depending on the zein/API ratio; EE up to 60%; evaluation of in vitro cytotoxicity in A549 and CaCo2 cells		[44]
CA + FAChitosanAqueous EtOH
70%		 Stirring + SD (inlet temperature of 100 °C)NPs with MD = 172–254 nm depending on the CA amount, FA amount, chitosan/zein ratio; EE up to 64% for CA and 84% for FA; chitosan forms complexes with FA, whereas CA is encapsulated in the hollow core[45]
CarvacrolLecithinAqueous EtOH
80%		 Stirring at 500 rpm overnightNPs with MD = 221–312 nm depending on the zein/API ratio; EE = 78%; 9% of the API released in 2 h (SGF conditions), up to 78% of the API (SIF conditions)—in 24 h; cytotoxicity against SW480 cells[46]
Coumarin SCAqueous EtOH
80%		50:1Stirring at 1200 rpm for 3 hNPs with MD = 165 nm at a high AS/S mixing rate and low c; MPs with MD = 1.2 μm at a low AS/S mixing rate and high c; EE up to 90%; dissolution profile with a burst in the first 30 min + slow release for 5 h[36]
Curcumin–Aqueous EtOH
80%		From 1:1
to 100:1		Stirring for 12 hNPs with MD = 102 nm; EE up to 94%; dissolution with a burst + SR for 8 h; excellent cellular uptake
ability by C6 glioma cells and penetration ability into 3D tumor spheroids		[47]
CurcuminTannic acidAqueous EtOH
70%		From 5:1
to 100:1		StirringNPs with MD = 86–114 nm depending on the c and zein/API ratio; EE up to 98%; controlled release in simulated GI conditions[48]
Curcumin–Aqueous EtOH
75%		10:1Stirring at 500 rpm for 3 hNPs with MD = 43 nm; EE = 89%; evaluation of the antioxidant activity[49]
CurcuminChitosanAqueous EtOH
75%		 StirringNPs with MD = 66–170 nm depending on the zein/curcumin ratio; EE up to 95%; evaluation of stability and DPPH assays[50]
CurcuminmPEGAqueous EtOH
90%		50:1Stirring at 50 rpm + dialyzing + FDNPs with MD = 124 nm; EE = 95%; SR up to 24 h; high
cell uptake in drug-resistant
NCI/ADR-RES cells		[51]
CurcuminGAAqueous EtOH
80%		10:1Stirring + rotavapor at 35 °CNPs with an MP lower than 250 nm; EE = 96%; evaluation of the stability of the system under different environmental conditions[52]
Curcuminβ-CDAqueous EtOH
80%		20:1RotavaporMucoadhesive NPs with MD = 140 nm for the API’s buccal delivery; SR within 10 days[53]
CurcuminPectinAqueous EtOH
85%		2.5:1Stirring + rotavaporNPs with MD = 230 nm; EE = 90%;
10% of the API released in 2 h (SGF conditions), up to 51% of the API (SIF conditions)—in 10 h		[54]
Curcumin–Aqueous EtOH
80%		20:1Stirring at 1200 rpm + rotavaporMonomodal NPs with MD = 120 nm; high loading capacity and good chemical stability[55]
CurcuminESPAqueous EtOH
85%		From 4:1
to 20:1		Stirring at 800 rpm for 2 h + rotavapor at 45 °C for 35 minNPs with MD = 253–266 nm depending on the zein/API ratio; EE up to 89%; initial burst release with 50% of the API detected after 2 h SGF digestion; 77% of the API detected after 3 h SIF digestion[56]
CurcuminHyaAqueous EtOH
70%		20:1Stirring at 600 rpm for 20 min + rotavapor at 40 °CNPs with MD = 140 nm; EE = 95%; controlled release in simulated gastroinstestinal digestion [57]
Curcumin–Aqueous EtOH
85%		–Stirring at 100 rpm for 30 min + rotavaporNPs with MD = 380–430 nm; EE up to 98%; 40% of the API released in 1.5 h (SGF conditions), more than 95% of the API (SIF conditions)—in 4 h[58]
CurcuminECAqueous EtOH
80%		From 16:1
to 80:1		Stirring at 500 rpm for 30 min + rotavapor at 45 °C for 10 minNPs with MD = 130–179 nm depending on the c, zein/EC, and zein/API ratios; EE up to 82%; pH-dependent release profile; cytotoxicity in HT29 cells[59]
CurcuminXGAqueous EtOH
80%		–Stirring at 600 rpm + rotavapor at 40 °C and −0.1 MPaNPs with MD = 179 nm; EE up to 92%; sustained API release in the GI tract for more than 6 h[60]
Curcumin + piperine HA + chitosanAqueous EtOH
70%		10:1 + 10:1Stirring at 600 rpm + rotavaporNPs with MD = 186 nm; EE = 90% for curcumin and 86% for piperine;
piperine was encapsulated in the polysaccharide shell, whereas curcumin was embedded into the
hydrophobic cationic zein core		[61]
DocetaxelCSAqueous EtOH
75%		From 3:1
to 5:1		Stirring
+ dialysis		NPs with MD = 158 nm; EE = 64%; SR in 48–72 h; enhanced tumor accumulation of the NPs was confirmed in PC3 xenograft mice[62]
DOX–Aqueous EtOH
80%		10:1Stirring at 800 rpmNPs with MD = 120 nm; EE up to 89%; SR in 15 days[63]
DOXSCAqueous EtOH
80%		From 20:1
to 60:1		Nitrogen stream + lyophilization in the darkNPs with MD = 198–244 nm depending on the c and zein/API ratio; EE up to 90%; burst release for 6 h + SR in 100 h; absence of in vitro cytotoxicity in HeLa cells[64]
DOX
hydrochloride		–Aqueous EtOH
70%		3:1Stirring and freezing at −20 °C for 12 hNPs with MD = 150 nm; EE = 21%[65]
DOXHAAqueous EtOH
70%		3:1Stirring and freezing at −20 °C for 12 hNPs with MD = 207 nm; EE = 44%; pH-sensitive SR; in vitro experiments revealed a high cytotoxicity to 4T1; in vivo, decreased DOX cardiotoxicity and liver targeting[65]
EGCGChitosanAqueous EtOH
75%		From 14:1
to 72:1		Stirring at 600 rpm for 30 min + rotavaporNPs with MD = 155–240 nm depending on the c and zein/API ratio; EE up to 81%; release profile with an initial burst effect which occurred within one day, followed by SR over 10 days; significant DPPH scavenging activity [66]
Felodipine–Aqueous EtOHFrom 1.5:1 to 4:1Drying overnight under vacuum at 40 °CNPs with MD = 150–300 nm depending on the zein/API ratio; EE up to 87% [67]
Ferulic acidSC + lysineAqueous EtOH
87%		 Stirring for 2 h + centrifugation for 20 minNPs with MD = 199 nm; slow SR for days; in vitro cytotoxicity in Caco-2 and HT29-MTX cells[68]
Folic acid–Aqueous EtOH
70%		1.5:1Rotavapor for 45 minNPs with MD = 97 nm; burst release in the first 12 h + SR after 6 days[69]
Gallic acidPhospholipidAqueous EtOH
90%		 Stirring at 600 rpm for 1 h + homogenization at 75,000 rpmNPs with MD = 269–313 nm; EE up to 65%; fast release within the first 2 h + SR within 24 h; evaluation of the delivery to the activated hepatic stellate cells[70]
GLI–Aqueous EtOH
70%		From 2.5:1 to 50:1SD (inlet temperature of 90 °C)NPs with MD = 190 nm; EE = 43%; 5% of the API released in 2 h (SGF conditions), more than 90% of the API (SIF conditions)—in 12 h; in vivo studies using C. elegans show a 15% reduction in the fat content[71]
Glim–Aqueous EtOH
90%		From 1:3
to 2:1		Stirring at 2000 rpm for 3 h + rotavapor overnightMD in the range of 11–603 nm depending on the zein/API ratio, stabilizer type, and concentration; EE up to 63%; API release characterized by an initial burst effect + slow release[72]
GNAPDAAqueous EtOH
70%		3:1Stirring at 200 rpm for 2 h + FD at −80 °C for 48 hNPs with MD = 279–312 nm depending on the presence of PDA; EE up to 82%; SR in more than 72 h; in vitro experiments revealed enhanced cytotoxicity in HepG2; in vivo pharmacokinetic experiments demonstrated tumor-targeting drug delivery[73]
GNA–Aqueous EtOH
70%		 Stirring at 30 °C in a ventilated cupboardNPs with MD = 103 nm; EE = 76%; SR of the API in 36 h; in vivo pharmacokinetic experiments in rats showed an increased bioavailability and prolonged half-life; tissue distribution revealed liver-targeting properties[74]
HonokiolPSAAqueous EtOH
85%		10:1Stirring at 1000 rpm for 1 h + rotavaporNPs with MP = 107 nm; EE = 79%; SR up to 48 h; in vivo experiments in mice revealed enhanced tumor accumulation of the NPs in 4T1, resulting in desirable antitumor efficacy and favorable biosafety[75]
HyperosidePectinAqueous EtOH
85%		From 5:1
to 20:1		Stirring at 800 rpm for 2 h + centrifugationNPs with MD = 51–298 nm depending on the pectin/zein ratio; EE up to 94%; SR under simulated gastrointestinal conditions[76]
IndoSucAqueous EtOH
80%		From 1:2
to 5:1		Stirring for 15 min + centrifugation at 8000 rpm for 15 minNPs with MD = 112–364 nm depending on the zein/API ratio; EE up to 97%; pH-responsive SR; in vitro evaluation of cytotoxicity in HACAT cells[77]
InsulinCSAAqueous EtOH
70%		3:1Stirring at 600 rpmNPs with MD = 200 nm; EE = 90.5%; dissolution profile with a burst + SR for more than 6 h; in vitro evaluation of cytotoxicity in Caco-2 cells [78]
InsulinGTAqueous EtOH
55%		10:1SDNPs with MD = 222–327 nm depending on the GT/zein ratio; EE = 87%; 30% of the API released in 2 h (SGF conditions), up to 60% of the API (SIF conditions)—in 26 h; in vivo studies using C. elegans under high glucose conditions show a 22% reduction of fat storage in the body[79]
InsulinGT–PEGAqueous EtOH
55%		10:1SDNPs with MD = 248 nm; EE = 89%; 28% of the API released in 2 h (SGF conditions), up to 84% of the API (SIF conditions)—in 24 h; in vivo studies using C. elegans show a significant reduction in the glucose content and fat accumulated in the body[80]
Ivermectin–Aqueous EtOH
66%		From 2:1
to 20:1		StirringMPs with MD = 1 μm; EE up to 69%; SR in 9 days with a burst effect in the first 24 h[81]
Lovastatin–Aqueous EtOH
80%		1:1Stirring at 2000 rpm for 3 hNPs with MD = 67 nm; EE = 86%; antiproliferative activity against HepG2 cells[82]
Lutein–Aqueous EtOH
85%		25:1Stirring at 1000 rpm + rotavapor at 50 °CNPs with MD = 398 nm; EE = 85%; improved stability in SGF and SIF conditions[83]
NicBSAIsopropyl alcohol
70%		8:1Rotavapor for 10–15 min + FD at
−53 °C for 48 h		NPs with MD = 173 nm; stable NPs to be used as an injectable nanomedicine with an SR[84]
Paclitaxel–Aqueous EtOH
66%		From 7:1
to 20:1		Stirring at 600 rpm for 12 hNPs with MD = 265 nm; EE up to 40%; in vitro cytotoxicity in K562 and MCF-7 cells[85]
Paclitaxel–Aqueous EtOH
85%		From 8:1
to 12:1		Stirring at 500 rpm + rotavaporNPs with MD = 132–495 nm depending on the zein/API ratio; SR without serious bursts in 8 h[86]
PNSLecithinAqueous EtOH 80%From 1:4
to 1:1		Stirring + evaporation at room T for 3 hNPs with MD = 116–155 nm depending on the zein/API ratio; EE up to 43%; API protected from the degradation of acid and enzymes in the GI tract; good potential to penetrate the mucus layer and enter enterocytes[87]
PTSFucoidanAqueous EtOH 75%10:1Stirring 1 h + rotavaporNPs with MD = 74–139 nm depending on the zein/fucoidan ratio; EE up to 95%; 21% of the API released in 2 h (SGF conditions); fast release in 60 min of the SIF conditions; SR up to 46% in 6 h[88]
QueHAcAqueous EtOH
70%		20:1Stirring at 600 rpm + rotavaporNPs with MD = 226 nm; EE = 94%; controlled release of the API[89]
QueChitosanAqueous EtOH
70%		20:1Stirring at 600 rpm + rotavapor at 40 °CNPs with MD = 330–396 nm depending on the chitosan’s MW; EE up to 95%; delayed release with respect to free API under simulated gastrointestinal conditions[90]
QuePGAAqueous EtOH
70%		From 2.5:1 to 20:1Stirring + rotavapor at 45 °C for 35 minSub-MPs with MD = 700–900 nm depending on the zein/API ratio; EE up to 96%[91]
QuercetinHP-β-CDAqueous EtOH
60%		12:1SD (inlet temperature of 90 °C)NPs with MD = 294–358 depending on the amount of HP-β-CD; EE = 81%; 15% of the API released in 2 h (SGF conditions), up to 80% of the API (SIF conditions)—in 30 h; after oral administration in rats, high and sustained plasma levels for 30 h[92]
RapamycinLecithinAqueous EtOH
80%		 Evaporation at room T for 3 hNPs with MD = 190 nm; EE = 87%; 65% of the API released in 4 h + 22% SR within the remaining 20 h; enhanced uptake in Caco-2 cells[93]
ResPLAqueous EtOH
80%		2.5:1Stirring for 12 hNPs with MD = 123 nm; EE up to 88%; dissolution profile with a burst for 4 h + SR in 10 h[94]
Res–Aqueous EtOH
65%		6:1SD (inlet temperature of 90 °C)NPs with MD = 307 nm; EE = 82%; 20% of the API released in 2 h (SGF conditions), up to 60% of the API—6 h later (SIF conditions); sustained and prolonged release in 48 h; in vivo studies on rats revealed an increased bioavailability and diminished endotoxic symptoms[95]
Res–Aqueous EtOH
70%		From 6:1
to 18:1		Stirring for 3 h + centrifugation for 30–40 minNPs with MD = 141–187 nm; EE up to 93%; dissolution profile with a burst in 60 min + a plateau up to 24 h; cytotoxicity in Caco-2 and HT29-MTX cells[96]
Res–Aqueous EtOH
70%		6:1Stirring + SD (inlet temperature of 200 °C)NPs with MD = 331 nm; EE = 87%; good tolerability and quantifiable plasma levels of the API after administration to 16 volunteers [97]
ResPectinAqueous EtOH 88% Stirring at 500 rpm + rotavaporCoated NPs with the MD of 250 nm; the release is characterized by a burst effect (38%) in the first 20 min followed by slow release[98]
Rutin–Aqueous EtOH
66%		From 2.5:1 to 10:1Homogenization at 24,000 rpm for 1 min + stirring at 600 rpm for 12 hNPs with MD = 103–136 nm depending on the zein/API ratio; EE up to 88%; constant and prolonged release over time; increased protective effect on C-28 and NCTC2544 cells[99]
TocGAAqueous EtOH
83%		From 1:1
to 100:1		Stirring at 600 rpmNPs with MD = 159 nm; EE up to 91%; slow release of Toc in simulated gastrointestinal digestion[100]
TocChitosanAqueous EtOH 75%From 2.3:1 to 9:1Stirring at 600 rpm for 1 hNPs and MP with MD = 211–862 nm depending on the c and zein/API ratio; EE up to 88%; burst release for 1.5 h + SR in 6.5 h; better protection of the TOC release against GI conditions due to chitosan coating[101]
Vor + Bor–Aqueous EtOH
92%		 Stirring + dialysisNPs with MD = 150 nm; EE = 60% for each API; pH-dependent controlled release in 48 h; synergistic toxicity against PC3 and DU145 cells [102]
Table
Table 2. Zein-based particles obtained using the SAS process. AC, acetone; β-car, β-carotene; c, concentration in the liquid solution; δ-toc, δ-tocopherol; DCM, dichloromethane; DIC, diclofenac sodium; DMSO, dimethyl sulfoxide; DR, dissolution rate; EE, encapsulation efficiency; EtOH, ethanol; HCPT, 10-hydroxycamptothecin; MP, microparticles; NP, nanoparticles; P, operating pressure; Rib, riboflavin; T, operating temperature.
Table 2. Zein-based particles obtained using the SAS process. AC, acetone; β-car, β-carotene; c, concentration in the liquid solution; δ-toc, δ-tocopherol; DCM, dichloromethane; DIC, diclofenac sodium; DMSO, dimethyl sulfoxide; DR, dissolution rate; EE, encapsulation efficiency; EtOH, ethanol; HCPT, 10-hydroxycamptothecin; MP, microparticles; NP, nanoparticles; P, operating pressure; Rib, riboflavin; T, operating temperature.
Active PrincipleOrganic
Solvent		P
(MPa)		T
(°C)		c
(mg/mL)		Zein/Drug
(w/w)		ResultsReference
AmoxicillinDMSO9.040–5050From 20:1
to 30:1		MPs in the range of 0.26–0.85 μm; EE up to 99.8%; DR about 16 times slower than of the unprocessed API with a burst effect (33%)[108]
AmpicillinDMSO9.040–5050From 5:1
to 30:1		MPs in the range of 0.31–1.31 μm; EE up to 99.8%; DR about five times slower than of the unprocessed API with a burst effect (10%)[108]
β-carAqueous EtOH 94%16.040401:1MPs of 11.79 μm[109]
CetirizineDMSO9.040–5050From 5:1
to 20:1		MPs in the range of 2.75–8.77 μm; prolonged release (5–6 times longer than the of the unprocessed API) with a burst effect of 10–20%[110]
δ-tocAqueous EtOH 94%16.04070From 2:5
to 2:15		MPs in the range of 8.40–14.36 μm[109]
δ-toc + RibAqueous EtOH 94%16.04075–175From 2:5.5
to 2:15.5		MPs in the range of 8.71–16.67 μm[109]
δ-toc + Rib+ β-carAqueous EtOH 94%16.0402001:9MPs of 17.8 μm[109]
DICDMSO9.04030–50From 5:1
to 30:1		MPs in the range of 0.31–1.31 μm; delayed release of the API with a burst effect equal to 10% at the optimized operating conditions[111]
HCPTDMSO/EtOH w/w (1/0, ¼, 2/3; 3/2) 8.0–14.030–456–21From 5:1
to 20:1		MPs in the range of 0.81–2.99 μm; EE up to 96%; 50% HCPT released in the first 20 h + sustained release up to 92 h; evaluation of in vitro antitumor activity against cancerous cell lines[112]
KetotifenDMSO9.040–5050From 5:1
to 20:1		MPs in the range of 0.72–2.23 μm; prolonged release with a burst effect equal to 10% at the optimized temperature[110]
LuteinAC/DMSO
7/3 v/v		10.0–15.032–4510–20From 12:1
to 24:1		NPs in the range of 198–355 nm; EE up to 83%; controlled release without a burst effect[113]
LysozymeAqueous EtOH 90%10.040550:1MPs in the range of 1–50 μm; EE = 47%; sustained release[114]
MelatoninDCM/EtOH
7/5 v/v		8.0–16.035–5510.5–11From 10:1
to 20:1		NPs in the range of 69–354 nm; EE up to 80%; controlled release without a burst effect[115]
RibAqueous EtOH 94%16.04022.5–27.5From 2.6:1
to 8:1		MPs in the range of 11.24–14.21 μm[109]
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De Marco, I. Zein Microparticles and Nanoparticles as Drug Delivery Systems. Polymers 2022, 14, 2172. https://doi.org/10.3390/polym14112172

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De Marco I. Zein Microparticles and Nanoparticles as Drug Delivery Systems. Polymers. 2022; 14(11):2172. https://doi.org/10.3390/polym14112172

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De Marco, Iolanda. 2022. "Zein Microparticles and Nanoparticles as Drug Delivery Systems" Polymers 14, no. 11: 2172. https://doi.org/10.3390/polym14112172

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