Recent insights on nanomedicine for augmented infection control.

Antimicrobial agents have been widely investigated for protecting against microbial infections in modern health. Drug-related limitations, poor bioavailability, toxicity to mammalian cells, and frequent bacteria drug resistance are major challenges faced when exploited in nanomedicine forms. Specific attention has been paid to control nanomaterial-based infection against numerous challenging pathogens in addition to improved drug delivery, targeting, and pharmacokinetic (PK) profiles, and thus, efficient antimicrobials have been fabricated using diverse components (metals, metal oxides, synthetic and semisynthetic polymers, natural or biodegradable polymers, etc). The present review covers several nanocarriers delivered through various routes of administration, highlighting major findings to control microbial infection as compared to using the free drug. Results over the past decade support the consistent development of various nanomedicines capable of improving biological significance and therapeutic benefits against an array of microbial strains. Depending on the intended application of nanomedicine, infection control will be challenged by various factors such as weighing the risk-benefits in healthcare settings, nanomaterial-induced (eco)toxicological hazards, frequent development of antibiotic resistance, scarcity of in vivo toxicity data, and a poor understanding of microbial interactions with nanomedicine at the molecular level. This review summarizes well-established informative data for nanomaterials used for infection control and safety concerns of nanomedicines to healthcare sectors followed by the significance of a unique "safe-by-design" approach.

Introduction

Traditional antimicrobial (AM) agents have several challenges, such as frequent drug resistance, pre-formulation-related limitations, poor drug targeting, and poor drug release which may lead to mammalian cell toxicity or ineffectiveness at the site of action. This was highlighted in a recent Centers for Disease Control prediction where more people are predicted to die from antibiotic-resistant bacteria than all cancers combined by 2050.1 This subsequent global antibiotic disaster has led to a decline in the number of new AM agents and marketed products to kill bacteria further resulting in serious implications.1 There are two strategies for a potential solution: 1) development of new antibiotics that are costly, time consuming, and may never receive regulatory approval, or 2) repurpose existing effective antibiotics (or new nanomedicines without drugs) into new formulations that are more effective. Of course, the latter (if done appropriately) can accelerate translation to the clinic economically with a faster life-saving capability.1

A new field termed “pharmaceutical nanotechnology” repurposes existing antibiotics to attract researchers working with approved AM agents. Several efforts have been implemented for numerous drugs using novel therapeutic strategies. Broadly speaking, nanomedicines are composed of either polymers or lipids as the basic component of the nanocarrier systems. A major concern in this area is the need for new and efficient approaches to enhance drug therapy using existing AM agents or a potent new compound as a substitute for existing drugs. In general, low and high molecular weight AM agents face common physiological barriers inside the body when administered using these delivery systems. Characteristic features of these nanocarrier delivery systems make for optimal carriers for the delivery of AM agents. For example, nanostructures (nanostructured lipid carriers [NLCs]) can be created to have water loving surface properties which are advantageous for carrying drug molecules to the target site by the reticuloendothelial system in the tissues and organs leading to prolonged mean resident times for maximizing AM activity. Conversely, nanostructures can also be developed to have hydrophobic properties which would be useful for loading hydrophobic antibiotics, prolonging their release and creating an anti-adhesive-type antimicrobial coating (AMC) in the healthcare setting. Furthermore, the modification of surface chemistry of these nanocarriers can enable conjugation of molecules as targeting signals, taking advantage of their high surface-area-to-volume ratios.2,3 Finally, nanocarriers can enter biofilms and subsequently bacteria (or even clog bacterial membrane nanospores) more easily than micron particles for maximum microorganism killing. Nanotechnology, thus, has been proven beneficial in infection diagnosis and control due to site-specific delivery and modified drug performance (via conjugation, ligand binding, and carrier-dependent cell internalization).

With all of the promises mentioned above, it is obvious that the application of nanomaterials for infection control has been investigated for improved cellular uptake using nanoparticles (NPs). These nanomaterials can lead to higher drug accumulation in microbial cells to toxic levels and subsequently produce tandem effects.4 Solid lipid nanoparticles (SLNs), NLCs, liposomes, nanoemulsions, self-emulsifying drug delivery systems (SEDDS), and polymeric NPs have all been established to enhance AM efficacy.5 This review emphasizes the current advances and challenges of such nanostructures, understanding the design principles for the development of novel nanocarriers, the cellular interplay between the nanocarriers and cells, prevention of drug degradation, stability enhancement of the integrated drug molecules, and improvement in PK profiles and challenges of nanomaterials used in the healthcare sector, involving ecosystems.

Despite the profound application of nanomedicine as drug delivery carriers to improve PK and pharmacodynamic profiles, safety aspects are of prime concerns for humans and other living systems in diverse ecosystems. The present review also highlights the challenges (surface coating) arising from employing nanomaterials in healthcare units and their current design criteria (ie, “safe by design”).

Nanomedicines as effective AM drug delivery systems

Approximately 33.3% of microbial infections are non-responsive to existing antibiotics generally prescribed to eradicate infections.6 Common challenges for formulation scientists is the frequent development of drug resistance against well-established antibiotics. Thus, the demand for newly developed antibiotics is increasing enormously. Presently, there is a serious demand to employ advanced approaches to improve their therapeutic effectiveness. Figure 1 illustrates this developmental progress involving several in vitro and in vivo assessments. Table 1 lists several nanocarrier formulations with basic components and their major advantages in medicine.

Figure 1

Schematic representation of the development of various nanostructures and in vitro and in vivo evaluation.

Abbreviations: DSC, differential scanning calorimeter; DLS, diffraction light scattering; ELS, electrophoretic light scattering; AFM, atomic force microscopy; XRD, X-ray diffraction; IVIVC, in vitro in vivo correlation; SLN, solid lipid nanoparticle; NLC, nanostructured lipid carrier; SNEDDS, self-nanoemulsifying drug delivery systems; SEM, scanning electron microscopy; TEM, transmission electron microscopy.

Table 1

Generally used nanomedicines for antimicrobial agents

Nanomedicines	Basic compositions	Main features	Advantages	Major route
Metal nanoparticles	Metals and metal oxide	• Nanorange carrier• Inherent antimicrobial activity such as Ag	Strong antimicrobial action	Oral11–13
Polymeric nanoparticles	Polymers (biodegradable, synthetic or semisynthetic) and stabilizers (hydrophilic or lipophilic depending on drug properties)	• Nanoscale carrier for improved absorption• Lymphatic mediated transport for enhanced bioavailability	Solubility improvement, enhanced oral and topical absorption, increased drug permeation across biological membranes, increased residence time in GIT, increased retention time at conjunctival membranes when bioadhesive polymer is used and sustained release of drug	Oral,47 topical, transdermal, nasal and ophthalmic
SLNs	Solid lipid(s) or blend of solid lipids (natural, semisynthetic, or synthetic lipid)	• Nanoformulation with more acceptability than polymeric NP• More drug loading and % EE than polymeric NP• Solid lipid are safe and biocompatible	Improved solubility, absorption, and BA due to solid lipid and lymphatic-mediated absorption Safer than polymeric NPs due to biocompatible carrier No free radical generation after metabolism	Oral, topical, transdermal, nasal and ophthalmic68–70
NLC	Combination of solid and liquid lipid	• More stable than SLNs• More loading and % EE• More imperfect matrix	Stable than SLN, less drug leaching ability on prolonged standing, more drug loading, and encapsulation efficiency	Oral, topical, transdermal, nasal and ophthalmic3,4,88
Nanoemulsion	Lipids, surfactants, and co-surfactants	• Thermodynamically stable• Nanocarrier based delivery• Stable and effective carrier• Biocompatible when lipid of GRAS category used	Improved solubility, drug loading, and absorption. Enhanced drug bioavailability and therapeutic potential due to the nanocarrier nature of formulation. Stable than microemulsion	Oral, topical, transdermal, nasal and ophthalmic86–89
SEDDS	Lipid, surfactant, and co-surfactants	• Nanoemulsion or microemulsion• Self-emulsification under mild agitation in GIT fluid• Higher drug loading and encapsulation efficiency• Thermodynamically stable and safe carrier	Improved solubility, drug loading, and % EE Improved oral absorption Biocompatible and stable carrier Economic and effective delivery system	Oral59–67
Liposome	Phospholipid (phosphatidylcholine), non-ionic or ionic surfactants, cholesterol	• Vesicular bilayer carrier• Capable to encapsulate both hydrophilic and lipophilic drugs• Higher drug loading and encapsulation efficiency than NP, SLN, NLC, and nanoemulsion• Physically unstable	Improved solubility, drug loading and % EE Enhanced permeation across the skin More compatible due to lipid and adhesive	Topical, transdermal, nasal and ophthalmic73–75
Elastic liposome	Phospholipid (phosphatidylcholine), non-ionic surfactants, edge activator, and ethanol (7% v/v)	• Vesicular bilayer carrier• Capable to encapsulate both hydrophilic and lipophilic drugs• Higher drug loading and encapsulation efficiency• Ultradeformable and squeezing ability due to absence of cholesterol• Stable than liposome	Improved solubility, drug loading, and % EE More enhanced permeation than liposome across the skin More compatible due to lipid and adhesive Cost effective due to absence of cholesterol	Topical, transdermal, nasal and ophthalmic83–86
Cubosome (liquid crystalline carrier)	Glyceryl monooleate, monoolein, phytantriol as lipid, and poloxamer as stabilizer	• Cubical vesicular carrier system• Capable to encapsulate both hydrophilic and lipophilic drugs• Higher drug loading and encapsulation efficiency• Stable to gastric fluid	Improved solubility, drug loading, and % EE Improved oral absorption Biocompatible and stable carrier Economic and effective delivery system	Oral, topical, transdermal, nasal and ophthalmic56,57
Micelle	Polymeric and surfactant-based micellar drug delivery	• Spherical micelle• Capable to encapsulate drug of both nature• Higher drug loading and encapsulation efficiency	Improved solubility, drug loading, and % EE Improved oral absorption Biocompatible and stable carrier Economic and effective delivery system	Oral, topical, transdermal, nasal and ophthalmic54,55

Abbreviations: SLN, solid lipid nanoparticles; NLC, nanostructured lipid carriers; SEDDS, self-emulsifying drug delivery systems; NP, nanoparticle; EE, entrapment efficiency; GIT, gastrointestinal tract; GRAS, generally regarded as safe.

Possible mechanisms of nanocarriers (or nanomedicine) as AM systems

Infectious diseases are a result of microbial infections. Understanding the chemical composition of the microbial cell wall, cellular physiology, and behavior is a prerequisite for developing an effective therapy using nanomedicine to identify a specific surfactant, lipid, drug, and/or polymer. NPs encapsulating noble metals have been recognized to exhibit potential AM activity.7 The materials employed for fabricating and designing NPs have several important parameters that affect AM efficacy, such as surface-to-volume ratios of the NPs wherein smaller ones have been reported to have the strongest bactericidal effect.8 Moreover, the mechanism of bactericidal activity is due to the association of a positive charge of the metal encapsulated in the NPs with the negatively charged surface of the microbial cell by virtue of the electrostatic attraction. Over the last two decades, many researchers have addressed the application of the excipients possessing innate AM activity acting synergistically with the drug for the treatment of bacterial, fungal, viral, and parasitic infections. Recently, the concept of synergistic activity of excipients with drugs has been implemented to formulate nanomedicine with innate AM action.4,9 A schematic representation of the mechanism of AM action of nanomedicine is illustrated in Figure 2 wherein possible mechanisms have been portrayed. These mechanisms are: (A) adherence of nanocarriers around the microbial cell owing to increased surface area and smaller size which thereby causes a maximum detrimental effect, (B) electrostatic attraction of cationic charges by the negatively charged bacterial surface or lipid-lipid internalization of nanoglobules within the bacterial membrane, (C) detergent-like action of lipids and surfactants to extract lipids of cytoplasmic membranes as reported, (D and E) creation of tiny pores in the membrane which then causes a loss of cytoplasmic content outside of the cell, (F) accumulation of lipids and surfactants to a toxic level for an enhanced detrimental effect, and (G) inhibition of P-gp efflux to produce increased residence of the absorbed drug or such excipients to produce a prolonged AM effect.10

Figure 2

Schematic illustration of the possible mechanisms involved in microbial killing using nanomedicines (nanocarriers) composed of lipids and surfactants. Possible mechanisms are: (A) lipid–lipid interactions, (B) cationic nanomedicine interactions with negatively charged bacterial surfaces, (C) detergency-like action, (D) cytoplasmic content oozing out through developed tiny pores, (E) micelles loaded with extracted cellular lipids, (F) accumulated excipients to toxic levels to produce detrimental effects, and (G) P-gp efflux pump inhibition by specific excipients (reported labrasol, tween 80) and drugs (ketoconazole).4,19,31,67

Metal and metal oxide NPs

Silver NPs (Ag NPs) and Gold NPs (Au NPs)

Metal NPs have been investigated extensively due their elite catalytic, magnetic, and AM properties for effective delivery to bacterial and fungal strains.11 Ag possesses action against microbes and their spores, such as those in the size range of 20–40 nm which could possess better entry and residence in bacteria and fungi. They inhibit fungal proliferation from spores without causing toxicity as compared to other artificial fungicides.3 Au NPs are relatively nontoxic and are considered effective against bacteria due to highly optimized properties (such as an inability to generate reactive oxygen species [ROS] that can kill bacteria as well as ease functionalization for targeting and polyvalency). The AM activity of Au was reported due to: 1) adherence to the bacterial cell membrane, 2) modification in membrane potential and thereby resulting in ATP reduction, and 3) interruption between tRNA and ribosome assembly.12 The role of Au NPs in killing microorganisms have also been explored due to its nanosize. Au NPs of sizes <5 nm were effective against Escherichia coli and Salmonella typhi by reducing the bacterial load (90%–95%). The bactericidal effect of Au-mediated lethality was rationalized due to the roughness and dispersion of Au NPs.13

Metal oxide NPs

Leung et al14 determined that magnesium oxide (MgO) NPs damaged microbial cell membranes and caused leakage of intracellular content leading to bacterial killing. In addition, MgO NPs exhibited strong antibacterial activity which might be due to their role in mediating ROS production.14 The AM activity of calcium oxide released from NPs was investigated against Escherichia spp. and Salmonella spp.15 A CaCO3 (calcium carbonate) and MgO combination-based NP reported activity against Escherichia spp. and Salmonella spp. Vidic et al confirmed the microbicidal activity of mixed nanostructures of zinc oxide (ZnO) and MgO.16 The study evaluated the activity of the combined oxides (MgO and ZnO) encapsulated in NPs against microbes as compared to individual ZnO and MgO NPs. ZnO nanocrystals showed greater AM activity against both Escherichia spp. and Salmonella spp. ZnO has gained the highest attention in the pharmaceutical industry among all metal oxides due to its excellent antibacterial activities against a broad spectrum of bacteria with low toxicity and normal clearance. The stereochemical properties of novel green ZnO–aloe vera NPs were optimized with significant activity against several pathogenic bacteria (such as Escherichia spp. and Staphylococcus spp.). From the results, it was concluded that the ZnO–aloe vera NPs possessed increased surface energy, crystallinity, and AM activities against infectious pathogens.17 Thus, metal oxide NPs with minimal toxicity may be used to eradicate various infectious diseases. It is believed that simple and low-cost inorganic AM agents (such as metal and metal oxide NPs) serve as another nanomedicine substitute of conventional antibiotics, promising for the future of medicine.

Nanoemulsions as nanostructures

Nanoemulsions are thermodynamically stable nanocarrier systems widely used as a delivery system for drugs. In our research laboratory, we have fabricated nanoemulsions loaded with ethambutol and exposed them to Mycobacterium smegmatis to evaluate in vitro anti-Mycobacterium activities. Scanning electron microscopy revealed a detrimental effect of nanoemulsion-loaded ethambutol which could be due to the facilitated accumulation of nanoglobules loaded with drugs inside the membranes of bacilli.4 The control culture possessed a normal architecture with intact cell morphology, whereas the treated bacteria were found to be damaged, amalgamated, and fused after a loss of cellular integrity as shown in Figure 3A and B.4 Thus, bacterial membrane internalization of nanostructures has been reported by others as a major mechanism by which nanomaterials kill bacteria.4 This could be a promising therapeutic approach for efficient and effective drug delivery of antitubercular drugs.

Figure 3

SEM microphotograph depicting the lethal effect of nanoemulsions loaded with ethambutol against Mycobacterium smegmatis: (A) control untreated, (B) damaged cells when treated with ethambutol-loaded nanoemulsion, (C and D) chemical structure of high molecular weight amphotericin B with cyclic hydrocarbon chain (amphiphilic molecule) with three-dimensional presentation, (E) rhodamine-123-probed nanoemulsion and dye-free AmB nanoemulsion, and (F) pseudoternary phase diagram for AmB-loaded nanoemulsion (Smix: 1:3).

Abbreviations: SEM, scanning electron microscopy; AmB, amphotericin B.

In a report,18 an essential oil was formulated as a water-dispersible nanoemulsion by using high-energy ultrasound and its antibacterial activity was evaluated against E. coli. The mechanism to investigate antibacterial activity was completed by measuring potassium, protein, and nucleic acid leakage from cells using electron microscopy. The nanoemulsion possessed an enhanced effect against E. coli by increasing their ability to disrupt cell membrane integrity.18 Similar findings were reported recently by fabricating nanoemulsions using excipients (cationic and non-ionic nanoemulsions) with concerted antibacterial activity.19 The authors reported a detrimental effect of cationic placebo nanoemulsions comprising capmul oil against several Gram-positive and Gram-negative bacterial strains.19 They evaluated and corroborated such results based on the cytoplasmic content released after treatment followed by morphological assessment using transmission electron microscopy (TEM) and atomic force microscopy after exposure to bacteria.19

Amphotericin B (AmB)

AmB is a chemically macromolecular polyene (Figure 3C and D) which has been widely used for a long time in the treatment of systemic and local fungal infections. The chemical structure and three-dimensional structure of AmB are presented in Figures 3C and D, respectively. AmB remains a first-line drug for the treatment of severe visceral fungal infections and leishmaniasis despite the availability of several drugs without resistance.20 Moreover, AmB is often related with severe dose-dependent toxicities (such as nephrotoxicity, anemia, and phlebitis) and general malaise as side effects significantly limit its applications. An antifungal activity study was carried out against Candida albicans, which revealed that AmB/PEG5kDa-cholane possessed 15% more antifungal activity than AmB in buffer solution.21

Caldeira et al22 developed nanoemulsions to encapsulate AmB for the treatment of leishmaniasis. The main objective of the investigation was to evaluate the importance of stearylamine (STE) on drug encapsulation efficiency, toxicity, and in vitro effects. In vitro studies revealed that STE was capable of increasing the efficacy of AmB present in nanoemulsions, and Aforcin® showed almost the same results as nanoemulsions without STE.22 Thus, cationic nanoglobules present in the nanoemulsion might have been found to internalize more with negatively charged fungal cells due to electrostatic attraction. Similar reports were conducted recently using cationic nanoemulsions with an increased killing effect against bacteria showing that cationic nanoglobules were densely adherent around the bacterial membrane.19

Oral SLNs

SLNs are novel nanoparticulate structures fabricated from the mixing of triglyceride-containing oils in the solid core of the particles. Despite topical applications of SLNs, these carriers can be used for oral delivery in the form of tablets, capsules, pellets, and parenteral methods. Tobramycin (TB) was orally effective for the treatment of cystic fibrosis of a gastrointestinal tract (GIT) infection caused by Pseudomonas aeruginosa.23 Thus, SLNs are concentrated inside the cells after passing through the transmembrane increasing TB payloads inside the cells.24

Table 2 provides a short summary of the nanocarriers reported for the delivery of AM agents with informative data that should be of high value for research scientists and formulation designers working in the domain of nanomedicine.25–46

Table 2

A short review of nanomedicines for the delivery of antimicrobial agents

Nanomedicines	Drug	Main components	Major findings	Reference
Polymeric NPs	Halofantrine	PEG-PLA nanocapsule	Targeted Plasmodium berghe Prolonged the circulation half-life	25
	Rifampicin, isoniazid, ethambutol, pyrazinamide	Alginate nanoparticle	Targeted M. tuberculosis High drug pay load Improved PK profiles High therapeutic efficacy	26
	Rifampicin, isoniazid, ethambutol, pyrazinamide	PLG nanoparticle	Targeted M. tuberculosis Improved PK profiles Improved pharmacodynamics	27
	Amphotericin B	Poloxamer 188-coated PCL nanosphere	Targeted Candida albicans Reduced in vivo toxicity due to decreased accumulation into the kidney	28
	Arjunglucoside	PLA nanospheres	Leishmania donovani Reduced toxicity	29
SLNs	Rifampicin, isoniazid, pyrazinamide	Stearic acid	Targeted Mycobacterium tuberculosis Increased residence time Improved bioavailability Decreased dosing frequency	30
	Tobramycin	Stearic acid, soya phosphatidylcholine, and sodium taurocholate	Targeted Pseudomonas aeroginosa Enhanced bioavailability	31
	Clotrimazole	Glyceryl tripalmitate and tyloxapol	Targeted fungi (eg, yeast, aspergilli, dermatophytes) Prolonged drug release improved physical stability high encapsulation efficiency	32
NLC	Fluconazole	NLCs	In vitro skin retention was improved In vivo skin retention was 5 times higher than drug solution. Maximized therapeutic efficacy against the Candida strain	33
Nanoemulsion	Rifampicin	Sefsol 218 oil-based nanoemulsion	Suitable for intravenous delivery Stable drug delivery system	34
Liposome	Streptomycin	Phosphatidyl glycerol, phosphatidyl choline, and cholesterol	Targeted Mycobacterium avium Improved antimicrobial efficacy	35
	Amikacin	Hydrogenated soy phosphatidylcholine, cholesterol, and DSPG	Targeted Gram-negative bacteria Prolonged drug exposure	36
	Vancomycin or teicoplanin	Egg phosphatidylcholine, diacetylphosphate, and cholesterol	Targeted methicillin-resistant Staphylococcus aureusIncreased uptake by macrophages Enhanced intracellular antimicrobial effect	37
	Gentamycin	PHEPC, cholesterol, and PEGDSPE	Targeted Klebsiella pneumonia Increased survival rate of animal model Increased therapeutic efficacy	38
	Polymixin B	DPPC and cholesterol	Targeted P. aeroginosa Reduced bacterial count in lung Increased bioavailability Decreased bacterial lung injury	39
	Amphotericin B	Hydrogenated soy phosphatidylcholine, cholesterol, and DSPG	Targeted Aspergillus fumigatus Targeted drug delivery	40
Cubosome (liquid crystalline carrier)	Rifampicin	Lipid-based dispersion	Sustained drug release from the formulation	41
	Amphotericin B	Lyotropic crystalline nanoparticles	Oral bioavailability was increased (6 times) as compared to native drug using glyceryl monooleate and dietary lipid (phytantriol)	42
Micelle	Pyrazinamide	Poly(ethylene glycol)-poly(aspartic acid) copolymer	Anti-Mycobacterium activity was found significant than original drug	43
Dendrimer	Sulfamethoxazole	PAMAM dendrimers	Targeted Streptococcus, Staphylococcus aureus, and Haemophilus influenza Sustained drug release Increased antibacterial activity	44
	Nadifloxacin and prulifloxacin	PAMAM dendrimers	Targeted various bacteria Improved water solubility	45
	Artemether	PEGylated lysine-based copolymeric dendrimer	Targeted Plasmodium falciparum Increased drug stability and solubility Prolonged drug circulation half-life	46

Abbreviations: SLN, solid lipid nanoparticle; NLC, nanostructured lipid carriers; NP, nanoparticle; PLG, poly-lactide-co-glycolide; PCL, poly(ε-caprolactone); PLA, poly(D,L-lactide); DSPG, distearoylphosphatidylglycerol; PHEPC, partially hydrogenated egg phosphatidylcholine; PEGDSPE, 1,2-distearoylsn-glycero-3-phosphoethanolamine-N-(polyethylene glycol-2000); DPPC, 1,2-dipalmitoyl-sn-glycero-3-phosphocholine; DSPG, distearoylphosphatidylglycerol; PAMAM, polyamidoamine; PK, pharmacokinetic; CMC, critical micelle concentration.

Oral polymeric NPs

Polymeric NPs have several unique features for AM drug delivery such as particle size, zeta potential, modified drug release data, and targeted AM ability using lectin as a ligand which attaches to simple or complex carbohydrates present in/on bacterial cell walls. During polymer NP preparation, AM drugs are either adsorbed to the nanocapsules incorporated during the polymerization process or covalently conjugated to the surface of the NPs after formation. The lipophilic molecules are loaded easily into the oil phase of the lipid-based NPs. Similarly, water soluble drugs are generally attached through covalent conjugation. It is noteworthy that their covalent linkage leads to inactivation of AM activity that needs to be verified before application. Polymeric NPs have been explored to deliver various AM agents with improved therapeutic efficacy.

Cationic bioadhesive chitosan NPs have also been established for a broad spectrum of antibacterial, antiviral, and antifungal activity. Later, chitosan conjugation was found to have high bactericidal action based on their biocompatibility, non-toxic nature, antibacterial properties, low immunogenicity, and their ability to act as an absorption enhancer.47 Chitosan NPs have demonstrated considerable antibacterial action depending on several factors such as pH and the solvent used. Moreover, chitosan was found to reduce the activity of metallic NPs despite its unknown reason for mode of action. Recently, comprehensive studies have focused on the effect of chitosan on Burkholderia cenocepacia and corroborated many membrane-related functions such as respiration, resistance modulation, cell division, the drug efflux system, and transport.47 This might be due to interactions of lipopolysaccharides with chitosan leading to the destabilization of membrane proteins and membrane lysis for cell death.47

AIDS is a deadly CD4+ cell disorder caused by the HIV that leads to the death of millions of people across the world. Protease inhibitors (PIs) are one of the main classes of anti-HIV drugs recently approved for the treatment of AIDS. However, eight PIs are approved, and saquinavir is the most potent among them. The treatment of AIDS with conventional saquinavir is not optimal due to its poor bioavailability.48 Multi-drug resistant 1 proteins led to the efflux of the drug because of its resemblance with the substrate analog of the P-gp-mediated system. The development of nanocarriers to encapsulate antiretroviral drugs may be a solution to the above-mentioned problems. The study concerning the antiviral activity of NPs was carried out by inducing viral infection of the target cells. The drug encapsulation efficiency and cell targeting efficiency were more than 70% and 92%, respectively. The developed formulation caused better control of viral proliferation when it was applied to the viral strain (NL4-3 and Indie-C1). Moreover, the same study was carried out at two different targets (T-cells) such as Jurkat and CEM-CCR5 cells to compare with a saturated solution of a drug (control). Chitosan NPs were optimized and showed better efficiency for cell targeting. This was to efficiently control viral proliferation in target T-cells.24

The minimum inhibitory concentration (MIC90) for plain (AmB), anionic, and Polyethylene glycol-lipid nanoparticles (PEG-LNPs) was 0.125 µg/mL and was found to be fivefold higher than AmBisome®.49 In vivo antifungal tests were conducted using an immunosuppressed mouse infection model. Efficiency of the PEG-LNPs was found to be higher than AmBisome®.49 The highly cleft architecture and high density gave higher surface area to size ratios and provided immense reactivity with microorganisms in vivo.50 Polyamidoamine (PAMAM) has been quite extensively studied as a dendrimer owing to its higher density of functional groups for AM drug delivery by causing a reaction to AM conjugation.51 Dendrimers having quaternary ammonium salts which act as biocides are responsible to break down bacterial membranes and show increased AM activity against target bacteria.50 The polycationic nature of this polymeric biocide facilitates electrostatic adsorption to the negatively charged bacterial surface. This leads to increased membrane permeability and enhanced accumulation of the polymer into the bacteria which further results into an escape of potassium ions followed by complete fragmentation of the bacteria.50 PAMAM dendrimers with silver salts have been investigated for considerable AM activity against Staphylococcus spp., Pseudomonas spp., and Escherichia spp.51 Sulfamethoxazole encapsulated into the PAMAM dendrimers in the core of ethylenediamine has profoundly increased water miscibility and efficacy as an antibacterial agent, the same as several other drugs.51

Poly(d,l-lactide-co-glycolic acid) (PLGA) has also been exploited to prepare AmB-loaded PLGA NPs and nanosuspensions as an alternative to Fungizone® and AmBisome®. An in vivo study using an Aspergillus fumigatus–infected mouse model showed that PLGA NPs and nanosuspensions were more effective than Fungizone® while both were two- and fourfold more efficient as compared to AmBisome®.52 An in vivo study was carried out to determine the amoebicidal activity of the formulation against Balamuthia mandrillaris and was compared to a drug solution and AmBi-some®. Conclusively, the nanosuspension showed maximum efficacy followed by the pure drug solution and AmBisome®.53

Oral micellar-based drug delivery

AmB has also been loaded into polymeric micelles composed of poly(ethylene glycol)-block-poly(ε-caprolactone-co-trimethylene carbonate) [PEG-p(CL-co-TMC)] and in vitro antifungal activity was investigated against C. albicans. Moreover, it was noted that the MIC of PEG-p(CL-co-TMC) was in the range of 0.30–1.19 µg/mL (at different concentrations) and Fungizone® showed an MIC of 0.15 µg/mL.54 Furthermore, a new micellar carrier was applied to deliver AmB using PLGA/dextran graft copolymer micelles. Particle size and drug loading efficiency of the formulation was 200 nm and 80%, respectively. The AM effect of the formulation was investigated against C. albicans, and it was found that micelles and pure AmB showed almost the same MIC value (~0.625 µg/mL). It was concluded from that study that AmB-loaded polymeric micelles are a potent AM agent carriers requiring further investigation.55

Oral cubosomal (liquid crystalline nanostructured) drug delivery

Cubosome is a cubical crystal NP composed of basic glyceryl monoolein and a surfactant stable in the gastrointestinal (GI) fluid. Yang et al used a solEmuls technique for developing AmB-loaded cubosomes to enhance its oral bioavailability with an encapsulation efficiency of 87.8%.56 In vivo studies showed zero nephrotoxicity and improved PK parameters as compared to Fungizone® in a rat model.56 Angra et al57 developed AmB-loaded microspheres using cross-linked BSA with a particle size of <5 µm and a zeta potential of ~30 mV. In vitro studies suggested that the formulation did not show any signs of toxicity and had comparable antifungal activity to that in solution.57

Rizwan et al58 investigated the effect of the hydrotrope type (ethanol, polyethylene glycol-200, and propylene glycol), concentration, and the lipid-to-stabilizer (pluronic F127) ratio on cubosome formation. Optimized formulations were studied for their capability to include and maintain ovalbumin (Ova), a model hydrophilic protein regularly utilized to develop the vaccine.58 They further reported the development and physicochemical profiles of modified cubosomes to encapsulate the agonist of the toll-like receptor, monophosphoryl lipid A, and imiquimod as a new vaccine delivery system as well as the capacity of the delivery system to encourage immune responses toward the model antigen Ova. They studied the comparison of the immune stimulating capacity of cubosomes and liposomes. The results confirmed that cubosomes could deliver an antigen to the antigen-presenting cells and prime native T-cells.58 Yang et al used the solEmuls technique for developing AmB-loaded cubosomes with glyceryl monoolein to present a more stable and efficient cubosomal formulation as compared to the marketed Fungizone®.56 Moreover, a Caco-2 cell line study confirmed the active transport of AmB cubosomes with a 5.1-fold higher transport than Fungizone®. Finally, it has been concluded that cubosomal AmB enhanced the oral delivery of drugs without causing toxicity.56 Various components used in the preparation of nanomedicines for AM applications are listed in Table 3.

Table 3

List of common components employed in nanomedicines

Excipients in nanomedicines
Lipids
Fatty acids	Monoglycerides	Diglycerides	Triglycerides	Wax	Liquid lipids	Cationic lipids
Dodecanoic acid	Glyceryl monostearate	Glyceryl palmitostearate	Caprylate triglycerate	Beeswax	Soya bean oil	Stearyl amine
Myristic acid	Glyceryl hydroxystearate	Glyceryl dibehenate	Caprate dibehenate	Carnauba wax	Oleic acid	BKC
Palmitic acid	Glyceryl behenate		Glyceryl tristearate	Cetyl palmitate	Medium chain triglycerides	CTAB
Stearic acid			Glyceryl trilaurate		α-Tocopherol/vitamin-E	CPC
			Glyceryl trimyristate		Squalene	DDAB
			Glyceryl tripalmitate		Hydroxyoctacosanyl-hydroxyl stearate	DOTAP
			Glyceryl tribehenate
Surfactants
Ionic		Amphoteric		Co-surfactant		Non-ionic
Sodium cholate		Egg phosphatidyl choline		Ethanol		Tween 20, Tween 40, Tween 60 Tween 80
Sodium deoxycholate		Soy phosphatidyl choline		Butyric acid
Sodium taurodeoxycholate		Hydrogenated egg phosphatidylcholine		Propylene glycol		Span 20, Span 40, Span 60, Span 80, Span 85
Sodium dodecyl sulfate		Hydrogenated soy phosphotidyl choline		PEG-400		Tyloxapol
Sodium oleate		Phospholipon 80-H		Transcutol-PG		Poloxamer 407
		Egg phospholipid (Lipoid E-80, Lipoid E 80S)				Poloxamer 127
		Soy phospholipid (Lipoid S75)				Poloxamine 908
						Brij 78
						Tegocare 450
						Solotol HS 15
						Labrasol
						Cremophor-EL
Others components
Counter ion		Surface modifiers				Ionic polymers
Mono-octyl phosphate		DPPE-PEG 2000				Dextran sulfate sodium salt
Mono-hexadecyl phosphate		DSPE-PEG 2000
Mono-decyl phosphate		SA-PEG 2000
Sodium hexadecyl phosphate		mPEG 2000-C-LAA18
		mPEG 5000-C-LAA18

Abbreviations: CTAB, cetrimide; BKC, benzalkonium chloride; CPC, cetyl pyridinium chloride; DDAB, dimethyl dioctadecyl ammonium bromide; DOTAP, N-[1-(2,3-dioleoyloxy) propyl]-N,N,N-trimethyl ammonium chloride; PEG-400, polyethylene glycol-400; DPPE-PEG 2000, dipalmitoyl-phosphatidyl-ethanolamine conjugated with polyethylene glycol 2000; DSPE-PEG 2000, distearoyl-phosphatidyl-ethanolamine-N-poly (ethylene glycol) 2000; SA-PEG 2000, stearic acid-polyethylene glycol 2000; mPEG 2000-C-LAA18, α-methoxy-PEG 2000-carboxylic acid-α-lipoamino acids; mPEG 5000-C-LAA18, α-methoxy-PEG 5000-carboxylic acid-α-lipoamino acids.

Oral SEDDS

SEDDS are capable of emulsification into nanocarriers or microcarriers (several structures) in gastric fluid media under mild agitation of physiological gastric movement. Wasan et al developed AmB-loaded SEDDS (Peceol/1,2-distearoyl-sn-glycero-3-phosphocholine [DSPC]-PEG lipid) formulations to increase stability, drug solubility, and antifungal activity.59 These formulations with drug content in the range of 100–500 µg/mL significantly decreased the number of colony-forming units (CFUs) in all organs by 80%. Kidneys showed a CFU reduction by 75% and 95% at a 5 and 10 mg/kg dose, respectively, as compared to the untreated group. No change in the level of creatinine in C. albicans-infected rats was found.59 Cytotoxicity studies confirmed a negligible toxicity to macrophages, and it was concluded to be a suitable carrier for AmB.43 Several authors reported the AM activity of lipids and surfactants wherein excipients revealed innate antibacterial, antifungal, antiviral, and antiparasitic potential.10,60–62 Table 4 shows a brief summary concerning lipids reported to have inherent anti-Mycobacterium activities.63–66

Table 4

Reports suggesting anti-Mycobacterium activity of certain lipids or fatty acids

Lipids	Anti-Mycobacterium activity reports	References
Chaulmoogric acid and hydnocarpic acid	Chaulmoogra oil reported for effective anti-Mycobacterium activity (M. leprae).	60
Free fatty acids	The effect of fatty acids on oxygen consumption by bacterium was studied in relation to their bactericidal action.	61
Chaulmoogric acid series and other fatty acids	Anti-tubercular and anti-leprotic activities (antiseptic and bactericidal actions) of different proportions of salt of fatty acid content of chaulmoogric acid were reported. Sodium salt of chaulmoogric acid was found to be bactericidal rather than bacteriostatic in action.	62
Long-chain fatty acids	Long-chain fatty acids had anti-Mycobacterium action due to detergent-like action on the cytoplasmic membrane.	10
Saturated and unsaturated long-chain free fatty acids	About 71 mycobacterial strains were studied for susceptibility for saturated and unsaturated free fatty acids (C2–C20) at pH 7.0. Most Mycobacterium species were resistant to saturated free fatty acids except lauric acid (C12:0) and capric acid (C10:0). Unsaturated free fatty acids (C16–20) were substantially toxic to mycobacteria. Particularly, M. smegmatis, M. fortuitum, and M. chelonie were susceptible to C12:1, C18:3, C20:5, and activity was found to be more marked with increase in number of double bond to carbon chain (C16–C20).	63
Four fatty acids: capric, lauric, oleic, and linolenic acids	These fatty acids were investigated against different variants (smooth and rough variants; T and D). Smooth T variants were more susceptible to all three fatty acids as compared to smooth D variants followed by same susceptibility against rough ones.	64
Amphiphiles	Amphiphiles showed activity against M. smegmatis strain (ATCC 607) probably due to the elevated cell surface hydrophobicity (highest among microorganisms) of mycobacteria. The tricarboxylate amphiphiles exhibited the best activity with specific chain length (C20).	65
Dendritic amphiphiles: nine series of dicarboxyl and tricarboxyl dendritic amphiphiles	These were active against M. abscessus, M. avium, M. chelonae, M. marinum, and M. smegmatis. These amphiphiles resolved the poor aqueous solubility of natural long-chain fatty acids, alcohols, and amines to enable profiling the susceptibilities of the different strains to the physicochemical properties. Various dendritic amphiphiles exhibited greater anti-Mycobacterium activity with high critical micelle concentrations and low hemolytic activities offering a platform for newer antibiotics.	66

Recently, rifampicin (RIF) and isoniazid (INH) were delivered by fabricating self-nanoemulsifying drug delivery systems (SNEDDS) employing excipients with innate anti-Mycobacterium activities (M. smegmatis and M. tuberculosis).67 The authors reported improved PK parameters followed by a profound detrimental effect against these strains at the explored concentrations by the optimized SNEDDS formulation.67 Figure 4A–F shows a three-dimensional response surface graph, interaction curve, and residual curves of labrasol and capmul content present in the nanoemulsion formulation, suggesting a mathematical relationship of the zone of inhibition (ZOI) against both strains (MS-942 and MS-995), respectively. There was a linear relationship of ZOI with the labrasol content against M. smegmatis (MS-942) while the ZOI was found to be quardratic with M. smegmatis (MS-995) (Figure 4A–D). Moreover, there was no interaction between the components on the response, and the model was found to be the best fit for the selection of the optimized nanoemulsion to produce a more detrimental effect with an optimized blend of labrasol and capmul MCM C8 (labrasol, campmul, and cremophor-EL were 500, 250, and 250 mg in the final optimized formulation, respectively).67 Thus, it was corroborated that the explored excipients at their concentrations tested were capable of producing an extremely lethal effect against Mycobacterium acting synergistically with INH or RIF.

Figure 4

Results of the experimental design-based optimization of nanoemulsions comprised of labrasol and capmul MCM C8 with respective ZOI (zone of inhibitions) against MS-942 and MS-995 strains (Mycobacterium smegmatis). A–C are three-dimensional surface response plots, interaction curves and residual plots of ZOI against MS-942, respectively. Similarly, D–F are three-dimensional surface response plots, interaction curves, and residual plots of ZOI against MS-995, respectively.

Abbreviation: ZOI, zone of inhibition.

This finding was further confirmed by a morphological study using TEM wherein the treated tubercular strain (M. tuberculosis H37 Rv) was observed to be fragmented, lysed, amalgamated, and profoundly damaged (Figure 5). Untreated cells were found to be normal with a smooth margin of intact bacilli without an abnormal structure as shown in Figure 5A.67 Figure 5B–D revealed the sequential damage of the bacterial cell wall, and cell membrane followed by a loss of cytoplasmic content. Figure 5E showed internalization of nano globules with bacterial membranes responsible to produce severe structural damage (black arrows). Moreover, Figure 5F presents the possible mechanistic view of action of the nanoemulsions leading to the creation of tiny pores in the cell wall and thereby removal of the cytoplasmic material from the cell (red encircled area). Such findings have been supported by several authors wherein nanoemulsions comprising labrasol and glyceryl monocaprylate showed cytoplasmic content lost after treatment to Gram-negative and Gram-positive bacterial strains.16 Collectively, it can be inferred that the explored labrasol- and capmul-based nanoemulsions address the concern of the safe delivery of anti-tubercular drugs with reduced resistance development and dose-dependent side effects with maximum efficacy per economic cost compared to conventional dosage forms.

Figure 5

Results of a TEM study on the morphological assessment when treated with optimization placebo nanoemulsions comprised of labrasol and capmul MCM C8 in comparison with untreated tubercular bacilli (Mycobacterium tuberculosis H37 Rv). These representative images portrayed sequential events after 30 minutes of treatment with explored nanoemulsions, suggesting a possible mechanistic view of action against a tubercular strain. (A) Normal intact smooth margin of tubercular bacilli, (B and C) progressive damage of a bacterial cell wall followed by fragmentation (black arrows), (D) loss of integrity of bacterial cell wall, (E) mechanistic view of nanoemulsion action after adherence around the bacterial cell surface (nano globules around the surface), and (F) oozing out of the cytoplasmic content of bacterium after nanoemulsion mediated cell wall damage.

Abbreviation: TEM, transmission electron microscopy.

Topical and transdermal nanomedicines

Several nanostructured carriers have been investigated for the topical and transdermal delivery of AM agents. These routes are preferred for local and systemic delivery, respectively, using various lipid- and polymer-based NPs. In this section, polymeric NPs, lipid-based vesicular systems (liposomes and elastic liposomes), SLNs, and nanoemulsions are emphasized with in vitro and in vivo findings.

SLNs

Various unique features of SLNs show a promising option for AM drug delivery in cosmetic and skin products for local action and transdermal products for systemic action. It contains occlusive components which rapidly form a thin film after application and reduces water evaporation to retain skin moisture. Thus, their occlusive nature facilitates molecule penetration into a deeper layer of the skin, such as SLNs encapsulated with retinol and retinyl palmitate which have shown enhanced drug diffusion rates from the epidermis and lesser amounts of drug expulsion than the free drug.68 SLNs can deliver azole (an extremely poorly soluble drug) antifungal drugs to cutaneous fungal infections such as tioconazole, miconazole, econazole, oxiconazole, and clotrimazole.69 These drugs are complicated to apply and deliver to infected cells. Therefore, they can be loaded in an efficient manner into SLNs which causes an occlusive effect, and the nanosized particles increase drug residence time into the upper layer of the skin through enhanced penetration across the skin.

Lv et al70 prepared penciclovir-loaded NPs for the topical delivery of drugs for the treatment of hepatitis virus, herpes simplex virus type-1 (HSV-1) and HSV-2, varicella-zoster virus (VZV), Epstein-barr virus (EBV), and cytomegalo virus. Penciclovir is a potent synthetic nucleoside analog (prodrug) extensively used for the treatment of HSV with very low oral bioavailability (6%–10%). However, its clinical use is significantly limited. Results showed that the percent of drug penetrating through excised rat skin from the developed NPs was more than twice as that compared to the marketed cream after 12 hours of administration.70

Corware et al71 used soluble AmB with polymethacrylic acid for the treatment of cutaneous leishmaniasis in non-healing BALB/c mice. In vitro studies revealed less toxicity and high effectiveness against leishmaniasis-infected macrophages as compared to deoxycholate AmB. From PK studies in BALB/c mice, it was found that a dose amount of 18 mg/kg body weight showed effective healing of lesions. It was concluded that AmB polymethacrylic acid can be used pharmacologically for lesion healing.71 Chen et al developed SLN as a podophyllotoxin (POD)-loaded topical nanocarrier for targeting the superficial layer of skin for the treatment of the human papilloma virus (HPV).72 The growth of the upper layer of skin (epithelial cells) infected with HPV can be prevented by POD in the epidermis. Hence, this drug has been used as the first-line drug in genital warts. This formulation showed a fivefold more effectiveness with minimum side effects.72

Liposomes

Vesicular lipid bilayer carriers such as liposomes have been explicitly employed to deliver numerous drug candidates by researchers in various domains of drug delivery. They have been investigated for higher transdermal permeation and prolonged stability with positively charged liposome formulations.73 Devi et al formulated different vesicular systems to deliver AmB to treat topical fungal infections and the prepared formulations were characterized for loading efficiency, particle shape, size, stability, in vitro release profile, and anti-fungal activity.74 Moreover, transfersome dispersion showed the highest transdermal flux (1.66 µg/cm2/h) and drug retention into the skin (77 µg) among them, suggesting a threefold higher flux value as compared to ethosome dispersions and relatively higher than liposomal dispersions (0.51 µg/cm2/h). In vitro anti-fungal studies revealed that transfersome dispersions maximized ZOI as compared to other formulations. In vivo skin irritation assessment was performed using albino rats that confirmed insignificant irritation scores as compared to conventional AmB therapy.74

Dithranol is a first-line drug for the treatment of topical psoriasis and has been delivered using liposomes. The use of conventional dithranol in disease conditions leads to a necrotizing effect, irritation, burning sensation, and discoloration effects on healthy and diseased skin. The entrapped drug in vesicles was visualized for the localized delivery and improved availability at the site. This could reduce the dose and dose-dependent side effects, such as irritation and staining.75

Polymyxin B-loaded liposomes have been used as an alternative successful delivery vehicle. This molecule has been well established to treat P. aeruginosa infections, such as lung disease and cystic fibrosis in chronic bronchopneumonia.76 However, in vivo clinical use has been restricted owing to some kind of toxic effects on vital organs (such as kidney, neuromuscular, etc).77 Interestingly, an investigation has been completed concerning the encapsulation of the drug molecule in the liposomes which significantly diminished severe side effects and increased efficacy against microbes, such as strains of P. aeruginosa.77 The mechanistic view of membrane fusion has been reported for the development of polymyxin B encapsulated in liposomes which was used against P. aeruginosa. Studies using TEM, flow cytometry, and fluorescent resonance energy transfer confirmed that there were reorganizations in the lipid structure when it was incubated with P. aeruginosa membranes.76 Membrane fusion of drug-loaded liposomes with bacterial strains is a quite swift and spontaneous process driven by non-covalent forces (Van der Waals forces and hydrophobic interactions) that minimize the free energy of the system. A more commonly known factor for antibiotic resistance is the P-gp efflux pump and has been extensively reported by several researchers as a strong mechanism for microbial drug resistance. The pump is made of proteins and acts as a transporter embedded and assembled in bacterial membranes leading to the efflux of AM drugs outside the cells even after absorption.78 After fusion with the bacterial membrane of liposomes, an increased amount of drug was instantly transported to the cytoplasmic portion through a membrane, which can profoundly suppress drug resistance by inhibiting the efflux pumps system and eventually improves AM activity of a drug.78

Several liposome-based novel formulations for AM drugs have been fabricated for many therapeutic applications such as ampicillin and benzyl penicillin for higher AM efficacy as compared to the drug solution.79,80 Kadimi et al81 developed AmB-loaded liposomal formulations using the fluid state of a carbon dioxide (SFC-CO2) process and a probe sonication method. Liposomes were characterized by phase contrast microscopy. Particle sizes of the formulations prepared by the SFC-CO2 method were 0.15–3 µm and when formed by a sonication method were from 0.15 to 6 µm. In vitro anti-fungal activity revealed that both liposomes and standard AmB solutions had the same ZOI.81

Elastic liposomes

Zidovudine (AZT) has been loaded into elastic liposomes for the management of HIV and AIDS. However, limitations with its use have been due to dose-dependent hematological toxicity, low plasma half-life, extensive hepatic first-pass metabolism, and low bioavailability. The targeted and sustained drug delivery of AZT using transfersomal formulations has been accomplished. Furthermore, researchers have developed elastic liposomes using PEG AZT formulations and studied their transdermal flux on rat skin which confirmed results of biodistribution, indicating a 28-fold higher accumulation of AZT in lymphoid tissues when it was applied as compared to the free drug.82 Furthermore, these authors prepared elastic liposomal formulations of acyclovir sodium for transdermal delivery in the treatment of various viral diseases and reported enhanced transdermal flux on rat skin compared to conventional liposomes bearing drug and plain drug solutions. Hussain et al reviewed several elastic liposomes with their chemical compositions, advantages, and limitations.83

Ethosome

Topical delivery is patient friendly and non-invasive as compared to parenteral routes of administration. Kaur et al reported the enhanced topical delivery of AmB in nanoethosomal formulations with vesicle sizes in the range of 186.0±2.0 to 298.0±4.0 nm in the treatment of cutaneous fungal infections.84 The prepared nanocarriers were included into the gel base to obtain a nanogel which was elastic in nature and restraint to deformation at 37°C. The value of yield stress of the nanoethogel was calculated (109.05±2.4 Pas) and compared against marketed formulations (52.15±0.9 Pas). Enhanced drug–skin permeation and deposition studies were also carried out followed by drug penetration using confocal laser scanning microscopy (CLSM) and an in vivo Draize test study confirmed zero skin irritation.84 Jain et al developed transdermal ethosomal formulations of lamivudine (an anti-HIV drug) for the management of AIDS and hepatitis. Lamivudine has a very small biological half-life (4–6 h), and there is a need for frequent administration for over a prolonged period of time to achieve a desired antiviral effect.85 Moreover, they studied ethosomes loaded with hepatitis B surface antigens for in vitro qualitative and quantitative uptake by human dendritic cells and its ability to stimulate T lymphocytes for reducing the viral load.85

Nanoemulsions as AM agents

Drugs used in the management of microbial diseases of the skin belong to antibiotics which hinder important microbial biochemical activities. Indiscriminate utility of these drugs precipitates consequences of multiple drug resistance against pathogens and, thus, leads to the need of new AM development. The non-toxic agents are of great importance to kill a variety of microbial organisms. The toxic nature of certain drugs has limited their topical application. Quaternary ammonium compounds have low potential efficacy against various pathogens (fungi and bacteria), whereas chlorhexi-dine is a broad-spectrum antibiotic agent due to its potential activity and low toxic effect on the skin.86 The activity was pH dependent and found to be reduced significantly in the presence of organic matter.86 Thus, there is a constant need for the development of safe AM formulations with a broad range of rapid biocidal activities. For this reason, non-ionic surfactant-based nanoemulsions are constantly being prepared and tend to be stable with the addition of a minimum content of surfactants. Nanoemulsions are the first choice with antimicrobicidal activity against various infection-causing pathogens in the skin.87 Hamouda et al investigated nanoemulsions possessing a strong efficiency to kill spores of Bacillus spp.87 In some studies, 1% emulsions were found to be effective against influenza virus, Neisseria spp., Streptococcus spp., Bacillus spp., and Cholerae spp.87 They further evaluated activities against HSV-1, influenza, and other viruses and fungistatic activity against C. albicans.87

In our preceding publications, a nanoemulsion was developed as a nanocarrier for the enhanced topical delivery of AmB.88 An oil-in-water nanoemulsion was prepared using different ratios of surfactants and co-surfactants following a spontaneous titration method as shown in Figure 3E and F. Of the different formulations, F1 was considered optimal with a 96.9%±1.0% transmittance value. The formulation was characterized for particle size (67.37±0.8 nm) and zeta potential (−3.7±1.2 mV). An optimized formulation showed a higher drug release rate as compared to commercial Fungisome®. In vivo skin deposition studies reported a 2.11-fold higher drug deposition from formulations as compared to Fungisome®.88 Furthermore, the same nanocarrier was exploited employing a sefsol-218 lipid for enhanced stability and permeation potential for topical delivery.9 Different formulations were developed at varying pH and temperatures of a continuous phase. Formulations showed the highest flux rate (17.85±0.5 µg/cm2/h) as compared to Fungisome® (7.97±0.01 µg/cm2/h) and drug solution (5.37±0.01 µg/cm2/h). The CLSM results demonstrated enhanced skin penetration of the drug at pH 6.8 and 7.4. Conclusively, the formulation was stable at pH 7.4 with a higher shelf life (12 months) at refrigerated conditions. The prepared nanoemulsion gel (0.1% w/w AmB in carbopol base) showed the highest flux rate (18.08±0.6 µg/cm2/h) as compared to the nanoemulsion (4.59±0.01 µg/cm2/h) without skin irritation (as conformed in a Draize test). Finally, the nanoemulsion gel served as an economic and effective topical delivery system of AmB.9 A breakthrough of recent developments for the topical delivery of AmB was reported employing the synergistic activity of excipients (lipid and surfactant) in nanoemulsion form using peceol and labrasol which revealed potential in vitro antifungal activities.89

Ophthalmic drug delivery

Ocular drug delivery is well established by several researchers and has been employed for various drug molecules available commercially. The potential issue associated with ophthalmic formulations is its residence time after instillation and frequent washing by the eyelids while blinking. However, bioadhesive biocompatible polymers (chitosan and carbopol) have been explored to enhance drug residence time followed by release improvement by various researchers for the treatment of eye infections. Das and Suresh reported an improved delivery of AmB to the ocular surface employing nanosuspensions prepared by a solvent displacement technique with a mean size range and zeta potential of 150–290 nm and +19–28 mV, respectively.90 From in vitro studies, it was found that there was 60% of drug release in 24 h with the same efficacy as that of the free AmB solution.90 Several authors have reported to deliver AmB using other nanostructures such as NPs, NLCs, SLNs, liposomes, elastic liposomes, ethosomes, transfersomes, and gel formulations.4,88 The basic fundamental purpose of these carriers is to deliver drugs with enhanced ocular permeation across the corneum layer of the eye for an extended time period. All nanostructures have been fabricated using several lipids, surfactants, co-surfactants, stabilizers, and other particular components. Aminoglycosides were loaded in liposomes and served as a reservoir to prolong drug release directly to the site of action after topical application. This study witnessed that the therapeutic efficacy would be improved in eye infections of AIDS patients.91 These excipients have been tabulated in Table 3.

Inhalation nanostructures

Shah and Misra developed AmB-loaded liposomal dry powder inhalation formulations.92 The formulations were prepared using hydrogenated soya phosphatidylcholine (PC), cholesterol, saturated soya phosphatidylglycerol (7:3:0.5) with ethyl acetate and ethanol (1:1) as an organic solvent by reverse phase evaporation methods and were characterized for mean particle size as 1.8±0.2 and 2.0±0.3 µm, respectively.92 In one report, the effect of temperature (at 35°C and 4°C) on the transfer of drugs from AmBisome® to fungal cell membranes was investigated followed by antifungal activity of AmBisome® against S. cerevisiae. At 35°C, the formulation showed effective antifungal activity as compared to 4°C. The binding ability of AmBisome® to the yeast cells was further studied and it was observed that the formulation binding was achieved after 3 h of exposure at 35°C.93 Imam et al prepared and characterized distigmasteryl hemisuccinoyl-glycero-phosphatidylcholine liposomes.94 The liposome particle size was found to bê100 nm with a negative zeta potential (~0.2 mV). The formulation was found to be less toxic than Fungizone®. In vitro antifungal studies revealed lower values of MIC against Candida as compared to AmBisome®. Moreover, the anti-leishmanial potential of the formulation was found to be similar to AmBisome® and Fungizone®. The liposome maximum tolerated dose was estimated to be 60 mg/kg using BALB/c mice.94

Optical properties of metal NPs

Noble metals have been used for years for radiation therapy of cancer, diagnosis of diseases (X-ray), drug delivery, and for sensors and detectors. Moreover, these have been explored for fine tuning their surface plasmon absorption band by changing particle size into the nanometer regime which further results into increased interactions between the electric field of light and oscillation of electrons.95 It was observed that ultraviolet emission intensity is enhanced (60-fold) when the core of the Ag NP was coated with ZnO as compared to Au (17-fold).95 The investigators suggested that metal NPs are suitable tools for the enhanced detection of ionizing radiation.95

Current challenges of nanomedicines/nanomaterials

Recently published reviews have summarized and compiled informative data from the literature concerning the safety profile of nanomaterials followed by addressing challenges for the delivery of AM agents.96 Authors have comprehensively viewed various aspects of (eco)toxicological risks and a potency to induce antimicrobial resistance (AMR) owing to AMCs when applied to healthcare sectors. They have discussed issues in light of recently published scientific reports and expert opinions (eg, members of the Cooperation in Science and Technology Programme, COST and Action AMiCI, AntiMicrobial Coating Innovations).96 It is noteworthy that weighing the risk and benefits of AMCs in healthcare settings requires a thorough assessment of 1) ecotoxicological hazards in health-care settings, 2) experiences obtained from AMR evaluations, 3) addressing the quality, efficacy, and safety evaluation of AMCs at the level of a “Safety by Design Approach,” and 4) involving stakeholders for the risk–benefit analysis of AMCs created AMR.96 A potentially promising tool against microbial growth is AMCs employed in healthcare sectors which are based on chemical strategies and technologies such as 1) AMCs containing active eluting agents (ions, NPs of metals, antibiotics, chloride, iodine), 2) immobilized molecules on contact surfaces, and 3) light-activated molecules (such as TiO2 or photosensitizers).97–99 These authors have compiled a comprehensive review on the risk of AMR to biocides used as AMCs wherein several issues need to be resolved through regulatory bodies, such as the European Commission.95 It is noteworthy that NPs of metals (silver, copper, zinc, etc) are extensively used in AMCs due to innate superior biocidal efficacy introduced as additives in hospital fabric bandages, wound dressings, and intravenous catheters.100–102 A comprehensive approach for the risk–benefit analysis in the healthcare sector is still required and limited data have been reported on high-quality studies for these concerned issues.

Despite several benefits of AMCs, these may cause serious adverse effects on human, livestock, and microbiota after reaching the ecosystem. Particularly, a slow and steady diffusion of nanomaterials leached from AMCs may induce different types of AMR as compared to current antibiotics.103 Thus, scientific committees recommend the limited use of AM in a balanced way in all areas and highlight the urgent need for assessing major AMR contributors.104 The issues that need to be resolved are 1) information on currently used biocides in terms of volumes and production sources, 2) epidemiological data of the public health on the relevance to AMR, 3) data on environmental stability, 4) triggering factors for the emergence of AMR, and 5) generation of international standards for testing and surveillance on AMR.

In brief, major current issues for nanomedicines/nanomaterials include:

Major challenges of AMC applications in healthcare settings (solid–air interface and solid–liquid interface), particularly for nanomaterials.

Ecotoxicological hazards of nanomaterials for mammalian cells at environmental levels.

Risk–benefit weighing of AMCs before development and application.

Challenges in the drug delivery of nanomedicines.

Importance of “safe by design” strategies.

Some of these issues are described shortly in the present review.

Possible (eco)toxicological risks related to AM agents used

Broadly, AMCs can be grouped into three categories such as 1) antibacterial agent release-based coatings, 2) antibacterial agent contact killing-based surfaces, and 3) anti-adhesion surfaces (eg, topographically modified surface). A majority of AMCs are based on category (1) wherein biocides (silver ions) are released either from Ag NP or polymeric NPs, such as nanosilver-based coatings. A slow release of silver results into AMR against bacteria and therefore a long shelf life is desired to tackle the AMR.105 In contact killing, there is an interaction between the bacterial cell surface and subsequent inhibition by virtue of surface topography (a smooth surface with more bacterial as compared to a rough surface), releasing agents in the vicinity, and bacterial repulsion (hydrophilic/hydrophobic interactions).106,107

AMs incorporated in AMC are inherently toxic to proliferating pathogens. However, these intrinsically show harmful effects on animals, humans, and microorganisms such as algae. Most commonly noted notorious metal NPs are those containing silver, copper, and zinc. These metal ions are water soluble salts released into the aquatic ecosystem that then produce toxic effects on aquatic bioorganisms/animals.108,109 Moreover, the authors expanded on the use of AgNPs with sizes ranging from 10 to 40 nm for widespread use in AMCs.95 AgNPs could be a promising approach for AM action due to the release of Ag ions and the subsequent release of ROS for producing detrimental effects to bacteria.95 However, there are now new concerns over bacterial resistance to Ag as well as its cytotoxicity to mammalian cells; such studies highlight the complex biosafety issues by using Ag (and all) NPs for antibacterial applications which require more investigation especially at the in vivo level. A dossier of the project “NanoTrust” addressed the adverse effect of AgNP on human and aquatic animals due to the 1) development of silver-resistant bacteria owing to released subtoxic levels of Ag ions, 2) compromised human skin microflora to regularly exposed cosmetic containing silver nanomaterials, and 3) accumulation of silver at elevated concentrations into aquatic animals/microflora.110 Recently, nanosilver nanomedicines have been reported to have toxic effects on the same ecosystems and human beings.59 Moreover, meta-analysis of toxicity due to NPs of ZnO, CuO, and ZnO used in AMCs suggested remarkable lethality on ecotoxicological test organisms (aquatic crustaceans and phytoplanktons) as compared to bacteria which could be due to waste released to the aquatic environment.111

Possible risks of AMCs related to the potential development of AMR

It has been pointed out that there is horizontal gene transfer of AMR to pathogens or environmental bacteria. The effect of concentration, exposure time, cleaning procedure and hospital wastewater management are aspects to consider as prime precautions to avoid AMR and gene transfer. Thus, AMR is a global problem arising from potential AMC inducers which contribute to a developed resistance.112

Current challenges in drug delivery of nanomedicines

The use of nanomaterials is gaining interest with the greatest attention in diverse fields such as theranostics, personalized medicine, tissue engineering, highly sensitive diagnostics (biosensors), and nanostructured lab-on-a-chip systems interacting with a biological interface.113,114 Despite the tremendous benefits of nanomedicine in patients and society, nanomedicine is moving in new directions possessing certain challenges to the field at a fundamental level in future decades.115 This might be due to a limited understanding of the complex interaction among developed artificial nanomaterials, biological surfaces (at the protein, cellular, and whole organism level), and immediate environment (or ecosystem). Furthermore, there is a need to improve our understanding of surface chemistry, morphology (nanoscale to macroscale), material softness, and biosafety aspects greatly affecting biological behavior.113–115 We would like to emphasize the intravenous administration of nanomaterials that has certain challenges, but researchers have moved very quickly to establish technologies (and companies). Today, these assumptions still remain, such as a highly warranted investigation of the so-called enhanced permeation and retention effect in humans instead of xenograft models (where usually 4%–8% of the injected doses reach the solid tumor).113,116 Another challenge is a very poor understanding of the barrier constituted by the extracellular matrix, in a drug delivery context and a lack of data from larger animals and humans with spontaneous tumors. In addition, a lack of understanding of targeting ligands for overexpressed receptors on the tumor cells conjugated with NPs, the interplay between the target and nanomaterials, quantitative assessment of in vivo cellular uptake, and unavailable techniques for the quantitative assessment of drug targeting are also continuous problems that need to be solved before the field can grow.

The principle of effective doxorubicin delivery to the active/target site of the current commercial product DOXIL is based on using physicochemical characteristics for successful delivery which is only applicable for a small dose range and unsuitable for large dose biologicals. Recent advanced approaches in drug release have been explored, such as the application of heat, light, ultrasound-sensitive systems, and pH- and enzyme-based strategies (such as the lower pH of tumor cells and endosomes inducing drug release).113 Employing pH/enzyme-based targeted delivery could be an interesting approach wherein drug binding is not based on tumor identification; however, transferring in vitro findings to in vivo performance has been a challenging issue. Investigations using drug delivery systems are not available to evaluate the pharmacokinetics of drugs from nanocarriers directly inside the cancer tissues. Nanomedicines as drug delivery systems are still facing challenges due to a lack of a thorough understanding of the interplay between protein adsorption on nanomaterials resulting in a significant variation in their biological/therapeutic behavior.117

Despite programmable nanomaterials offering great promises in the healthcare system, the dichotomy of the nanotechnology and nanotoxicology paradigms must be of the utmost consideration. Therefore, before nanomaterials can be routinely integrated into mainstream therapeutics, several key gaps must be considered. The US Food and Drug Administration and the Alliance for NanoHealth in 2008 organized a joint workshop in this area where six areas were identified as critical priorities that remain as priorities to date.118 These include 1) the development of imaging technologies, 2) determination of the distribution of nanovehicles in the body upon their systemic administration, 3) the biological affinity of nanodrugs, the pathways by which they are internalized, retention time, and their ability to translocate across barriers, 4) the development of new computational models for predicting the human health risks of nanomaterial exposures, 5) the establishment of consensus toxicity testing protocols, and 6) understanding the unexpected secondary effects of NPs.119

Exposure of nanomaterials (at specific concentrations) leads to undesirable outcomes. Thus, there is need to understand the mechanistic view of nanomaterial uptake, interaction with the physiological molecules, environment, and toxicity to inform a “safe by design” leading to safer nanomaterial applications. Several nanomaterials may be a significant challenge with a “systems biology” approach and can be feasible to build efficient molecular and computational screening tools to overcome those challenges.118

Recently, Jennifer et al reported a critical review for challenges in the delivery of nanomedicines for cancer treatment.120 However, queries still need to be answered such as: 1) a complete understanding of the tumor heterogeneity and the biological factors responsible for the behavior of nanomedicines in cancers, 2) translation from formulation-driven research to disease-driven development, 3) to implement the most relevant animal model and diagnostic protocol, and 4) the prior selection of the patients most likely to respond to specific nanomedicine therapies.120 Conclusively, the present review also highlighted the major concerns about the deficiency of studies for a clinical and mechanistic understanding of nanomaterials at the molecular level to produce sufficient evidence to exploit nanomaterials safely for human applications and keeping the ecosystem healthy.

Carbon nanotube (CNT) and graphene oxide (GO) in AMCs: a safe alternative

Recently, some authors have focused on the solid–air interface (as a main concern considering tables, door handles, computer keyboards, textiles, etc) as well as the solid–liquid interface (taps, shower, and drains wherein biofilms appear frequently) in healthcare units.121 Thus, new alternative methods (state-of-the-art topographical modification, chemical modifications using polyethylene glycol or hydrogel) are needed to reduce microbial activity and infection and develop antibiotic resistance. Biocide release based strategies are “toxic by design” approaches where the slow release of biocides results into the development of antibiotic resistance which becomes toxic to humans as well as other ecosystems.96 However, CNTs, graphene (diamond like-carbons), and GO have promised prudent AM activity with relatively low cyto-toxicity to human tissues and other ecological biosystems.121 It is noteworthy that whether these novel systems achieve AM activity on the surface or whether it occurs when released in an aqueous solution is still unknown. A synergistic effect has been reported when CNTs were combined with chitosan in hydrogen, dendrimers, and Ag2S quantum dots.122–124 Shorter CNTs embedded in a poly(lactic-co-glycolic acid) polymeric matrix exhibit greater AM activity as compared to longer CNTs.124 Several investigations have been published on plant extracts revealing significant AM action to protect food. However, such research is still limited for AM action on the surfaces in healthcare units, on medical devices, and diagnostic centers. Tea tree oil coatings have been investigated to possess AM action against methicillin-resistant Staphylococcus aureus when incubated for 2 days.125

Importance of “safe by design” in AMCs

Safe by design is a well-accepted approach for the timely assessment of risks associated with industrial innovation processes and the value chain of nanomaterials including nanoproducts. This was designed to ensure three interrelated communities such as workplace, consumers, and environment.96 Strategies based on the functional principle have been described in the previous section which may further be considered under safe by design such as 1) contact killing and 2) anti-adhesive, whereas biocide release can therefore be considered as toxic by design. Sometimes two functional strategies are combined to achieve a synergistic effect. Moreover, state-of-the-art is a new strategy identified at AMiCI meetings.121–124 Recently, upcoming “anti-adhesive” strategy approaches focus on 1) zwitterions, 2) morphology, and 3) hydrophobic materials. Similarly, polymeric brushes, bacteriophages, and enzymes are becoming strategies of “contact active.” Triggered release, quorum sensing, photo oxidation, plant extract, CNTs, and GOs are recently updated strategies used in AMCs.121 There are no standard test protocols, sufficient toxicity data, and fate of nanomaterials at the environmental and mammalian cell level. Therefore, EU programs (NanoFase, SafeNano, ProSafe, NaNoReg, and Euro-Nano-Tax) developed a procedure to establish and implement standardized toxicological measurements for the early assessment and fate of nanomedicine. They reported that four challenges in the safe design of AMCs are 1) the toxicity of the material, 2) potential impact of the material on the emergence of resistance, 3) the duration of the antimicrobial activity in the long term, and 4) the lack of a standardized method for the assessment of AM activity under representative environmental conditions.121 The rationale of adding an AM agent to a particular surface should be balanced between the potential impact of the AM agent on the development of antibiotic resistance and the impact of controlling the spread of the pathogenic strain within the healthcare environment.121

Summary and conclusion

The present review has compiled data from recently published research that addresses the challenges for the delivery of AM agents. Major findings concerning preformulation studies, drug degradation, cytotoxicity to healthy cells, and oral bioavailability are presented. In view of the challenges and limitations, numerous diverse nanocarriers have been successfully discovered for diverse routes of administration to improve local and systemic therapeutic efficacy for killing bacteria. The potential interplay of NPs with microbial cell membranes demonstrate facilitated AM delivery to the site of action working in tandem due to nanoscale carriers. Thus, with ongoing efforts in this domain, nanomedicine carriers will continue to improve the treatment of life-threatening diseases such as cancer, bacterial infection, tuberculosis, and HIV. Safety concerns of nanomaterials or nanomedicines must be of prime consideration including development, waste management, and regulatory aspects. Finally, this review provided a brief description of drug development over the last decade using nanocarriers which is hopefully valuable for their continued use in infection control followed by safety concerns of nanomedicines at environmental and mammalian cell levels.

Future prospects

Despite several advantages and the constant advancement in nanomedicine for the delivery of AM agents, we call special attention to a lack of strategies for the improved delivery of these candidates. There is still a united interest among nanotechnologists and microbiologists to implement theoretical and practical concepts against infectious diseases to overcome today’s challenges. One possible strategy is to employ safe excipients with innate AM agents which may be more detrimental against the microbes and, thus, develop an approach that may reduce unnecessary introduction of excipients and drugs into the patient’s body. This may mitigate drug-associated side effects and chances of drug resistance. Acquired drug resistance is a major challenge for most of the antibiotics used today which could be resolved by the concurrent delivery of more than one drug in the carrier against the same pathogen. Combination therapy has been expected to have high potency owing to synergistic effects and different mechanistic approaches to disturb the microbial defense system. Premature drug delivery is another major challenge for nanocarrier systems particularly in systemic delivery and targeting microbes. This loss of a drug may be reduced by drug targeting to intracellular microbes (such as M. tuberculosis) and modulating their release to the microenvironment of the infection site rather than the normal tissue (namely blood). The triggered release may be manipulated by pH, ligand binding, enzyme-mediation, and other properties, such as using pyrazinamide which is more active in an acidic medium at an infection site (pus area) than the blood pH. Lastly, it could be beneficial to use nanostructured carriers functionalized with antigen-specific ligands (site-specific drug targeting like aptamers, antigens and antibodies, antibody fragments, proteins, and peptides) for the treatment of infectious, cancerous, and cardiovascular diseases.