At the beginning of the 20th century, the concept of ion therapy was introduced, and it was demonstrated that “ionic drugs” can penetrate the skin and exert important local and systemic effects ^[1][29].

Iontophoresis is a technique that uses low-intensity electric currents to increase the absorption of drugs through the skin ^[1][29].

The values of the intensity of the electric current used in iontophoresis are between 0.5 and 20mA (Figure 12) ^[1][29].

This technology is successfully used by dermatologists to treat patients with hyperhidrosis ^[1][29].

The method uses an electrical device to inject a low-voltage current into the affected area. It is painless and relatively safe, but its effectiveness is sometimes similar to a topical antiperspirant ^[1][29].

Iontophoresis is mainly used to increase skin absorption of ionizing drugs, but neutral or weakly charged molecules can also be administered through electroosmosis ^[2][30].

Iontophoresis has been investigated with the administration of various types of drugs, including nonsteroidal anti-inflammatory drugs (ibuprofen, aspirin, and indomethacin) ^[1][29], granisetron, donepezil, and insulin ^[2][30].

In this technology, neutral or cationic products are positioned under the anode and anionic products under the cathode ^[3][31]. The low-intensity electric current used moves the ions through the skin. This method can be used to administer medicinal substances for local or systemic effects ^[3][31].

In ophthalmology, atropine, scopolamine, gentamicin and fluorescein are being tested ^[3][31]. In dentistry, they are used as local anesthesia in cases of multiple dental extractions ^[3][4][31,32]. The administration of systemic drugs (fentanyl ^[3][31], certain insulin formulas, antihypertensives, antirheumatics, antidiabetics, hormones, etc.) via iontophoresis is still under investigation ^[4][32].

Sonophoresis is a method of increasing the absorption of drugs through the skin, which uses ultrasounds with frequencies varying between 20 kHz and 16 MHz to modify the structure of the lipid layer of the stratum corneum (Figure 23) ^[3][31].

The use of ultrasound results in an increase in skin temperature and, implicitly, the better absorption of the medicine at this level ^[2][30].

In this technique, a predetermined frequency of ultrasound is used on the drug solution that is positioned under the probe, as well as on the skin ^[3][4][31,32].

Various studies have shown that ultrasound-mediated transdermal delivery had good results in the case of the administration of some proteins (erythropoietin, interferon y and insulin), ketoprofen ^[5][33] and vancomycin, which demonstrates that a wide range of hydrophilic and hydrophobic products, as well as macromolecules and small molecules, can be administered through sonophoresis ^[2][3][4][30,31,32].

The result of the sequential ultrasound procedure is so-called sonophoresis. Sonophoresis is a process of the penetration and migration (spreading) of dermo-cosmetic substances in the skin under the action of these sequential ultrasounds ^[2][30].

Electroporation is a method used to facilitate the transdermal delivery of drugs; it is based on the penetration of the skin and the creation of micropores by using high voltages (between 10 and 1000 V) for a duration of less than a few hundred milliseconds (Figure 34) ^[2][3][30,31].

With the help of pulse waves, aqueous pores are created in the double lipid layer of the stratum corneum, the solution with the active substance on the skin penetrates deeply, and thus, superior absorption is achieved (Figure 45) ^[2][30].

By using this method, good results have been reported regarding the in vitro absorption of insulin, tetracaine, thymol and fentanyl ^[3][31].

Blagus et al. performed in vivo research using this method on rats, following the degree of absorption of fentanyl, dextrin and doxorubicin ^[4][32].

Galvanization achieves superior absorption in the skin ^[2][30].

Microns (MNs) are defined as needles with heights between 25 μm and 2000 μm, and the materials used in their preparation determine their applications ^[2][3][30,31]. The principle of the microneedle release system consists of the creation of microns that penetrate the stratum corneum, which limits absorption, to create micropipes through which the medicine is deposited in the dermis. (Figure 56) ^[2][30].

This new technology presents multiple advantages from many points of view:

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MNs can penetrate the stratum corneum, avoiding contact with nerves and capillaries, offering a faster, efficient, painless and comfortable delivery compared to other transdermal administration methods ^[2][3][4][5][30,31,32,33].

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It does not require specialized personnel for administration.

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By dissolving and forming the hydrogel, MNs eliminate the need to use specific measures for the disposal of needles and syringes, and the risk of contamination or accidental reuse is avoided ^[6][7][8][34,35,36].

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The patient’s skin can regenerate very quickly after the removal of MNs; thus, there is only a very low probability of infection and irritation at the application site, as well as possible occurrences of isomorphic lesions due to the Koebner phenomenon, such as lichen planus and psoriasis ^[6][7][8][34,35,36].

MNs are used to make micropipes with an absorption role in the patient’s skin; after removing the needles, a transdermal patch is applied with a medicinal substance that is released through passive diffusion in the skin ^[7][8][35,36].

Covered MNs are obtained through different methods to ensure uniform coverage ^[7][8][35,36]. A coating is used consisting of the medicinal substance combined with surfactants and thickening agents, which ensure adhesion to the needle ends ^[7][8][35,36]. The needle tips are coated with a formulation in the form of a solution or dispersion ^[6][7][8][34,35,36]. To make the MNs, polymers or metals are used ^[6][7][8][34,35,36].

After the MNs have penetrated the skin, at the moment of contact between the interstitial liquid and the coating, it is dissolved and absorbed ^[6][7][8][34,35,36].

Empty MNs are formulated to release a drug continuously into the skin through needle holes ^[2][3][4][5][30,31,32,33]. The solution or dispersion containing the medicinal substance is loaded inside the MNs and then administered transdermally ^[2][3][4][5][30,31,32,33]. (Figure 56c) Empty MNs and solid MNs can be made of glass, polymers, silicon and metals ^[2][3][4][5][30,31,32,33].

As an advantage, compared to solid MNs and coated MNs, MNgol has a greater capacity to fill with medicine ^[2][6][30,34].

Following application to the skin, the needles also dissolve from the MN matrix, and the active substance is released slowly (Figure 56d) ^[2][30].

In the case of the manufacture of these forms of transdermal administration methods, mixtures of biocompatible and soluble polymers with medicinal substances are used ^[2][30].

Polymers can be vinyl alcohol, polycarboxymethylcellulose, vinylpyrrolidone, hyaluronic acid and copolymers of methyl vinyl ether and maleic acid ^[2][30].

A reservoir containing the active substance is embedded in the empty MN upon application, and after penetration through the skin, the MN swells due to the absorption of interstitial liquid, the reservoir dissolves and the medicine is absorbed through the already-dilated ducts ^[2][5][30,33]. A hydrogel mass is formed to control the release of the drug depending on the crosslinking power of the hydrogel network. This allows the drug to be released slowly over a long period (Figure 56e) ^[2][5][30,33].

In dentistry, special needle-based devices could be very useful and beneficial, because oral carcinoma is often oral squamous cell cancer and is very difficult to detect in the early stages, being asymptomatic ^[2][5][30,33]. These special devices can detect elevated levels of biomarkers, such as Cyfra 21-1, TPA, CA-125 antigen, MMP-9 and TNF-α ^[9][10][37,38].

Microneedles can be used in dental periodontal surgery as an adjuvant because they can accelerate the healing process and locally increase platelet-derived growth factor (PDGF), transforming beta and alpha (TGF-β and TGF-α), connective growth factor and fibroblasts (FGF) ^[10][11][38,39]. They can potentiate neocollagenases and neovascularization through intercellular matrix layering and fibroblast proliferation ^[11][39].

Antimicrobial patches that hold gingival-grip microneedles could help speed up the healing of periodontal lesions ^[11][12][13][39,40,41]. These microneedles are loaded with antimicrobial agents, possibly with green tea and nano-silver, and these patches have been used in experiments designed to suppress the microbial load at the periodontal wound site ^[12][13][40,41].

Following a study, rat experiments demonstrated that analgesic microneedle (AMN) patches have been developed using pain-free soluble content microneedles with the transdermal transfer of the selective antagonist peptide CGRP to treat localized neuropathic pain ^[14][42].

Compared to conventional therapies, AMN patches produced a satisfactory analgesic effect without influencing the motor function of laboratory animals, indicating the high specificity of the peptides released against CGRP receptors ^[14][42].

Recently, the use of a combination of a stainless steel nanoemulsion and microns was studied to improve the transdermal delivery of aceclofenac ^[15][43].

Researchers created an amorphous molecular complex by combining different anti-inflammatory substances (flurbiprofen, etodolac, naproxen, piroxicam and indomethacin) and lidocaine and examined the physicochemical properties of the complex ^{[16][17][18][19]}[44,45,46,47].

The focus was on intermolecular flurbiprofen–lidocaine interaction. They found that the solubility of flurbiprofen was 100 times higher than the product alone, and the solubility of lidocaine was 2 times higher ^[18][46]. The conclusion was that it was possible to develop a transdermal preparation with anti-inflammatory and analgesic effects useful for treating the pain of various diseases ^[18][19][46,47].

Ionic liquids (ILs) are ionic salts in a liquid state over a wide temperature range (between ambient temperature and below 100 °C), with high polarity and very high ionic conductivity, high thermal stability, negligible vapor pressure, low volatility and viscosity, non-flammability and a very good recycling capacity ^[19][20][21][47,48,49].

Third-generation ionic liquids comprise an innovative class of functional materials with improved properties, characterized by excellent biological activity, due to their physical–chemical and biological properties, low toxicity and especially their biotechnological and pharmaceutical potential ^{[22][23][24][25]}[50,51,52,53]. These ILs are distinguished by surprising antimicrobial and antibacterial, antibiofilm (bacterial resistance) and antitumor pharmaceutical activity ^{[22][23][24][25]}[50,51,52,53].

The role of third-generation biodegradable ILs has been highlighted in the case of transdermal drug delivery systems ^[26][54]. Within these systems, ILs can play various roles: as active pharmaceutical ingredients, in drug modification or as transdermal permeation enhancers, as individual agents or in combination with other agents or as chemical permeation enhancers ^[26][54].

The incorporation of active pharmaceutical ingredients (APIs) brings about efficient API-IL drug delivery systems, which currently represent an innovative solution for improving the pharmacokinetic and pharmacodynamic properties of many less water-soluble drugs by increasing their solubility, bioavailability, permeability and stability, as well as by eliminating polymorphisms ^[19][27][47,55].

IL molecules are able to act as ideal solvents (green solvents) for drug substances, allowing topical and transdermal administration ^[28][56]. Incorporating ILs into water, oils or hydroalcoholic solutions bring about topical IL-based drug administration systems, which have very good therapeutic efficiency at the level of the hydrolipidic film of the skin barrier, due to the increase in drug solubility and the increase in the local permeability of the skin ^[19][28][47,56].

Cholinium-amino-acid-based ionic liquids display high efficiency in the transdermal delivery of ferulic acid and puerarin by improving the solubility and permeability of these two APIs ^[28][56].

The skin release capacity of hyaluronic acid has been improved using different choline-based ionic liquids, the strongest being obtained for an IL consisting of choline and citric acid ^[29][57].

1-butyl-3-methylimidazolium hexafluorophosphate and 1-hexyl-3-methylimidazolium chloride showed 5% higher antimicrobial activity and higher skin penetration levels ^[30][58].

In vitro studies on the production of insulin biopolymer films based on biocompatible ILs have also been performed to improve the transdermal permeability of insulin ^[31][59].

A study showed that ionic fluids are safe, contribute to the increase in skin permeability and are promising applications in the field of transdermal systems used in pain treatment ^[32][60].

The design of non-irritating drug-IL systems, with high efficiency for permeability through the skin, is based on the effects of the structure of counterions: polarizability, their molecular weight and their polar surface area ^[33][61].

The therapeutic potential of the topical delivery of siRNA (small interfering RNA) using ionic liquids (ILs) for the treatment of genetic skin diseases is enhanced by the use of choline-geranic acid ionic liquid ^[34][62].

The exact mechanism of this anti-inflammatory combination with low-dose capsaicin for the treatment of osteoarthritis pain is still under investigation ^[35][63].

The efficacy of transdermal administration for biologics is limited due to the barrier function of the stratum corneum and possible adverse reactions ^[36][64].

Bee venom has been studied since the early 19th century and has been shown to have a complex composition that confers numerous potential therapeutic uses ^{[37][38][39][40]}[65,66,67,68].

Many studies are conducted specifically to test the anti-inflammatory effect of bee venom and its mechanism of action ^{[41][42][43][44][45]}[69,70,71,72,73].

Efforts are being made to discover safe practices combined with modern delivery systems to minimize adverse reactions ^[46][74].

Melittin in the composition of bee venom is responsible for the anti-inflammatory action and is therefore the most studied compound ^{[47][48][49][50][51][52]}[75,76,77,78,79,80].