Monodispersed sodium hyaluronate microcapsules for transdermal drug delivery systems

This study presents an alternative to cross-linking for the preparation of monodispersed polymer microcapsules made from water-soluble and biocompatible sodium hyaluronate (SH). Water was removed from monodispersed drug-containing SH droplets by creating an osmotic pressure difference, causing the droplets to thicken and solidify into microcapsules. The fabricated microcapsules were water-soluble and could be stored in oil for at least one month without dissolution, thereby retaining the contained drug. In addition, we used SH microcapsules to prepare biodegradable microneedles (MNs), one of the materials for transdermal drug delivery systems (TDDS), by embedding the microcapsules in poly(lactic-co-glycolic acid) copolymer, which was molded into a needle shape. The MNs embedded with drug-containing microcapsules released the drug over time based on the amount of microcapsules contained and were capable of penetrating the stratum corneum of the skin. These findings show the application potential of these monodispersed SH microcapsules for TDDS, while avoiding the common issues associated with cross-linking, such as toxicity and bursting. This novel material exhibits potential for use in pharmaceutics and cosmetics.


Introduction
Hyaluronic acid (HA) is a natural linear polysaccharide comprising alternating D-glucuronic acid and N-acetyl-Dglucosamine disaccharide units connected via (1→4) glycosidic bonds 1 . HA is abundant in the synovial fluid and extracellular matrix and can retain large amounts of water owing to its high negative charge. Therefore, HA plays a major role in controlling tissue hydration 2 . In the field of cosmetics, HA is an excellent moisturizer used in skin care and serves as a material for skin wrinkle suppression, skin condition improvement, and facial rejuvenation [3][4][5][6][7] . The biocompatibility, biodegradability, and water-retention ability of HA and its sodium salt, sodium hyaluronate (SH), have enabled its use in various forms, such as solutions [8][9][10] , hydrogels [11][12][13] , and microcapsules 14,15 , in the medical field for arthritis treatment 8,16 , ophthalmic treatment 9, 10 , and drug delivery 11,[17][18][19] . HA can bind to receptors in the liver, kidney, lymphatic vessels, and tumor tissues, and is therefore used as a carrier in drug delivery systems (DDS) [including transdermal drug delivery systems (TDDS), which are used for administering drugs into the skin 20 ] to deliver genes and anticancer drugs to target cells 13,[21][22][23] . HA and SH have been used for the continuous administration of peptide and protein drugs 14,24,25 . Microcapsules based on HA and SH and that protect the inclusion drug from the external environment and prevent whole-dose failure have been developed, although certain microcapsules exhibit malfunction 26,27 .
HA and SH for DDS can be prepared by converting watersoluble HA and SH to water-insoluble forms via chemical or physical cross-linking 14,24,25,28 . Chemical cross-linking produces cross-linked HA and SH with excellent mechanical strength and degradability control properties, but the toxicity of the crosslinking agent must be considered 11,18 . Physical cross-linking (such as ionic cross-linking) does not require toxic cross-linking agents, but bursting is associated with the resulting fragile cross-linked HA and SH, which can lead to drug overdose. Therefore, new methods for the fabrication of HA-and SHbased DDS materials are required to avoid these issues.
Microcapsules can be mass-produced via monodispersion [coefficient of variation (CV) = <10%] using microchannels and are widely used as drug, compound, and cell carriers in the form of droplets and polymer microparticles 15,[29][30][31][32][33][34] . A shrinkage and gelation technique, where osmotic pressure difference and diffusion are used to generate microparticles from droplets, has been previously reported 33,[35][36][37] . Previous applications of this technique generated monodispersed sodium alginate droplets in microchannels, which were transferred to a gel plate with a high concentration of calcium chloride, which served as a cross-linking agent for sodium alginate. The droplets were dehydrated due to the osmotic pressure difference between the droplets and gel plate and simultaneously solidified via the diffusion of calcium chloride from the gel plate to the droplets. The microcapsules produced using this technique were monodispersed; the size was controlled by the flow rate of the dispersed and continuous phases introduced into the microchannel as well as the osmotic pressure difference between the droplets and the gel.
Biodegradable microneedles (MNs) are an alternative to oral and subcutaneous injections and are minimally invasive DDSs that deliver drugs through the skin [38][39][40] . MNs, biodegradable polymers that are loaded with drugs and molded into needle shapes, penetrate the stratum corneum to deliver drugs (including polymeric and water-soluble ones) directly into the skin. Various materials (such as poly(lactic-coglycolic acid) (PLGA) [41][42][43] , polyglycolic acid 44 , and polylactic acid 45 ) are used for MNs.
The aim of the present study was to prepare water-soluble monodispersed SH microcapsules for TDDS using the shrinkage and gelation technique 35 . Monodispersed microcapsules typically offer well-controlled release properties 46 , and the solidified microcapsules are capable of maintaining monodispersity without coalescence. Drug-containing monodispersed SH droplets were generated using a microchannel, where the generated droplets were concentrated via dehydration due to the osmotic pressure difference and thickened (solidified) due to concentration. The resulting non-crosslinked SH microcapsules were characterized based on size, water solubility, and storage stability. In addition, we fabricated MNs with embedded microcapsules to impart sustained-release property using PLGA, which is an established material for sustained-release preparations 41, 47, 48 .

Microcapsule preparation
2.1.1 Microchannel fabrication. Microchannels were used to generate the monodisperse droplets, which served as templates for the formation of microcapsules. The microchannels were fabricated using a conventional fabrication method based on photo-and soft-lithography 49 . The microchannels were designed based on a previous report by Rotem et al. 50 ( Figure S1). A convex mold was prepared by curing photosensitive resin (SU-8 2100, KAYAKU Advanced Materials, Inc., USA) under ultraviolet light via a photomask printed with a microchannel design. Polydimethylsiloxane (PDMS) (SILPOT 184, Dow Corning Toray Co., Ltd., Japan) mixed with a curing agent (weight ratio = 10:1) was poured into the convex mold, cured in an oven at 85 °C for 2 h, and released from the mold. Inlet and outlet holes (diameter = 1.0 mm) were punched into the PDMS slab. The PDMS slab was irradiated with oxygen plasma and permanently bonded to a glass plate. The microchannels were treated with Sigmacote (Sigma, USA) to render them hydrophobic.
2.1.2 Droplet formation using microchannels. SH droplets containing fluorescein isothiocyanate conjugate with bovine serum albumin (FITC-BSA) as a model drug were prepared. The SH droplets were obtained by introducing a continuous oil phase and dispersed aqueous phase into the microchannel via a syringe and polytetrafluoroethylene tube (inner diameter = 0.8 mm, outer diameter = 1.4 mm) using syringe pumps (KDS-200, KD Scientific, USA) ( Figure 1a). The continuous phase comprised mineral oil (Sigma Aldrich, USA) with 1 wt% surfactant (SY-Glyster CRS-75, Sakamoto Yakuhin Kogyo Co., Ltd., Japan), and the dispersed phase comprised 0.01 or 0.1 wt% SH aqueous solution (Fujifilm Wako Pure Chemical Industries, Ltd., Japan) with 0.5 mg/ml FITC-BSA (Sigma Aldrich, USA). An inverted microscope (CKX53, Olympus Corporation, Japan) equipped with a high-speed camera (FASTCAM Mini, Photron, Japan) was used to observe droplet formation.

Microcapsule formation from droplets.
The water solvent was removed from the droplets containing the model drug FITC-BSA and SH, comprising a viscous aqueous solution. This allowed for concentration of the droplet content to form solidified droplets (i.e., microcapsules). Water was removed from the droplets using a gel plate with high osmotic pressure. The gel plate was brought into contact with the droplets via a thin layer of oil and surfactant ( Figure 1b). The gel plate was prepared using 2 wt% agarose gel (Agarose S, Fujifilm Wako Pure Chemical Industries, Ltd., Japan) and 0.2, 0.4, 0.6, 0.8, 1.2, 1.6, 2.0, or 2.4 mol/L calcium chloride aqueous solution (CaCl 2 aq. ; Fujifilm Wako Pure Chemical Industries, Ltd., Japan). Equal parts of dissolved agarose gel and CaCl 2 aq. were mixed, poured into a polystyrene dish, and cooled to room temperature (approximately 20°C) for solidification. CaCl 2 is an osmolyte and acts as a gelling agent for sodium alginate but not for SH. The resulting gel plates comprised 1 wt% agarose gel and 0.1, 0.2, 0.3, 0.4, 0.6, 0.8, 1.0, or 1.2 mol/L CaCl 2 aq . Sunflower oil (Fuji Film Wako Pure Chemical Industries, Ltd., Japan) and 1 wt% SY-Glyster CRS-75 surfactant were poured onto the gel plate, and the droplets generated using the microchannel were collected on the gel plate and incubated at room temperature for concentration and solidification. An inverted microscope (BZ-X710, KEYENCE Co., Ltd., Japan) was used to acquire the transmitted light images and fluorescent images of the droplets and the microcapsules.

Confirmation of water solubility.
The solubility of the microcapsules in oil, ethanol, and water was evaluated. The microcapsules were placed in a continuous oil phase in a microtube. The microcapsules were separated via centrifugation at 750 rcf for 1.5 min (Eppendorf, Germany). The oil phase was aspirated with a pipette and replaced with ethanol. The microcapsules were re-dispersed in the ethanol and centrifuged at 750 rcf for 1.5 min. The ethanol was removed using a pipette. The entire process was repeated thrice. The microcapsules were re-dispersed in water and centrifuged at 750 rcf for 1.5 min.

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Preservation stability.
A stable storage period for the prepared microcapsules was established by storing a suspension of the microcapsules at 4 °C and under ambient temperature (22-28 °C). Confocal microscope images (16-bit) and phase-contrast images of the microcapsules were acquired over time using a confocal microscope (FLUOVIEW FV10i, Olympus Corporation, Japan) and an inverted microscope (BZ-X710), respectively. The fluorescence intensity and diameter of the microcapsules were determined using image analysis software (ImageJ, National Institute of Health, USA).

Microneedle preparation
2.3.1 Microcapsule pretreatment. The microcapsules were embedded in MNs by replacing the continuous phase around the microcapsules with a material that was miscible with the MN substrate material-namely, PLGA ( Figure S2). The suspension of microcapsules was transferred from the gel plate to a 1.5 ml microtube and centrifuged at 750 rcf for 1.5 min. Three separate layers were acquired-oil phase, microcapsule-containing oil phase, and aqueous phase. The microcapsules were resuspended in the oil phase by gently tapping the microtubes. Silicone oil (KF-995, Shin-Etsu Chemical Co., Ltd., Japan) was dropped onto the sample to form a layer of silicone oil between the suspension and the aqueous phase.
The suspension layer was transferred to another microtube to remove the aqueous phase, and the volume of the suspension layer was adjusted to 1 ml by adding sunflower oil with 1 wt% SY-Glyster CRS-75 surfactant. The microcapsules were counted using a disposable cell counting plate (Fukae  Kasei Co., Ltd., Japan), and the desired number of microcapsules (1.2×10 6 , 2.4×10 6 , or 3.6×10 6 ) was transferred to another microtube. The oil phase was completely replaced with silicone oil by settling the microcapsules in the oil phase via centrifugation at 750 rcf for 1.5 min. The oil phase was removed, and the silicone oil was added. Centrifugation was repeated to separate the microcapsules from the silicone oil. The replacement process was repeated twice to obtain a microcapsule suspension. The silicone oil used in this study (which is used as a cosmetic additive) had a lower boiling point than the heating temperature for dissolving PLGA. Because the silicone oil can volatilize during the molding of MNs (in contrast, sunflower oil does not volatilize and phase separates from PLGA), we used it as replacement for the sunflower oil. Additionally, the viscosity of the silicone oil was lower than the appropriate oil phase viscosity for droplet shrinkage and solidification (according to our previous study 33 ). Therefore, the sunflower oil was replaced with silicone oil after (but not before) the droplet shrinkage and solidification.

Microneedle fabrication.
MNs containing 1.2×10 6 , 2.4×10 6 , or 3.6×10 6 microcapsules were prepared. PDMS-based resin mixed with a curing agent (weight ratio = 10:1) was poured onto a convex metal mold (3×3 cm, stainless steel, base diameter = 200 μm, height = 700 μm, distance between needle centers = 600 μm, number of needles = 256 (16×16); Yoneyama Mold. Co., Ltd, Japan) ( Figure 2). The mold was cured in an oven at 85 °C for 2 h and then peeled from the metal mold to obtain a concave PDMS-based mold. The microcapsule suspension was mixed with 0.2 g PLGA (Sigma Aldrich, USA) melted on a hot plate set at 250 °C. The PLGA and microcapsule mixture was applied to a concave PDMSbased mold. A polyvinyl chloride (PVC) substrate (3 cm×3 cm×1 mm) was pressed onto the mixture, cooled to room temperature to solidify, and peeled from the concave PDMSbased mold to form MNs.

Microneedle characterization
2.4.1 Microneedle morphology. The shape and dimensions of the metal mold and fabricated MNs were determined using a digital microscope (VHX-6000, KEYENCE Co., Ltd., Japan). The needle dimensions (base diameter, height, and tip diameter) were determined using image analysis software (Image J).

Release properties.
The release behavior of the model drug FITC-BSA from the fabricated MNs was investigated. MNs containing either 1.2×10 6 or 3.6×10 6 microcapsules were fixed to the bottom of a 35 mm polystyrene dish using glue, and 3 ml phosphate buffered saline (PBS) (263-300 mOsm/kg, without calcium and magnesium, Thermo Fisher Scientific, USA) was added. The dish was placed in a container with water to maintain the humidity inside the container. The container was sealed and stored at 37 °C. FITC-BSA concentration in the PBS over time was determined by measuring the absorbance (495 nm) of FITC-BSA in the PBS (1 µL) using a spectrophotometer (NanoDrop OneC, Thermo Fisher Scientific, USA).

Skin puncture ability.
The penetration characteristics of the MNs into the stratum corneum were investigated. MNs containing 2.4×10 6 microcapsules were pressed against porcine skin (1 cm×1 cm; Funakoshi Co., Ltd., Japan) for 3 min. The skin surface was observed after the MNs were applied by scanning electron microscopy (SEM; VHX-D510, Keyence Corporation, Japan). A cross-sectional image of the skin was acquired using an inverted microscope (BZ-X710) from a skin sample fixed with 10% formalin (Fujifilm Wako Pure Chemical Industries, Ltd., Japan), sliced, and stained with hematoxylineosin.

Microcapsules formed from droplets
Droplets were generated using microchannels and served as templates for the microcapsules. A preliminary study (Table S1) indicated that a dispersed phase comprising 0.01 wt% SH aqueous solution and 0.5 mg/ml FITC-BSA was suitable. The flow of the dispersed aqueous phase and continuous oil phase (mineral oil with 1 wt% surfactant) into the microchannels at a constant flow rate facilitated the continuous formation of monodispersed droplets (Table 1). Please do not adjust margins Please do not adjust margins Microcapsules were produced from the droplets by removing water to concentrate and solidify the droplets. Because no crosslinking agent was used in this method, we inferred that dehydration caused the polymer in the droplets to thicken and eventually solidify. (Note: CaCl 2 did not act as a cross-linker for SH, as shown in Figure S3) As mentioned in our previous report 35 , water was removed from the droplets by placing the droplets on a gel plate containing CaCl 2 aq with high osmotic pressure. The diameters of the droplets on the gel plate were measured over time (Figures 3 and S4); the droplet diameter decreased and eventually became constant and monodispersed. The concentration of calcium chloride was proportional to the osmotic pressure: a higher concentration in the gel plate led to faster shrinkage and a smaller droplet diameter. The droplet diameter decreased to 14-20% of its original diameter, thereby increasing the concentration of the contents by a factor of 125-358. In addition, shrinkage of the droplets did not lead to breakage due to mechanical stimulation during handling with a pipette and centrifugation. This can be attributed to the difference in osmotic pressure due to generation of droplets via dehydration instead of crosslinking.
Droplet shrinkage was characterized based on the relationship between the shrinkage rate and the osmotic pressure difference between the droplet and the CaCl 2 aq in the gel plate. Specifically, droplets with three different diameters were used to investigate the difference in shrinkage behavior (herein referred to as shrinkage rate) for each original droplet size (Figure 4). A previous study 33 defined shrinkage rate as the absolute value of the slope when droplet diameter is plotted against time. A higher osmotic pressure difference led to a faster shrinkage rate, regardless of the original droplet diameter. In addition, smaller droplets exhibited a faster shrinkage rate at a given osmotic pressure difference. A previous study on the shrinkage behavior of sodium alginate droplets based on the same experimental system revealed that contact with calcium chloride initiated cross-linking within the sodium alginate droplets to achieve gradual solidification 33 . Further, the shrinkage rates of sodium alginate droplets also increased with increasing osmotic pressure difference. However, the slope of the droplet diameter-time plot for the SH droplets was 18 in the present study, which was substantially higher than that for the sodium alginate droplets (2.6) in the previous study 33 . This can be attributed to the polymer network formed within the sodium alginate droplets via cross-linking, which prevented the movement of water from inside the droplet to the surface of the droplet.
To investigate the difference in shrinkage behavior (herein referred to as shrinkage factor) for each original droplet size and to compare the behavior of cross-linked (i.e., sodium   alginate) and non-cross-linked (i.e., SH) materials, the shrinkage factor was plotted against the osmotic pressure difference between the droplet and the aqueous calcium chloride solution in the gel plate ( Figure 5). A previous study 33 defined shrinkage factor as the volume change of the droplet using Eq. (1): Shrinkage factor (%) = (original droplet volume-shrank droplet volume)/(original droplet volume) × 100 (1) The shrinkage factor increased with increasing osmotic pressure difference, and eventually reached ~99.9%. Therefore, the size of SH microcapsules can be controlled by adjusting the diameter of the original droplets and the osmotic pressure difference. The shrinkage factor of sodium alginate droplets stabilized at an osmotic pressure difference of ~10 MPa 33 . In comparison, the shrinkage factor of the SH droplets stabilized at a smaller osmotic pressure difference of ~2 MPa. This indicated that the water in the non-cross-linked SH droplets responded to a smaller osmotic pressure difference than the cross-linked sodium alginate droplets, and can be attributed to the polymer network formed during cross-linking. In addition, theoretically, osmotic pressure is constant at constant concentration, temperature, and volume, regardless of pH, as shown in the following equation: where Π, c, R, and T represent the osmotic pressure, molecular concentration, ideal gas constant, and temperature, respectively. According to this relationship, our method is more dependent on the osmotic pressure difference than the pH. Conversely, a change in pH change can alter the microstructure of the polymer. This may affect the shrinkage and solidification behavior in this method.
The traditional "solvent removal method" has been reported as a method for dehydrating and solidifying droplets 51 . This method solidifies the droplets by evaporating the liquid present in the system. This principle is simple and well established; however, applying this method to the water-in-oil droplets in our study is difficult due to the use of oil, which has a relatively high boiling point.
FITC in the microcapsules prepared by this method was completely water-soluble without insolubilization in spite of the poor solvent environment.
In addition to water-soluble content such as FITC-BSA, insoluble content (e.g., inorganic particles) can be applied in this method 33 . In the case of microcapsule generation using insoluble content, in principle, the minimum size of the resulting microcapsules is close to the total volume of the content. This indicates that the obtained microcapsule size is affected by the osmotic pressure and amount of content.
The phenomenon of droplet condensation driven by water removal, which has been reported in previous studies 52,53 , has been quantitatively evaluated using water activities (calculated based on the solute concentration of the droplet). In these previous studies, the solute concentration of the droplet could be calculated from the droplet size because its solute does not flow out or in. Conversely, as we reported in our previous study 35 , in our droplet shrinkage process, the ions contained in the gel plate flow into the droplet. The measurement of solute concentration in the droplet is limited by the complexity of measuring the ion influx. In future, when it becomes possible to measure the concentration of the ions flowing into the droplet, it will be possible to discuss the final microcapsule size in detail from the viewpoint of water activities, as has been done in previous studies.

Microcapsule characterization
The water solubility and preservation stability of the microcapsules were evaluated to demonstrate their applicability as a TDDS. The microcapsules instantly dissolved in water, but were insoluble in oil and ethanol ( Figure 6). This suggested that transdermal administration of microcapsules  Please do not adjust margins containing an active ingredient (i.e., a drug) lead to rapid dissolution of the microcapsules upon contact with water present in the skin, thereby releasing the drug. The preservation stability of the microcapsules was demonstrated by immersing the microcapsules in the oil phase to prevent drying during storage at 4 °C and ambient temperature for 1 month (Figure 7). The fluorescence intensity was measured to monitor the release of the model drug (i.e., FITC-BSA) contained in the microcapsules, whereas the diameter was measured to detect dissolution of SH in the oil phase. At both storage temperatures, the fluorescence intensity increased slightly, and no change in diameter was observed. The slight increase in fluorescence intensity was smaller for the microcapsules stored at 4 °C, suggesting that refrigeration of the microcapsules allows for more stable storage than ambient temperatures in terms of inclusion release. The water-soluble protein may have migrated toward the center of the microcapsule, away from the oil, over time. In addition, the fact that the intensity in the microcapsules did not decrease in this way suggests that the encapsulated model drug can be retained in the microcapsules (indicating high encapsulation efficiency). This also implies that the size of the microcapsules can be controlled in this method without considering the change in the encapsulation efficiency.
As the microcapsule size and fabrication parameters (such as CaCl 2 concentration) change, the specific surface area and physical properties of the microcapsules may change, respectively. These may affect the encapsulation efficiency and water solubility of the model drug contained in the microcapsules.

Application of microcapsules to microneedles
PLGA-based MNs containing microcapsules were prepared in a 256 (16 × 16) needle structure (Figure 8a-c). The dimensions of the convex metal mold and fabricated MNs were measured ( Table 2), revealing that the base diameters were almost the same but the height of the MNs was smaller than that of the convex metal mold. Further, the tip diameter of the prepared MNs was larger than that of the convex metal mold because the tip of the needles in the concave PDMS-based mold could not be filled with the high-viscosity PLGA. MNs with a sharper needle tip may be fabricated by designing a metal mold with a larger height and tip diameter or by reducing the viscosity of PLGA.
Release of the model drug, FITC-BSA, from the fabricated MNs was evaluated; deformation of the needle and substrate was observed after inserting the MNs in PBS (Figure 8d-f). For the fabrication of the MNs, we used microcapsules whose shrinkage behavior is described in Figure 3. Therefore, the following conditions were used to produce microcapsules with the same size as in Figure 3. Droplets were generated at a flow rate of 1.0 ml/h in the dispersed phase (comprising 0.01 wt% SH aqueous solution and 0.5 mg/ml FITC-BSA) and 2.5 ml/h in the continuous phase (mineral oil with 1 wt% surfactant). The generated droplets were contracted and solidified on a gel plate containing 0.2 mol/L CaCl 2 . To examine the trend of FITC-BSA concentration in PBS at a constant level (meaning that the release is complete), the time course was measured for 3 min in this study. Additionally, because PLGA melted by heating is highly viscous, the microcapsules added to PLGA could remain in the container and be lost when transferred to the PDMS mold. The loss of microcapsules can be avoided by mixing the molten PLGA and microcapsules on the PDMS mold. If the mixing of PLGA and microcapsules in a container is necessary, depending on the application, the loss of microcapsules may be reduced by using a container made of a material that does not easily adhere to PLGA. Consequently, the FITC-BSA concentration of the PBS increased over time. This increase was higher for the MNs with more microcapsules (3.6 × 10 6 ), indicating that MNs containing more microcapsules released  more FITC-BSA. The MNs containing 3.6 × 10 6 microcapsules led to an increase in the drug concentration of PBS for ~48 h, after which no significant change was observed, and drug release was complete. These findings show that MNs can be potentially used for sustained-release drug administration that may be controlled by changing the material properties of the MNs and microcapsules. In addition, the MNs with less microcapsules (1.2 × 10 6 ) showed a constant FITC-BSA concentration in PBS immediately after immersion in PBS (earlier than the MNs with more microcapsules). This suggests that the drug release was completed relatively early in the MNs with less microcapsules compared to those with more microcapsules. The amount of drug released in this study was relatively small (~0.011 mg). For applications that required additional administration, the release (dose) rate could be further increased by increasing the number of microcapsules embedded in the MNs. The ability of the MNs to puncture the skin was examined by pressing the MNs against porcine skin, where an array of puncture holes was formed on the surface of the skin ( Figure  8g). The MNs penetrated the stratum corneum (Figure 8h), which is a barrier layer containing lipids. Therefore, drugs that cannot pass through the stratum corneum, such as macromolecular drugs and water-soluble drugs, would be delivered using the proposed TDDS. A section of skin that could not be penetrated by the MNs was observed ( Figure S5). Inability to penetrate was attributed to pressure distribution caused by skin elasticity and the bed of nail effect 54 . This can be improved by fabricating MNs with sharper needles and an optimized needle pitch.

Conclusions
Monodispersed SH microcapsules were produced by applying an approach based on the shrinkage and gelation technique instead of cross-linking. This method uses non-toxic materials that are widely used as additives in cosmetics and pharmaceuticals. The size of the microcapsules was controlled according to the original droplet size and the osmotic pressure difference between the droplets and aqueous solution in the gel plate. The microcapsules were water-soluble and could be stored stably for one month. Furthermore, sustained release of SH microcapsules was observed by producing PLGA-based MNs with embedded microcapsules. The MNs released the drug into PBS over an extended time period, which was dependent on the amount of microcapsules contained. In addition, the MNs were capable of penetrating the stratum corneum. These results demonstrate that the developed SH microcapsules can be potentially used for sustained-release preparations and avoid issues commonly associated with cross-linking, such as toxicity and bursting. While physically cross-linked gels such as ionic cross-linked gels, which form a relatively fragile structure, could burst and cause discontinuous drug release in the presence of water, the developed microcapsules (and microcapsules in MNs) could stably dissolve and release drugs in the presence of water in the skin without bursting due to their water solubility. This novel material shows excellent application potential in pharmaceutics and cosmetics.

Conflicts of interest
There are no conflicts to declare.