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. 2020 Jul 30;27(1):1147–1155. doi: 10.1080/10717544.2020.1797240

Dissolving microneedles for transdermal delivery of huperzine A for the treatment of Alzheimer's disease

Qinying Yan a,b, Weiwei Wang a, Jiaqi Weng a, Zhenghan Zhang a, Lina Yin c, Qingliang Yang a,b, Fangyuan Guo a, Xingang Wang d, Fan Chen e, Gensheng Yang a,b,✉
PMCID: PMC7470133  PMID: 32729341

Abstract

Increasingly attention has been paid to the transdermal drug delivery systems with microneedles owing to their excellent compliance, high efficiency, and controllable drug release, therefore, become promising alternative with tremendous advantages for delivering specific drugs such as huperzine A (Hup A) for treatment of Alzheimer’s disease (AD) yet with low oral bioavailability. The purpose of the present study is to design, prepare, and evaluate a dissolving microneedle patch (DMNP) as a transdermal delivery system for the Hup A, investigating its in vitro drug release profiles and in vivo pharmacokinetics as well as pharmacodynamics treating of AD. Skin penetration experiments and intradermal dissolution tests showed that the blank DMNP could successfully penetrate the skin with an adequate depth and could be quickly dissolved within 5 min. In vitro transdermal release tests exhibited that more than 80% of the Hup A was accumulatively permeated from DMNP through the skin within three days, indicating a sustained release profile. In vivo pharmacokinetic analysis demonstrated that the DMNP group resulted in longer Tmax (twofold), longer t1/2 (fivefold), lower Cmax (3:4), and larger AUC(0–∞) (twofold), compared with the oral group at the same dose of Hup A. Pharmacodynamic research showed a significant improvement in cognitive function in AD rats treated with DMNP-Hup A and Oral-Hup A, as compared to the model group without treatment. Those results demonstrated that this predesigned DMNP is a promising alternative to deliver Hup A transdermally for the treatment of AD.

Keywords: Dissolving microneedles, transdermal delivery, huperzine A, Alzheimer's disease

1. Introduction

Alzheimer's disease (AD) is a common degenerative disorders of central nervous system, and is generally considered as the primary cause of dementia in people aged 65 and over (Association, 2017, 2018). AD is characterized by a gradual decline in learning, memory, and executive function, which is the production of amyloid plaques and neurofibrillary tangles in the brain, as well as the loss of neurons associated with memory and learning (Hager et al., 2001; Selkoe & Hardy, 2016; Sevigny et al., 2016). By 2050, the number of AD patients will increase from 47 million to 130 million (Nguyen et al., 2017), which will be a tremendous social and economic burden to the whole world.

Numerous drugs have been designed and developed in the past several decades, including acetylcholinesterase inhibitors (AChEIs) (Galimberti & Scarpini, 2016) and cerebral blood flow and brain metabolism improver (Wu & Wen, 2016). Huperzine A (Hup A), from a Chinese herb, Huperzia serrata, is an effective AChEI (Ferreira et al., 2016; Zheng et al., 2016), and has been proved to significantly improve the memory of elderly AD patients (Wang et al., 2006), as well as to enhance the memory and academic performance of young students (Zhang et al., 2002). Currently, commercially available pharmaceutical forms of Hup A include oral dosages such as tablets (Xie et al., 2013; Peng et al., 2019), and capsules (Laicher & Fuchs, 1998) and injections, specifically intramuscular (IM) injection (Zhu et al., 1999). Due to its narrow therapeutic range and rapid metabolism (t1/2 α=9.8 min, t1/2 β=247.5 min), Hup A is required to be administered frequently, which not only causes undesirable fluctuation in plasma concentration and probably leads to gastrointestinal side effects such as anorexia, but also brings bad inconvenience in its clinical use (Wang et al., 2007). On the other hand, the IM injection has quite a few side effects, for instance, pain, inconvenience, short curative effect, vascular injury, muscle contracture, nerve damage, and injections site adverse reactions.

As one of the novel drug delivery systems developed recently, transdermal microneedles are capable to deliver drugs by penetrating the skin barrier, the stratum corneum, to improve the overall efficacy of such drugs, to avoid the gastric irritation, to eliminate first-pass metabolism, and to obtain a sustained-release (van der Maaden et al., 2012; Ye, 2018). Currently, five types of microneedles (solid, coating, hollow, hydrogel-forming (Eltayib et al., 2016), and dissolving) have been designed and characterized in depth (van der Maaden et al., 2012), and dissolving microneedle is considered as the safest transdermal delivery system mainly because of the biodegradation and biocompatibility of the utilized needle materials (Pérennès et al., 2006; Park et al., 2016; Choi et al., 2018; Ronnander et al., 2018). Practically, water soluble polymers such as polyvinyl pyrrolidone (PVP) (Li et al., 2020), polyvinyl alcohol (PVA) (Zhang et al., 2020), sodium carboxymethyl cellulose (CMC-Na) (Ono et al., 2017), are commonly applied as appropriate materials for dissolving microneedles. Particularly, sodium hyaluronate (HA) (Kim et al., 2020) is an ideal candidate with the most popularity due to its distinct properties of biocompatibility, biodegradability, non-immunogenicity and frequently used for microneedle manufacturing (Du et al., 2011; Leone et al., 2020; Wang et al., 2020). In a word, the HA dissolving microneedle technology combines the advantages (accurate, convenient, and efficient) of traditional injection and transdermal delivery routes. Meanwhile, disadvantages caused by the syringes can also be avoided, such as the feeling of pain, potential environmental pollution, and the safety risks (Kim et al., 2012).

The present study aims to design and prepare a dissolving microneedle patch (DMNP) to transdermally deliver Hup A, and to evaluate the in vitro drug release profiles and in vivo pharmacokinetics as well as pharmacodynamics for treating AD.

2. Materials and methods

2.1. Materials

Polydimethylsiloxane (PDMS, Sylgard 184) was purchased from Dow Corning (Midland, MI). Sodium hyaluronate (750–1000 kDa) was purchased from Lifecore Biomedical (Chaska, MN). Huperzine A powder (Hup A, Mw=242.32, log p = 2.70, 99.6% purity, particle size = 120–150 μm) and huperzine B (Hup B, 99.6% purity) were purchased from Zhejiang Wanbang Co., Ltd. (Taizhou, China). Acetylcholine (ACh), superoxide dismutase (SOD), and malondialdehyde (MDA) kits were purchased from Nanjing Jiancheng Biotechnology Institute (Nanjing, China). All other chemicals and solvents were analytical reagent grade.

2.2. Animals

Eight weeks old SD rats, 260 ± 15 g, were supplied by the Zhejiang Academy of Medical Sciences (Hangzhou, China). Rats were housed at a temperature range from 20 °C to 25 °C and humidity range from 50% to 60%, and they were fed with commercial aseptic food. All studies were reviewed and approved by the Institutional Animal Care and Use Committee at Zhejiang University of Technology.

2.3. Methods

2.3.1. Fabrication and mechanical properties of the DMNP

DMNP was fabricated by the micromolding technology as described with some modifications (Chen et al., 2017; Yan et al., 2017). In this work, HA powder was dissolved by distilled water in Eppendorf tubes with rotation at 25 °C for two days at a Four-Dimensional Rotating Mixer (Kylin-Bell Lab Instruments BE-100, Haimen, China), 15% (w/v) HA gel for the needles preparation and 10% (w/v) HA gel for the patch preparation. The PDMS mold was used to fabricate a patch of conical microneedles (6 × 6) with a height of 500 μm, a tip diameter of 20 μm and a base diameter of 250 μm. The 15% HA gel was added into the mold and centrifuged to fabricate the needles with cavities as reported before (Chen et al., 2017). After dried at room temperatures for overnight, the Hup A powder was loaded into the microneedles base material and cavities by a two-step sandwich (Figure 1), the 10% HA gel was put in the mold to form the patch under centrifugation.

Figure 1.

Figure 1.

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Schematic illustration of Hup A-HA microneedles preparation process.

For the qualitative investigation to the hardness of the needles, weights of 50 g, 100 g, 150 g, and 250 g were placed by using a tweezer on top of the formed 4 × 5 DMNPs for 1 min, respectively. After the weights were removed, the deformation of the microneedles was observed by a microscope.

In order to quantitatively test the mechanical properties of the needles, the compression method by texture analyzer (TA.XT Plus, SMS, Godalming, UK) was applied (Dillon et al., 2017). The DMNP with four microneedles (2 × 2) was attached by tape to the movable probe of the analyzer, with the moving speed of 0.1 mm/s, the trigger force of 0.04 N, and the data acquisition rate of 25 pps. The force and displacement were measured and recorded when the uppermost tip of DMNP touched the platform.

2.3.2. Intradermal dissolution, skin penetration of the blank DMNP and skin irritation test of DMNP

To study the skin penetration ability of the DMNP, the blank DMNP was punctured on the abdomen skin of the anesthetized SD rat without hair for 1 min. Then, the rat was sacrificed to dissect the injection site of the skin. After the procedure of fixing and staining by hematoxylin and eosin (H&E), the histological skin slides were scanned and analyzed by a microscopy (Leica DM2500, Wetzlar‎, Germany). The acute irritation test of 5 min treatment by the blank DMNP was also assessed in vivo. The state of skin recovery was monitored until the microholes on the skin became nearly invisible to the naked eye. Photographs were received before administration and at 0, 15, 30, 45, 60, 90, 120, 150, and 180 s after administration by a camera. The skin irritation of 24 h DMNP-treated was also recorded by a camera.

In order to investigate the dissolution of the microneedle after penetration into the skin, the blank DMNPs were punctured on the abdomen skin of the anesthetized SD rat without hair, removed after 3 min and 5 min to observe the in vivo dissolution of the microneedles by microscope (Olympus SZ-61, Shinjuku City, Japan).

2.3.3. The methods for quantitation of Hup A in DMNP and in serum

Hup A (1 mg) dry powder was added into the cavities of the microneedles as described in section 2.3.1 and enclosed by the 10% HA as the patch (Yan et al., 2017). Hup A in DMNP was analyzed by the method of high-performance liquid chromatography (HPLC). Hup A was dissolved in 5 mL of phosphate buffer, filtered through a 0.45 μm microporous membrane filter, and 20 μL of the filtrate was injected into the HPLC system (Dionex U3000, Lohmar, Germany), with UV detection at 307 nm. The mobile phase consisted of a mixture of acetonitrile and 0.01 M potassium dihydrogen phosphate buffer (10:90, v/v), with a flow rate of 1 mL/min. The column temperature was maintained at 25 °C.

Hup A concentrations in serum were measured by liquid chromatography–mass spectrometry (LC–MS) method (Wang et al., 2004) using LC–MS system (Waters Xevo TQ-S micro, Milford, MA). Chromatographic separation was performed on an ACQUITY UPLC HSS T3 C18 column (1.8 µm particle size, 100 mm × 2.1 mm, Waters, Milford, MA), with acetonitrile–0.1% aqueous formic acid (60:40, v/v) at a flow rate of 2.0 µL/min. Desolvation temperature was set to 350 °C, and 500 L/h nitrogen was used to remove the solvent. The positive ion multiple reaction monitoring (MRM) was used to detect Hup A and Hup B (as an internal standard) with the selected transitions of m/z 243.3 → 226.2 and m/z 257.3 → 198.2, respectively.

2.3.4. In vitro release of Hup A in DMNP

In this study, a modified Franz diffusion cell (Migdadi et al., 2018; Gao et al., 2019; Chen et al., 2020) was used to study the permeability of 1 mg Hup A delivered by microneedle through the abdomen skin of SD rat. The 10% HA mixed with 1 mg Hup A was prepared to be the patch layer as a control group, by the same procedure as mentioned in section 2.3.1. Skin samples obtained from healthy rats with the removal of subcutaneous fat were trimmed to a suitable size with surgical scissors, to fix on a diffusion cell. DMNP-Hup A was punctured into the skin as the test group, while the patch layer loaded with Hup A was applied directly on the skin. Physiological saline was used as a receptor medium, and the temperature was kept at 37 ± 3 °C, with stirring at a constant rate of 500 rpm. All receiving chamber fluids were withdrawn at appropriate intervals and then supplemented with an equivalent amount of physiological saline. The samples were assayed by HPLC after filtered through a 0.45 μm filter.

2.3.5. Pharmacokinetic analysis

Eighteen SD rats were allowed to acclimatize for seven days prior to experimentation. The flank hair of the rats was removed after anesthetized. They were divided into three groups of six rats each: (a) one group received oral administration of Hup A and (b) two groups received DMNP administration of Hup A with a different dosage. For the oral group, 0.5 mg Hup A solution was inserted into the stomach using oral gavage (ig). For the DMNP groups, DMNP-Hup A with a drug loading of 0.5 mg (a half patch, 3 × 6) and 1 mg (a single patch, 6 × 6) were then respectively applied and stuck to the naked flank skin with adhesive tapes (3M Transpore tapes, 3M Healthcare, Loughborough, UK). Blood samples were taken from the orbital sinus at pre-defined time intervals: 0, 1, 2, 3, 4, 6, 8, 12, and 24 h with 1 mL collected at each sampling point. To separate plasma from the blood, the tubes were centrifuged at 3000 relative centrifugal force (RCF) for 5 min at 4 °C. 0.5 mL of plasma was subsequently aliquoted into 1.5 mL Eppendorf tubes and stored at −40 °C until used.

Prior to analysis, frozen samples were thawed at 37 °C in a water bath and vortexed briefly. For the analysis, 20 μL internal standard of Hup A methanol solution (1 μg/mL), 100 μL sodium hydroxide solution (1 mol/L), and 5 mL re-distilled dichloromethane solution were added into the samples. After centrifugation at 5500 rpm for 10 min and vortex mixing for 5 min, the organic phase was transferred to another glass tube and evaporated to dryness at 40 °C under a gentle stream of nitrogen. The residue was reconstituted in 100 μL methanol, and centrifugation at 10,000 rpm for 5 min, then the supernatant was collected and injected into the LC–MS system. The separation was performed using a Waters HSS T3 column (100 mm × 2.1 mm, 1.8 μm) in an AcquityTM ultra performance liquid chromatography (UPLC) system. Acetonitrile and water containing 0.1% of formic acid (60:40 v/v) were used as mobile phase A and mobile phase B, respectively. The flow rate was 2.0 μL/min. The temperature for the column was 30 °C. The analyte was quantified using a Waters XEVO TQ-S micro triple quadrupole mass spectrometer equipped with an electro-spray ionization (ESI) source. Multiple reactions monitoring (MRM) scan type was used in the positive scan mode to increase the specificity of the analysis.

2.3.6. Pharmacodynamic evaluation

In this work, the Morris water maze test was used to investigate the effects of Hup A-DMNP on the acquisition and memory impairments (Vorhees & Williams, 2006). The qualified SD rats were randomly divided into four groups (six rats per group), and given the following treatment daily for 11 days: (1) the microneedle group was given DMNP-Hup A (half patch, 3 × 6, containing 0.5 mg Hup A) per rat, once a day (2) the oral group was given 1 mL Hup A (0.5 mg/mL) orally per rat, once a day, (3) the model group and (4) the control group were given 1 mL physiological saline orally (ig), once a day, respectively.

Since the 6th day, the rats were trained under the conditions of the platform to familiarize themselves with the pool environment. Then the positioning navigation test was carried out four times a day lasting for six days. Briefly, the rats were placed in the water facing the pool wall at one of four selected starting points (northwest, northeast, southwest, and southeast pole), and had to learn a new location of the submerged platform within 120 s. On the 11th day, the injection of scopolamine hydrobromide (1 mg/kg, ip) was performed 30 min after the daily treatment, except for the control group, to create a short-time memory defect AD model (Wang et al., 2007). Forty-five minutes later, a four-quadrant water maze test was performed to record the escape latency (Dhingra & Soni, 2018).

The experimental rats were sacrificed immediately after the end of the water maze test. The brains were quickly removed and the cerebral cortex was separated on the icebox. After washed by saline solution, the 10% brain homogenate was prepared using 0.9% sodium chloride solution, then centrifuged for 10 min at 3500 rpm (0 °C). Finally, the supernatant was collected for the subsequent kit verification of ACh, SOD, and MDA. The absorbance was recorded at 550, 450, and 532 nm, respectively.

2.3.7. Statistical analysis

Data were analyzed by one-way ANOVA among multiple groups or a Student's t-test between two groups with Prism Graph Pad software (Graph-Pad Software, La Jolla, CA). A value of p< 0.05 was considered statistically significant.

Pharmacokinetic data analysis was performed using a non-compartmental method, i.e. statistical moment analysis, and all pharmacokinetic parameters were calculated using the Drug and Statistic (DAS) 2.0 pharmacokinetic software (Chinese Pharmacological Association, Beijing, China). Parameters of AUC(0–∞) and plasma half-life (t1/2) were calculated and reported. The maximum measured plasma concentrations (Cmax) and the corresponding times (Tmax) were obtained directly from the raw data after the last dose was given.

3. Results and discussion

3.1. The morphology of the blank DMNP

The blank DMNP was observed under the SEM. As shown in Figure 2(A), it was a square patch with 36 needles, of which height was 489 ± 7.64 μm and base diameter was 242 ± 6.03 μm. The shape of the needle was conical, with a smooth surface and a sharp tip (Figure 2(B)).

Figure 2.

Figure 2.

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The morphology of the blank DMNP. (A) The overall appearance of the 6 × 6 DMNP. (B) SEM image of the HA DMNP, with a height of 489 ± 7.64 μm and a base diameter of 242 ± 6.03 μm. Scale bar, 500 μm.

3.2. The mechanical properties of the blank DMNP

For the qualitative investigation to the hardness of the needles, the weight-bearing experiment was carried on. 50 g, 150 g, and 250 g tweezers were placed on the 4 × 5 DMNPs respectively for 1 min. As shown in Figure 3(A), the shape of microneedles scarcely changed under the weight of 50 g, and still maintained the upright state when the weight was 150 g. While under the weight of 250 g, which force can be calculated to 0.12 N/Needle, all microneedles were nearly half bending. However, no broken fragments were observed, showing excellent hardness and flexibility of the DMNP.

Figure 3.

Figure 3.

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The mechanical properties of the blank DMNP. (A) Morphological changes of DMNP (4 × 5) loaded with different mass weights (0, 50, 150, and 250 g). Scale bar, 500 μm. (B) Representative pressure-displacement curve of the DMNP (2 × 2) measured by texture analyzer.

The compression method by texture analyzer was applied in order to quantitatively test the mechanical properties of the needles. From the experimental results as shown in Figure 3(B), the force was almost linear up to 0.38 N/Needle with displacement at 420 μm till the microneedle was broken, while the displacement was 170 μm at the force of 0.12 N/Needle, which was corresponded with the qualitative investigation result as mentioned above. According to the previous study, a force of 150 mN/Needle was needed to penetrate human skin for microneedle with a tip diameter of 24 μm (Yu et al., 2017). Thus, the DMNP in this study should have enough mechanical strength for transdermal delivery of Hup A.

3.3. Skin penetration, intradermal dissolution of the blank DMNP, and skin irritation test of blank DMNP

The DMNP could be pierced through the rat epidermis as confirmed histologically, with the depth of more than 200 μm (Figure 4(A)), which demonstrated the drugs loaded in the DMNP could be delivered into skin effectively. As shown in Figure 4(B), the tip of the DMNP was half dissolved in 3 min and disappeared after 5 min, which represented the DMNP here could be quickly dissolved and successfully release its cargo in 5 min. As shown in Figure 4(C1), the puncture marks gradually disappeared over time and the spots on skin finally became invisible 180 s later. After 24 h DMNP-treated, no obvious erythema and swelling were occurred. Those results indicated that the prolonged adherence did not cause severe inflammation for the reason that the microneedle materials (HA) possess a satisfactory biocompatibility, yet did cause a little redness resulted from the used bandage, which would be replaced with a more suitable material in our further studies.

Figure 4.

Figure 4.

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Skin penetration and intradermal dissolution of the blank DMNP. (A) Histological skin sections were prepared after insertion of DMNP to show skin penetration, scale bar, 200 μm. (B) The morphology of DMNP taken out from the rat skin at different time intervals after penetration, scale bar, 500 μm. (C) Images of DMNP-treated rats dorsal skin (C1, at different time intervals; C2, after 24 h DMNP-treated), scale, 5 mm.

3.4. In vitro transdermal release profile of Hup A

The Hup A was loaded in both the tip portion and the backing layer of the DMNP, which dramatically increased the drug loading and prolonged the release of the drug. As shown in Figure 5(A), notably, Hup A in DMNP performed an initial sharp burst release in the first 12 h, followed by a moderate release in the following 24 h, and stabilized gradually in the last 36 h. A set of interacting phenomena could explain this result as previously reported (Chen et al., 2013). When DMNP were inserted into the skin, Hup A located in the tip portion of DMNP may be rapidly dissolved by skin interstitial fluid, resulting in the initial burst release and the HA-induced hydration of the epidermis, which could contribute to drug retention in the skin and slow down the permeation process (Brown & Jones, 2005). Subsequently, Hup A located in the backing layer of DMNP may gradually diffuse from the HA matrix, as well as the poor solubility of the Hup A in skin, providing sustained release for nearly three days. During this period, approximately 80% of the Hup A was cumulatively released, in contrast, Hup A in the control group (loaded in patch layer) showed a poor release profile with nearly 5% cumulative release in three days. The in vitro release result clearly indicated that HA could be a suitable material for sustained release of Hup A, and DMNP could significantly improve the permeation rate of the transdermal delivery of Hup A.

Figure 5.

Figure 5.

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In vitro and in vivo transdermal release profile of Hup A. (A) In vitro cumulative permeation curve of Hup A (1 mg) loaded in patch layer and DMNP, which were measured by a modified Franz diffusion cell. (B) In vivo release curve of Hup A by different routes and dosages in rats. Data are expressed as the mean ± SD (n = 6).

3.5. Pharmacokinetic analysis

The concentration of Hup A in the plasma samples was detected with a validated HPLC–MS method (Wang et al., 2004). The main pharmacokinetic parameters of Hup A after being given ig and td are shown in Table 1. Compared with oral administration of the same dose of Hup A (0.5 mg), the DMNP group resulted in longer Tmax (twofold), longer t1/2 (fivefold), lower Cmax (3:4), and larger AUC(0–∞) (twofold). When considering the dosage factor, there were no significant discrepancies in the data of Tmax and t1/2 between the low and high dose groups (p> 0.05), while the values of Cmax and AUC(0–∞) from different groups were dose-related. As shown in Figure 5(B), the mean Hup A serum concentrations increased during the first 6 h after the administration of DMNPs, then reached the mean maximum concentrations, and decreased steadily in the next 18 h. Due to the continued absorption of Hup A in skin from the DMNP groups, a slower rate of disappearance was performed than the oral groups. Compared to previous studies, which focused on the oral administration (Peng et al., 2019) and injection (Chu et al., 2006), respectively, the HA DMNP proposed by the present study is more advantageous which not only produced a higher bioavailability but also accomplished a sustained release with the strategy of the DMNP.

Table 1.

Pharmacokinetic parameters after different administration routes of Hup A in rats.

Parameters Oral (0.5 mg) DMNP (0.5 mg) DMNP (1 mg)
Cmax (ng/mL) 8.48 ± 0.91 5.53 ± 0.53 11.70 ± 0.96
Tmax (h) 3.00 ± 0 6.00 ± 0 6.00 ± 0
t1/2 (h) 3.44 ± 0.40 15.21 ± 2.09 14.32 ± 0.75
AUC(0–∞) (ng·h/mL) 53.32 ± 8.73 110.88 ± 17.95 209.59 ± 18.83
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Mean ± SD, n = 6.

One common disadvantage of the traditional transdermal system is the low bioavailability. Therefore, sufficient medicine is required as the penetration force, and a large amount of the medicine still remains after wearing (Ye et al., 2008; Wu et al., 2011; Amjadi et al., 2018; Lee & Prausnitz, 2018). Results in this study indicated that DMNP can prolong the elimination of t1/2 and enlarge the area under the curve (AUC), presenting a higher relative bioavailability value than that of oral administration. Combining with our previous research findings (Chen et al., 2017), it can be concluded that dissolving microneedle technology has the advantages of delivering drugs into the skin interstitial fluid with a controlled and continuous release, reducing the frequency of administration, and improving the compliance of patients, which are very important to these drugs of short half-life.

3.6. Pharmacodynamic evaluation

The learning and memory performances in different groups were assessed by the Morris water maze task. As shown in Figure 6(A), positioning navigation test (day 6 to day 10) showed that as the number of training days increased, the escape latency of each group gradually decreased, indicating that each group of rats has gradually learned to find a platform in learning and training. There was no significant discrepancy in learning and memory between any of the groups. On the 11th day, rats were injected intraperitoneally with scopolamine hydrobromide to establish a short-time memory deficit model. Forty-five minutes later, the positioning navigation test (11th day) was performed. Figure 6(B) illuminates that a significant discrepancy of escape latency between the following groups: Control vs. Model (p < 0.0001), Oral-Hup A and DMNP-Hup A vs. Model (p < 0.001), indicating that the rat's multiple memory-related behaviors were affected after intraperitoneal injection of scopolamine hydrobromide, and the treatment of Hup A in oral as well as in DMNP way could partially reverse the memory deficit with no significant discrepancy (p > 0.05). Likewise, according to Figure 6(C), the typical swimming tracks indicated that the rats in Model groups often searched the platform in an inappropriate manner, resulting in a longer latency for the positioning platform than the other groups, and the DMNP-Hup A group had the similar effect as the Oral-Hup A group.

Figure 6.

Figure 6.

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Investigation of animal behavior in different groups. (A) Escape latency in the Morris water maze test on different training days. (B) Escape latency after modeling in different experimental groups. (C) Representative swim paths. Data are expressed as the mean ± SD (n = 6). ***p< 0.001, ****p< 0.0005, and NS, no significance.

As is well known, ACh is a cholinergic neurotransmitter that participates in information transmission and processing. Numerous studies have confirmed that enhancing ACh content can improve cognitive impairment in rats with dementia (Foyet et al., 2015; Perez-Lloret & Barrantes, 2016). In addition, oxidative damage of biomacromolecules such as lipoprotein in the cellular membranes is always related to oxidative stress. Elevated MDA is considered to be a specific indicator of lipid peroxidation during oxidative damage (Tsikas, 2017). Moreover, oxidative damage can also destroy the antioxidant defense system, accompanied by decreasing SOD activities. The levels of ACh, SOD, and MDA in different groups from our current work are displayed in Figure 7. As shown in Figure 7(A,B), there was a marked decreasing of ACh content and SOD activity in the Model group (p< 0.01), as compared to the Control, Oral-Hup A, and DMNP-Hup A groups. In contrast, the level of MDA content in the Model group was increased obviously (p< 0.001) with threefold higher than the other groups (Figure 7(C)). These data above illustrated that in the Model group, declining ACh content and oxidative damage (increased MDA content, decreased SOD activities) lead to the cognitive disturbance consistent with Figure 6(C). Finally, the phenomenon was significantly reversed after the treatment of Hup A both in Oral and DMNP ways, with no significance (p> 0.05). Collectively, these findings suggest that dissolving microneedle delivery of Hup A could effectively improve the cognitive impairment in rats with dementia.

Figure 7.

Figure 7.

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Effect of DMNP-Hup A on (A) ACh content, (B) SOD activity, and (C) MDA level in rats. Data are expressed as the mean ± SD (n = 6). **p< .05, ***p< .001, ****p< .0005, and NS, no significance.

Moreover, as the in vitro release profile (Figure 5(A)) showed, about accumulatively 80% of Hup A released in 24 h and then enter a stable phase. It can be speculated that 20% of the 0.5 mg Hup A still remain in the patch, owing to the gaps between microneedles which may prevent this part of the drug from being delivered to the skin. However, DMNP-Hup A can also achieve a satisfactory therapeutic effect with a smaller drug dose and fewer administration times than the oral way.

4. Conclusions

Presently, the marketed pharmaceutical forms of Hup A are tablets, capsules, and im injection. However, frequent administration and potential side effects, such as anorexia, are the main problems in oral routes. On the other hand, the im injection also has quite a few side effects, such as pain, inconvenience, vascular damage, nerve injury, injections site reactions, etc. Transdermal drug delivery strategy with dissolving microneedle is not only capable to significantly improve the bioavailability of the Hup A comparing to its oral administration, but also able to accomplish a desirable sustained release in a painless and minimally invasive manner. This study designed and developed a new strategy to transdermally deliver Hup A by DMNP, with advantages of high-dose Hup A loading, sustained-release, efficient transdermal delivery, and satisfactory therapeutic effect. The data indicated that DMNP-Hup A could clinically penetrate the skin in a minimal invasive, to deliver drugs into the skin interstitial fluid with a controlled and continuous release, and the effect of this method was similar or even better than that achieved using the oral way.

Funding Statement

This work was supported by the Natural Science Foundation of Zhejiang Province [LY20H300005].

Disclosure statement

The author(s) have no conflict of interest to declare.

References

  1. Amjadi M, Sheykhansari S, Nelson BJ, Sitti M. (2018). Recent advances in wearable transdermal delivery systems. Adv Mater 30:1–19. [DOI] [PubMed] [Google Scholar]
  2. Association A. (2017). Alzheimer's disease facts and figures. Alzheimer's Dement 13:325–73. [Google Scholar]
  3. Association A. (2018). Alzheimer's disease facts and figures. Alzheimer's Dement 14:367–429. [Google Scholar]
  4. Brown MB, Jones SA. (2005). Hyaluronic acid: a unique topical vehicle for the localized delivery of drugs to the skin. J Eur Acad Dermatol Venereol 19:308–18. [DOI] [PubMed] [Google Scholar]
  5. Chen F, Yan Q, Yu Y, Wu MX. (2017). BCG vaccine powder-laden and dissolvable microneedle arrays for lesion-free vaccination. J Control Release 255:36–44. [DOI] [PMC free article] [PubMed] [Google Scholar]
  6. Chen M-C, Huang S-F, Lai K-Y, Ling M-H. (2013). Fully embeddable chitosan microneedles as a sustained release depot for intradermal vaccination. Biomaterials 34:3077–86. [DOI] [PubMed] [Google Scholar]
  7. Chen Y, Yang Y, Xian Y, et al. (2020). Multifunctional graphene-oxide-reinforced dissolvable polymeric microneedles for transdermal drug delivery. ACS Appl Mater Interfaces 12:352–60. [DOI] [PubMed] [Google Scholar]
  8. Choi JT, Park SJ, Park JH. (2018). Microneedles containing cross-linked hyaluronic acid particulates for control of degradation and swelling behaviour after administration into skin. J Drug Target 26:884–94. [DOI] [PubMed] [Google Scholar]
  9. Chu DF, Fu XQ, Liu WH, et al. (2006). Pharmacokinetics and in vitro and in vivo correlation of huperzine A loaded poly(lactic-co-glycolic acid) microspheres in dogs. Int J Pharm 325:116–23. [DOI] [PubMed] [Google Scholar]
  10. Dhingra D, Soni K. (2018). Behavioral and biochemical evidences for nootropic activity of boldine in young and aged mice. Biomed Pharmacother 97:895–904. [DOI] [PubMed] [Google Scholar]
  11. Dillon C, Hughes H, O'Reilly NJ, McLoughlin P. (2017). Formulation and characterisation of dissolving microneedles for the transdermal delivery of therapeutic peptides. Int J Pharm 526:125–136. [DOI] [PubMed] [Google Scholar]
  12. Eltayib E, Brady AJ, Caffarel-Salvador E, et al. (2016). Hydrogel-forming microneedle arrays: potential for use in minimally-invasive lithium monitoring. Eur J Pharm Biopharm 102:123–31. [DOI] [PubMed] [Google Scholar]
  13. Ferreira A, Rodrigues M, Fortuna A, et al. (2016). Huperzine A from Huperzia serrata: a review of its sources, chemistry, pharmacology and toxicology. Phytochem Rev 15:51–85. [Google Scholar]
  14. Foyet HS, Abaissou HHN, Wado E, et al. (2015). Emilia coccinae (SIMS) G extract improves memory impairment, cholinergic dysfunction, and oxidative stress damage in scopolamine-treated rats. BMC Complement Altern Med 15:333. [DOI] [PMC free article] [PubMed] [Google Scholar]
  15. Galimberti D, Scarpini E. (2016). Old and new acetylcholinesterase inhibitors for Alzheimer's disease. Expert Opin Investig Drugs 25:1181–7. [DOI] [PubMed] [Google Scholar]
  16. Gao Y, Hou MM, Yang RH, et al. (2019). Transdermal delivery of therapeutics through dissolvable gelatin/sucrose films coated on PEGDA microneedle arrays with improved skin permeability. J Mater Chem B 7:7515–24. [DOI] [PubMed] [Google Scholar]
  17. Hager K, Marahrens A, Kenklies M, et al. (2001). Alpha-lipoic acid as a new treatment option for Alzheimer type dementia. Arch Gerontol Geriatr 32:275–82. [DOI] [PubMed] [Google Scholar]
  18. Du H, Liu P, Zhu J, et al. (2011). Hyaluronic acid-based dissolving microneedle patch loaded with methotrexate for improved treatment of psoriasis. ACS Appl Mater Inter 11:43588–98. [DOI] [PubMed] [Google Scholar]
  19. Kim DS, Choi JT, Kim CB, et al. (2020). Microneedle array patch (MAP) consisting of crosslinked hyaluronic acid nanoparticles for processability and sustained release. Pharm Res 37:11. [DOI] [PubMed] [Google Scholar]
  20. Kim YC, Park JH, Prausnitz MR. (2012). Microneedles for drug and vaccine delivery. Adv Drug Deliv Rev 64:1547–68. [DOI] [PMC free article] [PubMed] [Google Scholar]
  21. Laicher A, Fuchs WS. (1998). Pellet technology sustained release pellets in hard gelatine capsules – a suitable dosage form for theophylline. Arzneimittelforschung 48:540–7. [PubMed] [Google Scholar]
  22. Lee JW, Prausnitz MR. (2018). Drug delivery using microneedle patches: not just for skin. Taylor & Francis 6:541–543. [DOI] [PubMed] [Google Scholar]
  23. Leone M, Romeijn S, Slütter B, et al. (2020). Hyaluronan molecular weight: effects on dissolution time of dissolving microneedles in the skin and on immunogenicity of antigen. Eur J Pharm Sci 146:105269. [DOI] [PubMed] [Google Scholar]
  24. Li ZL, He YJ, Deng L, et al. (2020). Correction: a fast-dissolving microneedle array loaded with chitosan nanoparticles to evoke systemic immune responses in mice (vol 66, pg 489, 2020). J Mater Chem B 8:578–79. [DOI] [PubMed] [Google Scholar]
  25. Migdadi EM, Courtenay AJ, Tekko IA, et al. (2018). Hydrogel-forming microneedles enhance transdermal delivery of metformin hydrochloride. J Control Release 285:142–51. [DOI] [PMC free article] [PubMed] [Google Scholar]
  26. Nguyen TT, Giau VV, Vo TK. (2017). Current advances in transdermal delivery of drugs for Alzheimer's disease. Indian J Pharmacol 49:145–54. [DOI] [PMC free article] [PubMed] [Google Scholar]
  27. Ono A, Ito S, Sakagami S, et al. (2017). Development of novel faster-dissolving microneedle patches for transcutaneous vaccine delivery. Pharmaceutics 9:27. [DOI] [PMC free article] [PubMed] [Google Scholar]
  28. Park Y-H, Ha SK, Choi I, et al. (2016). Fabrication of degradable carboxymethyl cellulose (CMC) microneedle with laser writing and replica molding process for enhancement of transdermal drug delivery. Biotechnol Bioprocess Eng 21:110–8. [Google Scholar]
  29. Peng T, Shi Y, Zhu C, et al. (2019). Huperzine A loaded multiparticulate disintegrating tablet: drug release mechanism of ethyl cellulose microparticles and pharmacokinetic study. Powder Technol 355:649–56. [Google Scholar]
  30. Pérennès F, Marmiroli B, Matteucci M, et al. (2006). Sharp beveled tip hollow microneedle arrays fabricated by LIGA and 3D soft lithography with polyvinyl alcohol. J Micromech Microeng 16:473–9. [Google Scholar]
  31. Perez-Lloret S, Barrantes FJ. (2016). Deficits in cholinergic neurotransmission and their clinical correlates in Parkinson's disease. NPJ Parkinsons Dis 2:16001. [DOI] [PMC free article] [PubMed] [Google Scholar]
  32. Ronnander P, Simon L, Spilgies H, et al. (2018). Dissolving polyvinylpyrrolidone-based microneedle systems for in-vitro delivery of sumatriptan succinate. Eur J Pharm Sci 114:84–92. [DOI] [PubMed] [Google Scholar]
  33. Selkoe DJ, Hardy J. (2016). The amyloid hypothesis of Alzheimer's disease at 25 years. EMBO Mol Med 8:595–608. [DOI] [PMC free article] [PubMed] [Google Scholar]
  34. Sevigny J, Chiao P, Bussière T, et al. (2016). The antibody aducanumab reduces Aβ plaques in Alzheimer's disease. Nature 537:50–6. [DOI] [PubMed] [Google Scholar]
  35. Tsikas D. (2017). Assessment of lipid peroxidation by measuring malondialdehyde (MDA) and relatives in biological samples: analytical and biological challenges. Anal Biochem 524:13–30. [DOI] [PubMed] [Google Scholar]
  36. van der Maaden K, Jiskoot W, Bouwstra J. (2012). Microneedle technologies for (trans)dermal drug and vaccine delivery. J Control Release 161:645–55. [DOI] [PubMed] [Google Scholar]
  37. Vorhees CV, Williams MT. (2006). Morris water maze: procedures for assessing spatial and related forms of learning and memory. Nat Protoc 1:848–58. [DOI] [PMC free article] [PubMed] [Google Scholar]
  38. Wang C, Zhang T, Ma H, et al. (2007). Prolonged effects of poly(lactic-co-glycolic acid) microsphere-containing huperzine A on mouse memory dysfunction induced by scopolamine. Basic Clin Pharmacol Toxicol 100:190–5. [DOI] [PubMed] [Google Scholar]
  39. Wang M, Han YY, Yu XJ, Liang LL, et al. (2020). Upconversion nanoparticle powered microneedle patches for transdermal delivery of siRNA. Adv Healthc Mater 9:11. [DOI] [PubMed] [Google Scholar]
  40. Wang R, Yan H, Tang XC. (2006). Progress in studies of huperzine A, a natural cholinesterase inhibitor from Chinese herbal medicine. Acta Pharmacol Sin 27:1–26. [DOI] [PubMed] [Google Scholar]
  41. Wang Y, Chu D, Gu J, et al. (2004). Liquid chromatographic–tandem mass spectrometric method for the quantitation of huperzine A in dog plasma. J Chromatogr B Analyt Technol Biomed Life Sci 803:375–8. [DOI] [PubMed] [Google Scholar]
  42. Wu C-L, Wen S-H. (2016). A 10-year follow-up study of the association between calcium channel blocker use and the risk of dementia in elderly hypertensive patients. Medicine 95:e4593. [DOI] [PMC free article] [PubMed] [Google Scholar]
  43. Wu T, Li CY, Chen M, et al. (2011). Clinic pharmacokinetic profiles of huperzine A following transdermal administration to healthy human volunteers. Chromatographia 74:67–73. [Google Scholar]
  44. Xie D, Xie J, Wang J, et al. (2013). Huperzia serrata (Thunb.) Trev. composition comprising compounded Huperzine A and Huperzine B and methods for preparing it. U.S. Patent No. 8,574,633. Washington, DC: U.S. Patent and Trademark Office. [Google Scholar]
  45. Yan Q, Liu H, Cheng Z, et al. (2017). Immunotherapeutic effect of BCG-polysaccharide nucleic acid powder on Mycobacterium tuberculosis-infected mice using microneedle patches. Drug Deliv 24:1648–53. [DOI] [PMC free article] [PubMed] [Google Scholar]
  46. Ye JC, Zeng S, Zheng GL, Chen GS. (2008). Pharmacokinetics of huperzine A after transdermal and oral administration in beagle dogs. Int J Pharm 356:187–92. [DOI] [PubMed] [Google Scholar]
  47. Ye Y, Yu J, Wen D, et al. (2018). Polymeric microneedles for transdermal protein delivery. Advanced drug delivery reviews 127:106–18. [DOI] [PMC free article] [PubMed] [Google Scholar]
  48. Yu W, Jiang G, Liu D, et al. (2017). Fabrication of biodegradable composite microneedles based on calcium sulfate and gelatin for transdermal delivery of insulin. Mater Sci Eng C Mater Biol Appl 71:725–34. [DOI] [PubMed] [Google Scholar]
  49. Zhang XX, Chen GP, Liu YX, et al. (2020). Black phosphorus-loaded separable microneedles as responsive oxygen delivery carriers for wound healing. ACS Nano 14:5901–8. [DOI] [PubMed] [Google Scholar]
  50. Zhang Z, Wang X, Chen Q, et al. (2002). Clinical efficacy and safety of huperzine alpha in treatment of mild to moderate Alzheimer disease, a placebo-controlled, double-blind, randomized trial. Zhonghua Yi Xue Za Zhi 82:941–4. [PubMed] [Google Scholar]
  51. Zheng W, Xiang Y-Q, Ungvari GS, et al. (2016). Huperzine A for treatment of cognitive impairment in major depressive disorder: a systematic review of randomized controlled trials. Shanghai Arch Psychiatry 28:64–71. [DOI] [PMC free article] [PubMed] [Google Scholar]
  52. Zhu X, Gu Y, Wang H. (1999). Comparison of the efficacy between tablet and capsule of huperzine to treat age associated memory impairment by double blind trail method. Chin J Clin Pharm 8:227–9. [Google Scholar]

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