Introduction

Roughly one in six people suffers from various types of neurological disorders across the world, and up to 7 million premature deaths occur each year. Brain diseases affect people’s way of life negatively through seizures which cause irregular behaviors. Millions of people suffer from epilepsy, making it one of the most common types of brain disorders. The current treatment of epilepsy is poor due to the lack of availability of anti-seizure medication and its lack of effectiveness. Current medication has various side effects such as dizziness and difficulties with speech. Utilizing nanotechnological formulations to treat the disorders could lead to a cure for up to 70% of diagnosed patients (Silva, Reference Silva2008; Bennewitz & Saltzman, Reference Bennewitz and Saltzman2009; Bozdağ Pehlivan, Reference Bozdağ Pehlivan2013; World Health Organization [WHO], 2020). Dopamine and gamma-amino-n-butyric acid are brain neurotransmitters that are important when researching brain disorders such as epilepsy; ionomycin allows the calcium response in brain membrane cells to be followed. In the barrier, brain microvascular endothelial cells are the main layer component making a membrane with blood vessels. Endothelial cells account for much of the proteins that deny access to the brain by pathogens and other toxic substances. This barrier also prevents most anti-seizure medications from reaching the brain tissue (Mahringet al., 2013; Lvov et al., Reference Lvov, Wang, Zhang and Fakhrullin2016). Using Hly clay nanotubes helps to penetrate the endothelial cells through a ‘nano torpedo’ approach and effectively delivers the loaded substances over an extended time.

Use of nanotubes that are 50 nm in diameter is effective at penetrating cell membranes due to the small cross-section. In the present case, the tubule penetrability of the materials is defined by their diameters being tens of nanometers rather than by their length – up to a micrometer. This idea allowed introduction of the term ‘nano-torpedo’ drug delivery; it assumes that the most efficient barrier breaking is achieved by close to perpendicular intrusion of the Hly tubes. Halloysite nanotubes are formed by 10–15 revolutions of 0.72 nm-thick aluminosilicate sheets and have diameters ranging between 40 and 60 nm, lumen diameters of 12–15 nm, and are between 500 and 900 nm long (Fig. 1) (Liu et al., Reference Liu, Jia, Jia and Zhou2014; Lvov et al., Reference Lvov, Wang, Zhang and Fakhrullin2016). Halloysite is a natural and cheap nanomaterial, available in large quantities. The outer surfaces of Hly are composed of SiO₂, and the interiors are composed of Al₂O₃, which are oppositely (negative/positive) charged in the pH range of 3–9 (Lazzara et al., Reference Lazzara, Cavallaro, Panchal, Fakhrullin, Stavitskaya, Vinokurov and Lvov2018). The loaded Hly usually has enhanced electrical zeta-potential of –40 to –50 mV allowing for stable aqueous colloids, which is important for the formulated drug injection. The structure of Hly displays how the neurotransmitter can be loaded inside the lumen, which is effective for the adsorption of negatively charged drug molecules. Based on geometrical sizes of Hly, one may conclude that the maximal volume load inside the tubes is 10–12 vol.%, which may reach 15–20 wt.% with adsorption of an external drug (especially a cationic one). This is a typical drug load, as summarized by Santos et al. (Reference Santos, Pereira, Reis, Veiga, Saleh and Lvov2019). Greater drug loading means that drug molecules are adsorbed on the tube external surface, which may change the formulation properties that are observed through zeta-potential and colloidal stability. Thus, inner adsorption of negative molecules usually increases the electrical potential magnitude from ~−30 mV in pristine to –45 to –50 mV in loaded nanotubes (Liu et al., Reference Liu, Jia, Jia and Zhou2014. Drugs such as khellin, oxytetracycline, gentamicin, ciprofloxacin, vancomycin, atorvastatin, metronidazole, dexamethasone, doxorubicin, furosemide, nifedipine, curcumin, resveratrol, povidone, iodine, amoxicillin, brilliant green, chlorhexidine, and DNA and viral genes were loaded successfully in Hly (Santos et al., Reference Santos, Pereira, Reis, Veiga, Saleh and Lvov2019).

Fig. 1. a TEM and b SEM images of Hly, and c a schematic image of a rolled clay tube

Halloysite is a biocompatible material with low-toxicity assessments (Dzamukova et al., Reference Dzamukova, Naumenko, Rozhina, Trifonov and Fakhrullin2015b; Fakhrullina et al., Reference Fakhrullina, Khakimova, Akhatova, Lazzara, Parisi and Fakhrullin2019; Hu et al., Reference Hu, Chen, Li, Sun, Huang, Li, Liu, Xu and Zhong2017; Kamalieva et al., Reference Kamalieva, Ishmukhametov, Batasheva, Rozhina and Fakhrullin2018; Kruchkova et al., Reference Kruchkova, Danilushkina, Lvov and Fakhrullin2016; Mehdia et al., Reference Mehdia, Fizira, Itatahinea, Hea and Dramoua2018; Vergaro et al., Reference Vergaro, Abdullayev, Lvov, Zeitoun, Cingolani, Rinaldi and Leporatti2010; Wang et al., Reference Wang, Gong, Gui, Hu and Xu2018; Zhao et al., Reference Zhao, Wan, Fu, Meng, Ou, Zhong, Zhou and Liu2019). Researchers reached a consensus that these clay nanotubes are safe at levels of up to 0.5 mg/mL, which is less toxic than common table salt (Vergaro et al., Reference Vergaro, Abdullayev, Lvov, Zeitoun, Cingolani, Rinaldi and Leporatti2010). This was tested on in vitro and in vivo systems: cell lines, microworms, infusoria, fishes, mice, and rats (Santos et al., Reference Santos, Pereira, Reis, Veiga, Saleh and Lvov2019). The only minor toxic effect was found with significant oral consumption of Hly when acidic clay decomposed in the stomach and increased Al³⁺ accumulation (Kamalieva et al., Reference Kamalieva, Ishmukhametov, Batasheva, Rozhina and Fakhrullin2018). The mice that were fed orally with small nanoclay doses (5 mg/kg of mouse weight, which corresponds to a daily consumption of 3 g of Hly for adult humans for 1 month) showed no oxidative stress or other toxicity signs and even demonstrated greater growth rates. Clay nanotubes loaded with drugs will penetrate cells more efficiently than spherical particles of the same mass (Dzamukova et al., Reference Dzamukova, Naumenko, Badrutdinov, Lvov and Fakhrullin2015a; Wang et al., Reference Wang, Gong, Gui, Hu and Xu2018). This approach allowed for effective delivery by Hly of doxorubicin and other anticancer drugs (Dzamukova et al., Reference Dzamukova, Naumenko, Badrutdinov, Lvov and Fakhrullin2015a; Yang et al., Reference Yang, Wu, Shen, Zhou, Li, He and Liu2016; Zhang et al., Reference Zhang, Luo, Wu, Wu, Li, He and Liu2019).

In the current work, the penetration of Hly nanotubes into primary rat endothelial cells (BMVECs), the main cell types which prevent the entry of drugs through the blood–brain barrier, were studied (Prajapati et al., Reference Prajapati, Karan, Khezerlou and DeCoster2021; Prajapati & DeCoster, Reference Prajapati and DeCoster2020; Rodrigues et al., Reference Rodrigues, Prajapati, DeCoster, Poh and Murray2021; Vivès et al., Reference Vivès, Schmidt and Pèlegrin2008). In addition, a model was developed showing the interaction of tagged Hly with the endothelial lining by layering the cells on a porous membrane in transwell inserts. This was done using fluorescent rhodamine isothiocyanate dye, where Hly binds on the cell, penetrates the cell interior, concentrates around the nuclei, and may deliver a drug load. The Hly/brilliant green formulations with intracellular delivery allowed the preferable elimination of human lung carcinoma cells (A-549) as compared with hepatoma cells due to different intracellular penetration (Dzamukova et al., Reference Dzamukova, Naumenko, Badrutdinov, Lvov and Fakhrullin2015a).

The transwell assay is used widely to study the absorption in the intestine of molecules administered orally (Artursson, Reference Artursson1991; Artursson et al., Reference Artursson, Palm and Luthman2001; Hubatsch et al., Reference Hubatsch, Ragnarsson and Artursson2007; Stenberg et al., Reference Stenberg, Norinder, Luthman and Artursson2001). The development of an in vivo membrane system to mimic in vitro and analyze the transport of loaded Hly tubes across the model (endothelial and astrocyte cells) blood–brain barrier was challenging. Transwell inserts were utilized with a porous polycarbonate membrane which acts as a chamber where a confluent layer is formed on top of astrocytes. The membrane nanotube permeability and the ability to visualize the multilayered cells were realized through non-inverted confocal microscopy (Fig. 2).

Fig. 2. A co-culture model of brain endothelium and astrocyte membrane developed for testing the penetration and delivery of Hly nanotubes and their payload (RITC) across the blood–brain barrier model

Throughout these experiments, the penetration of Hly nanotubes into rat brain microvasculature was analyzed within and outwith the endothelial cells, which are the primary defenders of the brain tissue. Tagging the nanotubes with fluorescent rhodamine B isothiocyanate (RITC) illustrated the ability of Hly to bind to and penetrate the endothelial cell membrane while delivering the payload. Halloysite nanotube formulations can, therefore, be effective carriers for various drugs and neurotransmitters for treating brain diseases. The development of a model for the blood–brain barrier is illustrated in Fig. 1 which shows how a cell insert is used with a porous membrane, attaching one layer of endothelial cells on top of a layer of astrocytes and displaying how the Hly is binding and passing through the model barrier by tagging them with the RITC dye and ionomycin drug. The hypothesis is that Hly tubes acted as ‘nano-torpedoes’ penetrating the blood–brain barrier and releasing the drug load in a sustained manner. The layer-by-layer construction of the two-type cell model of the blood–brain barrier on transwell inserts was effective at displaying RITC-loaded Hly binding to and penetrating the cell membranes.

RESULTS AND DISCUSSION

Intracellular Rhodamine Isothiocyanate Delivery with Hly Nanotubes

Halloysite nanotubes are very capable of encapsulating, transporting, and slowly releasing the dye or drugs. Note that the surface of the Hly was not modifiedwith any type of polymer or silane coating. The penetration of the fluorescent RITC-loaded Hly into the layer of endothelial cells is shown in Fig. 3. The timeframe of the images is 4 and 24 h after release of the payload, for Hly + RITC and 2 μg/mL of RITC alone. The loading formulation of RITC in Hly was 20 wt.%, thus making the same amount added to the samples. The small bright dots found in the images of Fig. 3c are the aggregated Hly tubes that contain RITC. After 4 h, Hly-RITC aggregations were displayed mostly along the cellular membrane and inside the endothelial cells; those are indicated by nuclear exclusion. An image of only RITC added, and at the same concentration, is given in Fig. 3e–f, displaying a much dimmer visualization of the cell’s interaction with this non-encapsulated dye.

Fig. 3. Endothelial cells-BMVEC treated with Hly loaded with RITC after displaying fluorescence and direct images in time frames of: a, b and e, f 4 h; c, d and g, h 24 h phase, magnification. Positive controls; BMVECs treated with non-encapsulated rhodamine after 4 h: e,f fluorescence and direct images; g, h the same after a 24 h phase. i,j images are negative controls with unlabeled Hly. Direct phase and fluorescence microscopic imaging of primary endothelial cells that were treated with Hly only. Scale bars: 100 μm

Results for the 24 h treatment were similar with brighter fluorescence in both conditions but RITC-loaded Hly delivered more dye into the cells compared to the dye alone (Fig. 3). Images taken after 24 h displayed the nanotube distribution more evenly over the cell interior and within the cell body. The RITC-Hly was seen to be concentrated in smaller spots of ~1 μm, which may be the nuclear surroundings, as was found for MCF-7 cells treated with Hly (Vergaro et al., Reference Vergaro, Abdullayev, Lvov, Zeitoun, Cingolani, Rinaldi and Leporatti2010). Throughout the experiments, detection of nuclear exclusion through the use of fluoresence displayed cells, indicating that the nanotubes did not stress or kill the cells. The nanoclays appear as small dots in Fig. 3c and are brighter than the non-encapsulated dye spread inside the cells. Displaying localized nanotubes with red dye in the cell cytoplasm with a distinct nuclear exclusion shows a greater binding. Hly-RITC cells showed significant fluorescence, indicating a prolonged delivery of the dye from the nanotubes.The cells treated with Hly nanotubes alone (negative controls) showed no fluorescence (Fig. 3c,d and g,h).

Thermogravimetric Analysis, TGA

Thermogravimetric analysis was used to determine the sample's weight change during the component burning (Fig. 4) and demonstrated that the material or substance was loaded inside the nanotubes and gave an approximate percentage of the amount loaded. The TGA analysis (Thermal Advantage Q50, New Castle, Delaware, USA) was done using pristine Hly with a major phase transition at 490°C, with some nanotubes loaded with RITC, and others loaded with ionomycin. The difference in mass decrease during heating between pristine and loaded Hly (Fig. 4a–c) gave an estimated RITC loading of 5 ± 1 wt.%. A similar analysis for ionomycin drug loading into the nanotubes gave values of 14 ± 1 wt.%, indicating some external drug attachment. The results showed that, compared to pristine Hly, an ionomycin loading of ~8 wt.% was achieved.

Fig. 4. Thermogravimetric curves of pristine Hly, Hly loaded with rhodamine, and Hly loaded with ionomycin.

Hly Loaded Release Profile

The loaded Hly samples that were used to treat the endothelial cells were tested for RITC release kinetics (Fig. 5). This displays the rate at which the dye is released over a period of 24 h. The results showed that rhodamine is released in an initial burst of ~25% within the first 1 h, which is an expected characteristic when utilizing Hly nanocontainers. This caused no stress to the endothelial cells. During a further period, the advantages of Hly tubes began to become apparent, i.e. by releasing the dye slowly over a period of 24 h at a steady rate (releasing the remaining 75% over the next 23 h). The delivery process avoids major spikes that could stress or kill the cells. The nanotubes penetrated cell nuclei during the initial 4 h experiment in Fig. 3a,b,e,f. The red dots which represent the loaded Hly were confined within the cells; although they are extremely dim in these pictures, the visualization of drug release begins.

Fig. 5. Release profile of rhodamine isothiocyanate-RITC loaded into Hly taken at 555 nm

Hly-loaded Ionomycin: Calcium Imaging

A good method to visualize ionomycin-loaded HNT is the calcium response (Saleh et al., Reference Saleh, Prajapati, DeCoster and Lvov2020). With real-time calcium imaging, the cell's response to ionomycin had a spiked increase in Ca²⁺ which decayed quickly due to clearance by cells. When Hly was used alone, the response was small (Fig. 6a). When ionomycin was loaded inside the tubules, achieving a greater response of Ca²⁺ for the same concentration of 1 μM (the bright blue color represents the cells responding to the ionophore) that was also used resulting in a gradual increase in calcium which remained higher for a greater period of time. This experiment also showed that the introduction of Hly maintained a stable and slow release of drug over 4 h without stressing the cells.

Fig. 6. Images captured for endothelial cells-BMVECs during Ca²⁺ treatment: a peak stimulation by 50 μg/mL of empty Hly nanotube, and b peak stimulation by 50 μg/mL nanotubes loaded with ionomycin.

Co-culture Studies of Blood–Brain Barrier

The confluence of the bilayer of astrocyte and endothelial cells was examined using a non-inverted microscope after Diff-Quik staining of the cells (Fig. 7a). When a continuous monolayer was ensured, the additional cells were examined using non-inverted confocal microscopy to indicate the two cells assay (Fig. 8b,c– both astrocyte and endothelial), based on the cell dimensions that have been seen on two distinct planes (0.3 μm step in the z-axis). The co-culture model of endothelial and astrocyte cells was, thus, produced. This represented a simulated brain barrier microenvironment where these two cell types (endothelial which are brain cells that make up the vascular structure and astrocytes, one of the main structural cells), are present in the complex layer holding the glial cells and neurons together.

Fig. 7. DiffQuik-stained images of a model brain barrier of aco-cultured endothelial astrocytes plated on a porous membrane. b, c (z-stack images with a 0.3 μm step size) of non-inverted microscopy images of the transwell assay with a layer of b astrocytes and c endothelial cells

Fig. 8. Controls a20μg/mL HLy-RITC fluorescence intensity (no cell inserts, direct addition to the bottom well), b20μg/mL HLy-RITC added to the support, and c membrane support treated with media alone

Passage of RITC through the Co-culture Model

The fluorescent intensity of the endothelial and astrocyte bilayer as well as images of solution beneath the cell inserts after the treatment with ‘nano-torpedo’ clay formulations are shown in Fig. 8, part a of which displays the dispersion of RITC-loaded Hly without the cell membrane. The intensity of rhodamine that is released by Hly after passing through the transmembrane for 4 h is shown in Fig. 8b. A negative control where the media alone is present, i.e. no Hly or rhodamine, is shown in Fig. 8c– no fluorescence signal was observed. Understanding the function of the transmembrane which allows the gradual passage of the rhodamine and partial passage of Hly in some cases, was one of the main purposes of the present study.

The treatment conditions were as follows: 20 μg/mL Hly-RITC formulations were placed on top of the well with the designed bi-cell membrane for an analysis of a time-dependent passage of a rhodamine nano-torpedo through the co-culture barrier model membrane over a period of 24 h. The RITC fluorescence intensity under the membrane increased significantly from the 4-h to the 24-h treatment time, indicating penetration by the Hly carrier. The fluorescence signal grew moderately in the first hour but by 24 h it had increased to 85%. Some decrease in the fluorescence intensity at the 4-h time point occurred because the co-culture cell membrane absorbed some of the upcoming rhodamine but further passing enhanced the signal growth beneath the model barrier (Fig. 9a,b). The Hly nanotubes being utilized in drug delivery were probably as efficient as this because of the predominantly vertical penetration through the cell membrane. An MTT assay was performed 24 h after treatment of the cells plated at 10,000 per mL when they reached 60% confluency to assess cell metabolism as the measure of cytotoxicity (Fig. 9c).

Fig. 9. Results of Hly penetration though the membrane: a,b fluorescent intensity of the solution beneath the co-culture brain–barrier model after 4 and 24 h of treatment. c The membrane cell viability after 24 h of treatment with Hly and copper nanomaterials as a negative control

The results indicated that the empty Hly nanotubes did not affect the cell metabolism in BMVECs and, hence, showed no significant sign of toxicity as the cellular metabolism was observed to be within 1–2% for the treatment of 10, 25, and 50 μg/mL of Hly, compared to control cells treated with media alone. Positive control of toxicity with 6 μg/mL of copper nanotubes (CuNPs) added demonstrated inhibition of the cell metabolism by 27% within 24 h.