Functionalization Of Inorganic Silic Silica Nannoparticle

Nanocrystals are made up of drug with only little amount of surfactant (below critical micelle concentration (CMC)) to stabilize formulation [14]. Most of the nanoparticles are made up of large amount of excipients which is not the case with nanocrystals as most of the part is only the drug. Besides lower amount of stabilizers makes toxicity issues associated with nanosuspensions negligible and offers ease of scale-up and better physical stability compared to amorphous form [15, 16]. Different methods are classified as top-down (high pressure homogenization, media milling, and sonication) and bottom-up techniques (nanoprecipitation) for effective production of Nanocrystals [17]. Development of nanocrystal based formulation of risperidone can be advantageous to tackle the problem of poor water solubility. Numerous solidification techniques are used to increase physical stability of nanosuspensions as spray drying, lyophilization and many more based upon the properties of drug and characteristics of final formulation. Amongst all these techniques lyophilization is used predominantly for nanosuspension solidification.

Since last two decades, several versatile drug delivery systems, including liposomes [24], block co-polymers [25], dendrimers [26], inorganic nanomaterials [27], proteins [28] as well as self-assembling small molecules [29] have been extensively studied and developed. Particularly, great interest has been focused on the self-assembling peptides as drug delivery vehicles, because of their good biocompatibility, flexible design, simple synthetic steps as well as facile modification and functionalization [30, 31]. Generally, the self-assembled peptides’ nanoparticles can spontaneously form in aqueous solution or triggered by pH [32], ionic strength [33], enzyme [34, 35] or light [36, 37], temperature [38, 39], driving by non-covalent interactions,

Nanocarriers (NCs) have emerged as a favored drug delivery approach towards improving the anticancer benefits of several bioactives for cancer therapy with recent reports showing the application of NC systems in clinical settings [18]. The NCs with size < 100 nm have been associated with enhanced permeation and retention effect (EPR) due to the presence of leaky vasculature in the tumor tissues which contributes to its enhanced efficacy. Also recently, NCs have shown to be effective in the treatment of malignant mesothelioma [19]. A recent study by Kanai et al. showed that the NC albumin-bound paclitaxel and carboplatin (nabPC) repetitively achieved tumor regression in malignant mesothelioma

Béalle and collaborators (2014) described the use of superparamagnetic iron oxide nanoparticles (ɣ-Fe2O3) to decorate catanionic vesicles. The vesicles were prepared by using cetyltrimethylammonium chloride and myristic acid and the nanomaterial was synthetized in aqueous alkaline solution by co-precipitation process of FeCl2 and FeCl3. The decoration and incorporation of ɣ-Fe2O3 was carried out by an adsorptive process onto the vesicles structure [7]. Additionally, silica-coated unilamellar surfactant vesicles was prepared by hydrolysis and condensation of silicon alkoxides [8] into organized inorganic material (Dioctadecyldimethylammonium bromide and didodecyldimethylammonium

The size of the NPs prepared was in-between 100-150nm. The NPs prepared were found to have sustained drug release properties (Mittal et al. 2007).

The physicochemical properties of nanoparticles that have been identified as important factors in uptake and toxicity include crystal structure, size, surface charge, surface energy, and chemical composition [14].

It was proven that surface active agents which are the backbone of the formulated lipid vesicles can enhance the transdermal delivery of drugs by lowering the permeability barrier of the skin and interacting with the SC in vitro [45]. On the other hand, Studies also reported that the drug molecules to be effectively transported across the SC they must be entrapped within the lipid vesicles suggesting that the vesicles act as drug carrier systems and not as penetration enhancers [46].

Physical permeation enhancement may be superior in delivering hydrophilic and macromolecular agents (Murthy et al., 2007b).

In the past, delivery of biotherapeutics has shown limited success due to the immunogenicity caused by the delivery vectors [154] (were the scientist were using the virus as a vector). Inclusion of biotherapeutics in NP delivery systems has promise as biocompatible polymer-coated NPs provide protection against inhibitive immune responses and targeted delivery of these therapeutic agents. Typically, for gene therapy, NPs are coated with a cationic polymer that encapsulates or binds DNA or siRNA as the positive charge of this layer allows for favorable electrostatic interactions with negatively charged nucleic acids [155]. The conjugating of NPs with peptides is other design considerations for DNA delivery to the cell nucleus for the successful transfection of genetic material. This is usually accomplished by conjugating peptides that

The efficient delivery of drugs and energy to tumors faces several difficulties and obstacles that need to be overcome for effective cancer treatment. Nanoparticles administrated through intravenous injections accumulate at a tumor site due to the enhanced permeability and retention (EPR) effect, but only a small quantity of the injected particles can actually “reach the tumor” (Su et al, 2016). The majority of the nanoparticles interact with “cancer cells at the periphery of a tumor” which presents a “physiological barrier” that prevents most of the injected particles from reaching the tumor (Su et al, 2016). In addition to this barrier, there is also another significant obstacle, “cancer-associated fibroblasts”, which can also

Use the ultrasound to enhance cell permeability is a new methods for gene transfection. The increase uptake of DNA or RNA has been demonstrated by several investigators2-1, 2-5. However, the further enhancement of gene transfection

The ongoing nanoparticle systems have provided a semi-solid foundation in mitigating tumours but further arenas are being explored in cancer therapeutics so as to enhance the drug delivery process. The researchers have suggested and made use of nanoparticles in the size range of 1 -100 nm. Nanoparticles are known to elicit a

In an effort to combat this, we will use nanoparticles to deliver anti-mitotic drugs to the site of the tumor. Preliminary data is promising for the administration of both proTAME and apcin, and inhibition of CSCs. In addition, the preliminary data for nanoparticles is promising for the delivery of this therapy across the blood brain barrier. Determining the extent that these nanoparticle/therapy complexes will impact CSCs in vivo is the focus of this aim and will provide information on nanoparticles in complex with anti-mitotic drugs and their ability to cross the blood brain barrier.

Although the small size of nanocrystals leads to several advantages, but at the same time, it can lead to stability concerns as well. Theoretically, if we increase the drug surface area, it leads to an increase in Gibbs free energy. The system tries to reverse this increase by agglomeration/aggregation, ultimately leading to increased particle size and reduced stability.

The structural analysis of nanodisc bound A1-40 ¬suggests the formation of intermediate conformation with typical sheet structures driven by the PMA. We next characterized the toxicity of these A1-40 intermediates in human neuroblastoma (SH-SY5Y) cells. Results showed substantial cytotoxic behavior of PMA in solution with a cell viability loss of ≈ 40 % at 2.5 M. The A1-40 monomer and fibers (2.5 M) incubated with equimolar PMA also showed a nearly equivalent cell cytotoxicity as that of the free PMA. In contrast, the PMA bound nanodiscs (Fig 5b) such as DMPC/GM1 (4:1) and DMPC (100 %) showed a relatively low cytotoxicity (< ≈ 10 %). On the other hand, the anionic