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Immunoreactivity of Nanoparticles

Author: Tilda Barliya PhD

As nanotechnology progresses from research and development to commercialization and use, it is likely that manufactured nanomaterials and nanoproducts will be released into the environment.

Adverse effects of nanoparticles on human health depend on individual factors such as genetics and existing disease, as well as exposure, and nanoparticle chemistry, size, shape, agglomeration state, and electromagnetic properties. Animal and human studies show that inhaled nanoparticles are lessefficiently removed than larger particles by the macrophage clearance mechanisms in the lung,causing lung damage, and that nanoparticles can translocate through the circulatory, lymphatic, and nervous systems to many tissues and organs, including the brain.

The key to understanding the toxicity of nanoparticles is that their minute size, smaller than cells and cellular organelles, allows them to penetrate these basic biological structures, disrupting their normal function. Examples of toxic effects include tissue inflammation, and altered cellular redox balance toward oxidation, causing abnormal function or cell death. http://arxiv.org/ftp/arxiv/papers/0801/0801.3280.pdf

Some NPs happen to be toxic to biological systems, others are relatively benign, while others confer health benefits. As current knowledge of the toxicology of ‘bulk’ materials may not suffice in reliably predicting toxic forms of nanoparticles, ongoing and expanded study of ‘nanotoxicity’ will be necessary. For nanotechnologies with clearly associated health risks, intelligent design of materials and devices is needed to derive the benefits of these new technologies while limiting adverse health impacts.

Human skin, lungs, and the gastro-intestinal tract are in constant contact with the environment. While the skin is generally an effective barrier to foreign substances, the lungs and gastro-intestinal tract are more vulnerable. These three ways are the most likely points of entry for natural or anthropogenic nanoparticles. Injections and implants are other possible routes of exposure, primarily limited to engineered materials. Due to their small size, nanoparticles can translocate from these entry portals into the circulatory and lymphatic systems, and ultimately to body tissues and organs. Some nanoparticles, depending on their composition and size, can produce irreversible damage to cells by oxidative stress or/and organelle injury.

Are they biocompatible? Do the nanoparticles enter the lymphatic and circulatory systems? If not, do they accumulate in the skin and what are the long-term effects of accumulation? Do they produce inflammation? If they enter the lymphatic and circulatory system, is the amount significant? What are the long-term effects of this uptake? Related to the beneficial antioxidant properties of some nanomaterials, long-term effect need to be studied, in addition to the short-term antioxidant effect. What is the long-

term fate of these nanoparticles? Are they stored in the skin? Do they enter circulation? What happens when the nanoparticles undergo chemical reactions and lose their antioxidant properties?

For a full view of the questions needed to be addressed please visit. http://bdds.fudan.edu.cn/…/fdfa2aa9-df2b-4c9f-a2a5-a33ee29acb76.pdf

The answers to some of these questions are known, and will be presented in the chapter dedicated to nanoparticles toxicity, however most of the remaining questions still remain unanswered.

The immunostimulatory properties of nanoparticles discussed here include their antigenicity, adjuvant properties, inflammatory responses and the mechanisms through which nanoparticles are recognized by the immune system. Since this is a very complicated mechanism , the factors affecting the immune response are summaried here:

Size

  • Th1/Th2 stimulation
  • Adjuvent properties
  • Internalization/phagocytic uptake
  • Hapten properties
  • Particle clearance

Charge

  • Toxicity to immune cells
  • Binding plasma proteins
  • Particle clearance
  • Immune cell stimulation

Hydrophobicity

  • Interaction with plasma proteins
  • Internalization/phagocytic uptake
  • Immune cell stimulation
  • Particle clearance

Targeting

  • Immunogenicity

For example: In general, cationic (positively-charged) particles are more likely to induce inflammatory reactions than anionic (negativelycharged) and neutral species. For example, anionic generation- 4.5 PAMAM dendrimers did not cause human leukocytes (white blood cells) to secrete cytokines53 but cationic liposomes induced secretion of cytokines such as TNF, IL-12 and IFNγ. Systemic administration of another cationic nanoliposome alone or in combination with bacterial DNA did not induce cytokine production but increased the expression of DC surface markers, CD80/CD86, which are important in the inflammatory response.

Trace impurities within the nanomaterial formulation can also frequently induce an inflammatory response. Early studies suggest that carbon nanotubes induce inflammatory reactions, but a more recent study shows that they don’t when they are purified.

Another consideration in the inflammatory response is maintaining the Th1/Th2 response — the inflammatory reaction.  triggered by Th cells that direct and activate other immune cells such as B and T cells and macrophages to secrete different cytokines. This response is important for protecting against cancer cells and pathogens and to avoid hypersensitivity (undesirable and exaggerated immune response) reactions. Several studies have addressed the influence of nanoparticles on Th1 and Th2 responses. Large (>1 μm) industrialized particles induced the Th1 response, whereas smaller ones (<500 nm) were associated with Th2.

In contrast, some small engineered nanoparticles such as 500 nm PLGA, 270 nm PLGA65, 80 nm and 100 nm nanoemulsions, 95 nm and 112 nm PEG–PHDA nanoparticles, and 123 nm dendrosome induced the Th1 response, while 5mn 5th generation PAMAM dendrimers didn’t cause overall inflammatory reaction in vivo but weakly induced Th2 cytokine production.

Therefore, more structure–activity relationship studies are required to understand how size, surface modification and charge of engineered particles influence the Th1/Th2 balance

Particle stimulation of adaptive (acquired) immunity has also been described. For example, small (<100 nm) polystyrene particles promoted CD8 and CD4 T-cell responses and were associated with higher antibody levels than larger (>500 nm) particles. Understanding the mechanisms requires further investigation, and is important for nanovaccine formulation development.

Phagosome-mediated processing and presentation of nanoparticles may differ from that of ‘canonical’ antigens. Certain biodegradable nanoparticles can be taken up through conventional pathogen-specific routes and can stimulate inflammatory reactions just like pathogens

More mechanistic studies are required to understand how the immune system manages non-biodegradable components of nanoparticles (for example, metallic cores). Many questions remain regarding processing of multi-component and multi functional nanoparticles. Are the individual components (the coating, core, and so on) stable inside the phagosome or do they separate? Are the biodegradable and non-biodegradable components processed together or individually?

Immunotoxicological analysis of new molecular entities is not a straightforward process, and there is no universal guide for immunotoxicity.

Conclusions:

The mechanism of cellular uptake of nanoparticles and the biodistribution depend on the physico-chemical properties of the particles and in particular on their surface characteristics. Moreover, as particles are mainly recognized and engulfed by immune cells special attention should be paid to nano–immuno interactions. It is also important to use primary cells for testing of the biocompatibility of nanoparticles, as they are closer to the in vivo situation when compared to transformed cell lines.

Understanding the unique characteristics of engineered nanomaterials and their interactions with biological systems is key to the safe implementation of these materials in novel biomedical diagnostics and therapeutics.

The main challenge in immunological studies of nanomaterials is choosing an experimental approach that is free of falsepositive or false-negative readouts. The majority of the standard immunotoxicological methods are applicable to nanomaterials. However, as nanoparticles represent physically and chemically diverse materials, the classical methods cannot always be applied without modification, and novel approaches may be required. For example, many nanoparticles absorb in the UV–Vis range and some particles may catalyse enzyme reactions or quench fluorescent dyes commonly used as detection reagents in various end-point or kinetic assays. These and other methodological

challenges in preclinical evaluation of nanoparticles are reviewed in detail elsewhere.

Both ‘classical’ and novel imunotoxicological assessments of nanomaterials clearly need a scrupulous stepwise validation, standardization, and demonstration of their physiological relevance.

Industry, academics, and federal agencies are now collaborating to identify critical parameters in nanoparticles characterization and to establish acceptance criteria for nanomaterial-specific assays.

Ref.

1.Cristina Buzea, Ivan. I. Pacheco Blandino, and Kevin Robbie. Nanomaterials and nanoparticles:Sources and toxicity. Biointerphases vol. 2, issue 4 (2007) pages MR17 – MR172 http://arxiv.org/ftp/arxiv/papers/0801/0801.3280.pdf

2. Marina A. Dobrovolskaia* and Scott E. McNeil. Immunological properties of engineered nanomaterials. Nature Nanotechnology 2007; 2; 469-479.  http:// bdds.fudan.edu.cn/…/fdfa2aa9-df2b-4c9f-a2a5-a33ee29acb76.pdf

3.  Kunzmanna A,  Anderssonb B, Thurnherrc T, Krugc H, Scheyniusb A,  Fadeel B. Toxicology of engineered nanomaterials: Focus on biocompatibility, biodistribution and biodegradation. Biochimica et Biophysica Acta (BBA) – General Subjects. Volume 1810, Issue 3, March 2011, Pages 361–373 http://www.sciencedirect.com/science/article/pii/S0304416510001145

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Nanotechnology and MRI imaging

Author: Tilda Barliya PhD

The recent advances of “molecular and medical imaging” as an integrated discipline in academic medical centers has set the stage for an evolutionary leap in diagnostic imaging and therapy. Molecular imaging is not a substitute for the traditional process of image formation and interpretation, but is intended to improve diagnostic accuracy and sensitivity.

Medical imaging technologies allow for the rapid diagnosis and evaluation of a wide range of pathologies. In order to increase their sensitivity and utility, many imaging technologies such as CT and MRI rely on intravenously administered contrast agents. While the current generation of contrast agents has enabled rapid diagnosis, they still suffer from many undesirable drawbacks including a lack of tissue specificity and systemic toxicity issues. Through advances made in nanotechnology and materials science, researchers are now creating a new generation of contrast agents that overcome many of these challenges, and are capable of providing more sensitive and specific information (1)

Magnetic resonance imaging (MRI) contrast enhancement for molecular imaging takes advantage of superb and tunable magnetic properties of engineered magnetic nanoparticles, while a range of surface chemistry offered by nanoparticles provides multifunctional capabilities for image-directed drug delivery. In parallel with the fast growing research in nanotechnology and nanomedicine, the continuous advance of MRI technology and the rapid expansion of MRI applications in the clinical environment further promote the research in this area.

It is well known that magnetic nanoparticles, distributed in a magnetic field, create extremely large microscopic field gradients. These microscopic field gradients cause substantial diphase and shortening of longitudinal relaxation time (T1) and transverse relaxation time (T2 and T2*) of nearby nuclei, e.g., proton in the case of most MRI applications. The magnitudes of MRI contrast enhancement over clinically approved conventional gadolinium chelate contrast agents combined with functionalities of biomarker specific targeting enable the early detection of diseases at the molecular and cellular levels with engineered magnetic nanoparticles. While the effort in developing new engineered magnetic nanoparticles and constructs with new chemistry, synthesis, and functionalization approaches continues to grow, the importance of specific material designs and proper selection of imaging methods have been increasingly recognized (2)

Earlier investigations have shown that the MRI contrast enhancement by magnetic nanoparticles is highly related to their composition, size, surface properties, and the degree of aggregation in the biological environment.

Therefore, understanding the relationships between these intrinsic parameters and relaxivities of nuclei under influence of magnetic nanoparticles can provide critical information for predicting the properties of engineered magnetic nanoparticles and enhancing their performance in the MRI based theranostic applications. On the other hand, new contrast mechanisms and imaging strategies can be applied based on the novel properties of engineered magnetic nanoparticles. The most common MRI sequences, such as the spin echo (SE) or fast spin echo (FSE) imaging and gradient echo (GRE), have been widely used for imaging of magnetic nanoparticles due to their common availabilities on commercial MRI scanners. In order to minimize the artificial effect of contrast agents and provide a promising tool to quantify the amount of imaging probe and drug delivery vehicles in specific sites, some special MRI methods, such as  have been developed recently to take maximum advantage of engineered magnetic NPs

  • off-resonance saturation (ORS) imaging
  • ultrashort echo time (UTE) imaging

Because one of the major limitations of MRI is its relative low sensitivity, the strategies of combining MRI with other highly sensitive, but less anatomically informative imaging modalities such as positron emission tomography (PET) and NIRF imaging, are extensively investigated. The complementary strengths from different imaging methods can be realized by using engineered magnetic nanoparticles via surface modifications and functionalizations. In order to combine optical or nuclear with MR for multimodal imaging, optical dyes and radio-isotope labeled tracer molecules are conjugated onto the moiety of magnetic nanoparticles

Since most functionalities assembled by magnetic nanoparticles are accomplished by the surface modifications, the chemical and physical properties of nanoparticle surface as well as surface coating materials have considerable effects on the function and ability of MRI contrast enhancement of the nanoparticle core.

The longitudinal and transverse relaxivities, Ri (i=1, 2), defined as the relaxation rate per unit concentration (e.g., millimole per liter) of magnetic ions, reflects the efficiency of contrast enhancement by the magnetic nanoparticles as MRI contrast agents. In general, the relaxivities are determined, but not limited, by three key aspects of the magnetic nanoparticles:

  1. Chemical composition,
  2. Size of the particle or construct and the degree of their aggregation
  3. Surface properties that can be manipulated by the modification and functionalization.

(It is also recognized that the shape of the nanoparticles can affect the relaxivities and contrast enhancement. However these shaped particles typically have increased sizes, which may limit their in vivo applications. Nevertheless, these novel magnetic nanomaterials are increasingly attractive and currently under investigation for their applications in MRI and image-directed drug delivery).

Composition Effect: The composition of magnetic nanoparticles can significantly affect the contrast enhancing capability of nanoparticles because it dominates the magnetic moment at the atomic level. For instance, the magnetic moments of the iron oxide nanoparticles, mostly used nanoparticulate T2 weighted MRI contrast agents, can be changed by incorporating other metal ions into the iron oxide.  The composition of magnetic nanoparticles can significantly affect the contrast enhancing capability of nanoparticles because it dominates the magnetic moment at the atomic level. For instance, the magnetic moments of the iron oxide nanoparticles, mostly used nanoparticulate T2 weighted MRI contrast agents, can be changed by incorporating other metal ions into the iron oxide.

Size Effect: The dependence of relaxation rates on the particle size has been widely studied both theoretically and experimentally. Generally the accelerated diphase, often described by the R2* in magnetically inhomogeneous environment induced by magnetic nanoparticles, is predicted into two different regimes. For the relatively small nanoparticles, proton diffusion between particles is much faster than the resonance frequency shift. This resulted in the relative independence of T2 on echo time. The values for R2 and R2*are predicted to be identical. This process is called “motional averaging regime” (MAR). It has been well demonstrated that the saturation magnetization Ms increases with the particle size. A linear relationship is predicted between Ms1/3 and d-1. Therefore, the capability of MRI signal enhancement by nanoparticles correlates directly with the particle size. 

Surface Effect: MRI contrast comes from the signal difference between water molecules residing in different environments that are under the effect of magnetic nanoparticles. Because the interactions between water and the magnetic nanoparticles occur primarily on the surface of the nanoparticles, surface properties of magnetic nanoparticles play important roles in their magnetic properties and the efficiency of MRI contrast enhancement. As most biocompatible magnetic nanoparticles developed for in vivo applications need to be stabilized and functionalized with coating materials, the coating moieties can affect the relaxation of water molecules in various forms, such as diffusion, hydration and hydrogen binding.

The early investigation carried at by Duan et al suggested that hydrophilic surface coating contributes greatly to the resulted MRI contrast effect. Their study examined the proton relaxivities of iron oxide nanocrystals coated by copolymers with different levels of hydrophilicity including: poly(maleic acid) and octadecene (PMO), poly(ethylene glycol) grated polyethylenimine (PEG-g-PEI), and hyperbranched polyethylenimine (PEI). It was found that proton relaxivities of those IONPs depend on the surface hydrophilicity and coating thickness in addition to the coordination chemistry of inner capping ligands and the particle size.

The thickness of surface coating materials also contributed to the relaxivity and contrast effect of the magnetic nanoparticles. Generally, the measured T2 relaxation time increases as molecular weight of PEG increases.

In Summary

Much progress has taken place in the theranostic applications of engineered magnetic nanoparticles, especially in MR imaging technologies and nanomaterials development. As the feasibilities of magnetic nanoparticles for molecular imaging and drug delivery have been demonstrated by a great number of studies in the past decade, MRI guiding and monitoring techniques are desired to improve the disease specific diagnosis and efficacy of therapeutics. Continuous effort and development are expected to be focused on further improvement of the sensitivity and quantifications of magnetic nanoparticles in vivo for theranostics in future.

The new design and preparation of magnetic nanoparticles need to carefully consider the parameters determining the relaxivities of the nanoconstructs. Sensitive and reliable MRI methods have to be established for the quantitative detection of magnetic nanoparticles. The new generations of magnetic nanoparticles will be made not only based on the new chemistry and biological applications, but also with combined knowledge of contrast mechanisms and MRI technologies and capabilities. As new magnetic nanoparticles are available for theranostic applications, it is anticipated that new contrast mechanism and MR imaging strategies can be developed based on the novel properties of engineered magnetic nanoparticles.

References:

1http://www.omicsonline.org/2157-7439/2157-7439-2-115.php

2http://www.clinical-mri.com/pdf/CMRI/8036XXP14Ap454-472.PDF

3http://www.thno.org/v02p0086.htm

4http://www.omicsonline.org/2157-7439/2157-7439-2-115.pdf

5http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3017480/

6http://www.nature.com/nmeth/journal/v7/n12/full/nmeth1210-957.html

7http://endomagnetics.com/wp-content/uploads/2011/01/TargOncol_Review_2009.pdf

8http://www.nature.com/nnano/journal/v2/n5/abs/nnano.2007.105.html

9http://www.azonano.com/article.aspx?ArticleID=2680

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Author: Tilda Barliya PhD

Title: Factors affecting the PK of the nanocarrier.

Category: Nanotechnology in drug delivery

A plethora of new products are emerging as potential therapeutic agents. This calls for detailed studies of their unique pharmacologic characteristics and mechanisms of action in humans. This review written by Caron WP et al (Zamboni’s group) provides a major overview of the factors that affect the pharmacokinetics (PK) and pharmacodynamics (PD) of nanoparticle carries in preclinical models and patients (1). I will use this article as the main source as it was so nicely written yet many other references are added within.

The disposition of carrier-mediated agents (CMAs) is dependent on the carrier and not on the parent drug, until the drug is released from the carrier into the system and includes encapsulated (the drug within or bound to the carrier), released (the active drug that gets released from the carrier), and sum total (encapsulated drug plus released drug).

After the drug has been released from its carrier, it is pharmacologically active and subjected to the same routes of metabolism and clearance (CL) as the non-carrier form of the drug (1,2).

In theory, the PK disposition of the drug after it is released from the carrier should be the same as after administration of the small-molecule or standard formulations. Therefore, the pharmacology and PK of CMAs are complex and call for comprehensive analytical studies to assess the disposition of encapsulated and released forms of the drug in plasma and tumor.

Interindividual variability in drug exposure, represented by area under the plasma concentration– time curve (AUC) of the encapsulated drug and several factor can potentially affect it:

  • Physical characteristics of the CMA (size, charge, surface modification). Figure 1
  • Host-associated characteristics such as gender and age as well as the host mononuclear phagocyte system (MPS), which is a collective term for the immune cells.

F3.large.jpg (1280×843)

Figure 1 here (=figure 3 in the original paper. ref 1) : Nanoparticle clearance and biocompatibility are dependent on various factors including physical characteristics of the carrier as well as physiologic parameters such as the mononuclear phagocyte system (MPS) (reticuloendothelial system (RES)) recognition and enhanced permeability and retention (EPR) effect. There are qualitative relationships between the independent variables, namely, particle size, particle zeta-potential (surface charge), and solubility, and the dependent variable, namely, biocompatibility. Biocompatibility, or extent of exposure (area under the plasma concentration–time curve), includes the route of uptake and clearance (shown in green as the EPR effect and renal and biliary clearance), cytotoxicity (shown in red, can represent either efficacy or toxicities/ adverse events in anticancer treatment), and MPS/RES recognition (shown in blue).

The effect on the immune cells is divided into two categories:  (i) responses to nanoparticles that are specifically modified to stimulate the immune system (e.g., vaccine carriers) and (ii) undesirable interactions and/or side-effects.

Immune cells that participate in nanoparticle uptake are circulating monocytes, platelets, leukocytes, and dendritic cells in the bloodstream (3,4).  In addition, nanoparticles can be taken up in tissues by phagocytes, e.g., by Kupffer cells in the liver, by dendritic cells in the lymph nodes, by B cells in the spleen, and by macrophages

Uptake mechanisms may occur through different pathways and can often be facilitated by the adsorption of opsonins to the nanoparticle surface

Physical characteristics:

  • Particle size: In one study of liposomes, particles that had a hydrodynamic diameter between 100 and 200 nm had a fourfold higher rate of uptake in tumors than particles <50 nm or >300 nm.
  • Surface modification: Conjugated PEG polymer onto the surface- is known to minimize opsonization and thus subsequent decreased rate of MPS uptake overall plasma exposures of drugs contained within PEGylated liposomes were six fold higher than those contained within non-PEGylated liposomes
  • Surface charge: Uncharged liposomes have lower CLs than either positively or negatively charged liposomes (probably due to reduced opsonization by MPS. rate of CL from blood was significantly higher for negatively charged particles than for uncharged particles

It can be summarized as for their rate of clearance from highest (left) to lowest (right) as:

positive>negative> neutral

Note: PEGylation can alter the alter this rate significantly for example,

Levchenko et al. showed that the negative charge on liposomes can be shielded with this physical alteration, leading to a significantly reduced rate of liver uptake and consequent prolongation of their presence in circulating blood (5).

Host characteristics

  • Age: In some cases, age-related effects on the PK of some PEGylated liposomal agents have been reported, where in younger male patients (<60) there was a higher rate of clearance of two different agents (Doxil and CDK602) compared to older patients (>60). In other words, in older age, the CL rate was lower and therefore higher AUC/dose. No relation to age was observed for female patients, in the same study.

Alterations in the PK and PD of CMAs may involve accerelated decline in immune system functioning, specifically the association between aging and the functioning of monocytes (6). In theory, there is a loss of MPS activity or function in elderly patients, and this decreases the CL of CMAs by the MPS, leading to increased drug exposures and toxicity in elderly patients. In terms of efficacy, greater age was inversely proportional to progression-free survival; however, no correlation was found between age and overall survival.

  •  Gender: In similar study to the one presented above, female patients had overall lower CL of DOXIL, IHL-305 and CDK602 compared to male patients of the same age.

The basis for the gender-related differences in the PK and PD of CMAs is unclear. It has been hypothesized that some of the differences may be attributed to the effects of sex hormones such as testosterone and estrogen on immune cell function.

Delivery of CMAs Into Tumor

Major advances in the understanding of tumor biology have led to the discovery of targeted agents that can deliver drugs to the desired site while minimizing exposure in normal tissues, thereby minimizing the associated adverse effects. Whereas conventional drugs encounter numerous obstacles en route to their target, CMAs can take advantage of a tumor’s leaky vasculature to extravasate into tissue, via the enhanced permeability and retention effect (EPR).

Note: The extend of the EPR effect is highly debated since although passive targeting through the EPR effect has been a key concept in delivering CMAs to tumors, it does not ensure uniform delivery to all regions of tumor. Furthermore, not all tumors exhibit an EPR effect, and the permeability of vessels may not be the same across any single tumor.

Active targeting may overcome these limitations. The CMAs can be enabled to bind to specific cells in a tumor by using surface attached ligands that are capable of recognizing and binding to cells of interest.

Antibody-mediated targeting has been the method of choice, other targeting strategies using nucleic acids, carbohydrates, peptides, aptamers, vitamins, and other agents are also being evaluated.

Other major points that can affect the PK disposition

  • The linearity and nonlinearity of the CLs of a drug (might be associated with the dose like with S-CKD602)(7).
  • Drug-drug interaction (single agent vs combination)
  • Body composition (Body surface area, body weight)

There are a multitude of properties of CMAs that differ from those of the active small-molecule drugs they contain. These differences lead to significant variability in the PK and PD of carrier- mediated drugs. It has been shown that physical properties, the MPS, the presence of tumors in the liver, EPRs, drug–drug interactions, age, and gender all contribute in varying degrees to the PK disposition and PD end points of CMAs in patients.

Areas of research that can aid in an understanding of how these agents should be used and how we may predict their actions in patients include pharmacogenomics, cellular function (probing the MPS), more sensitive and accurate analytical PK methods, and identification of the optimal preclinical (animal and in vitro) models.

References:

1. W P Caron, G Song, P Kumar, S Rawal and W C Zamboni.Interpatient PK and PD variability of carrier-mediated anticancer agent.  Clinical Pharmacology and Therapeutics 2012 91, 802-812 http://www.nature.com/clpt/journal/vaop/ncurrent/full/clpt201212a.html

2. Zamboni, W.C. Liposomal, nanoparticle, and conjugated formulations of anticancer agents. Clin. Cancer Res. 11, 8230–8234 (2005).

http://clincancerres.aacrjournals.org/content/11/23/8230.long

http://clincancerres.aacrjournals.org/content/11/23/8230.full.pdf+html

3. Dobrovolskaia, M.A., Aggarwal, P., Hall, J.B. & McNeil, S.E. Preclinical studies to understand nanoparticle interaction with the immune system and its potential effects on nanoparticle biodistribution. Mol. Pharm. 5, 487–495 (2008). http://www.ncbi.nlm.nih.gov/pmc/articles/PMC2613572/

4. Dobrovolskaia, M.A. & McNeil, S.E. Immunological properties of engineered nanomaterials. Nat. Nanotechnol. 2, 469–478 (2007). http://www.ncbi.nlm.nih.gov/pubmed/18654343

5. Levchenko, T.S., Rammohan, R., Lukyanov, A.N., Whiteman, K.R. & Torchilin, V.P. Liposome clearance in mice: the effect of a separate and combined presence of surface charge and polymer coating. Int. J. Pharm. 240, 95–102 (2002). http://www.ncbi.nlm.nih.gov/pubmed/12062505

6. Lloberas, J. & Celada, A. Effect of aging on macrophage function. Exp. Gerontol. 37, 1325–1331 (2002). http://www.ncbi.nlm.nih.gov/pubmed/12559402

7. Zamboni, W.C. et al. Pharmacokinetic study of pegylated liposomal CKD-602 (S-CKD602) in patients with advanced malignancies. Clin. Pharmacol. Ther. 86, 519–526 (2009). http://www.nature.com/clpt/journal/v86/n5/abs/clpt2009141a.html

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Author: Tilda Barliya PhD

Category owner: Nanotechnology in drug deliveryImage

Nanotechnology is simply defined as the technology to manipulate the matter on the atomic and/or molecular scale. It is generalized to materials, devices and structures with dimensions sizes at the nanoscale of 1 to 1000 nanometers (nm) (1,2).

Nanotachnology can be applied to many fields including sensors, biomaterials for tissue engineering, and nanostructures or 3D materials for molecular imaging and drug delivery among others. In medicine, nanotechnology is essentially a multidisciplinary field of physics, organic and polymer chemistry as well as molecular biology, pharmacology and engineering. These fields team up together to design a better and most opt treatment option for a disease using “the right drug, the right vehicle and the right route of administration”. In pharmaceutical industries, a new molecular entity (NME) that demonstrates potent biological activity but poor water solubility, or a very short circulating halflife, will likely face significant development challenges or be deemed undevelopable. There is always a degree of compromise, and such tradeoffs may inevitably result in the production of less-ideal drugs. However, with the emerging trends and recent advances in nanotechnology, it has become increasingly possible to address some of the shortcomings associated with potential NMEs. By using nanoscale delivery vehicles, the pharmacological properties (e.g., solubility and circulating half-life) of such NMEs can be drastically improved, essentially leading to the discovery of optimally safe and effective drug candidates. (3,4).

This is just one example which demonstrates the degree to which nanotechnology may revolutionize the rules and possibilities of drug discovery and change the landscape of pharmaceutical industries. (5)

Nanomedicine is facing many challenges in overcoming biological barriers, arrival and accumulation at the target site, therefore advances in nanoparticle engineering, as well as advances in understanding the importance of nanoparticle characteristics such as size, shape and surface properties for biological interactions, are necessary to create new opportunities for the development of nanoparticles for therapeutic applications (6).

Compared to conventional drug delivery, the first generation nanosystems provide a number of advantages. In particular, they can enhance the therapeutic activity by prolonging drug half-life, improving solubility of hydrophobic drugs, reducing potential immunogenicity, and/or releasing drugs in a sustained or stimuli-triggered fashion. Thus, the toxic side effects of drugs can be reduced, as well as the administration frequency. In addition, nanoscale particles can passively accumulate in specific tissues (e.g., tumors) through the enhanced permeability and retention (EPR) effect. Beyond these clinically efficacious nanosystems, nanotechnology has been utilized to enable new therapies and to develop next generation nanosystems for “smart” drug delivery (such as gene theraphy).

In summary; there are several factors that need to be included for a rational nanocarrier design:

–          Protect the drug from premature degradation

–          Protect the drug from premature interaction with biological environment

–          Enhance the absorption of the drug into the selected tissue-site

–          Improve intracellular drug penetration

–          Improve and control the drug pharmacokinetics and distribution profile.

Moreover there are several other factors that need to be taken into consideration to effectively influence the clinical translation of the drug delivery system (DDS) i.e materials that are biodegradable and biocompatible, easily functionalized, exhibit high differential uptake efficiency etc.(7-9).

In the next few chapters, we will try to address some of these factors as well as some examples that succeeded in the clinical setting as well as those who failed.

References:

  1. Nanotechnology and Drug Delivery Part 1: Background and Applications Nelson A Ochekpe, Patrick O Olorunfemi and Ndidi C Ngwuluka.Tropical Journal of Pharmaceutical Research, June 2009; 8 (3): 265-274. http://www.tjpr.org/vol8_no3/2009_8_3_11_Ochekpe.pdf
  2. Davis, M. E., Chen, Z. & Shin, D. M. Nanoparticle therapeutics: an emerging treatment modality for cancer. Nature Rev. Drug Discov. 7, 771–782 (2008). http://www.nature.com/nrd/journal/v7/n9/abs/nrd2614.html
  3. Nanotechnology in Drug Delivery and Tissue Engineering: From Discovery to Applications Jinjun Shi,†,§ Alexander R. Votruba,§ Omid C. Farokhzad,†,§ and Robert Langer*,†,‡. Nano Lett. 2010, 10, 3223–3230. http://engineering.unl.edu/academicunits/chemical-engineering/research/focuslab/kidambi_lab/CHME_896_496_files/Impact%20of%20Nanotechnology%20on%20Drug%20Delivery-Langer_ACSNano’09.pdf
  4. Sengupta, S. et al. Temporal targeting of tumour cells and neovasculature with a nanoscale delivery system. Nature 436, 568–572 (2005) http://www.ncbi.nlm.nih.gov/pubmed/16049491
  5. Torchilin, V. P. Recent advances with liposomes as pharmaceutical carriers. Nature Rev. Drug Discov. 4, 145–160 (2005). http://www.chem.umass.edu/~thompson/Courses/chem697a/papers/TorchilinReviewLiposomeCarriers.pdf
  6. Decuzzi, P. et al. Size and shape effects in the biodistribution of intravascularly injected particles. J. Control. Release 141, 320–327 (2010) http://www.ncbi.nlm.nih.gov/pubmed?term=Decuzzi%2C%20P.%20et%20al.%20Size%20and%20shape%20effects%20in%20the%20biodistribution%20of%20intravascularly%20injected%20particles.%20J.%20Control.%20Release%20141%2C%20320%E2%80%93327%20(2010)
  7. Nanocarriers as an emerging platform for cancer therapy. Dan Peer1†, Jeffrey M. Karp2,3†, Seungpyo Hong4†, Omid C. Farokhzad5, Rimona Margalit6 and Robert Langer3,4*. nature nanotechnology 2007 |  vol 2 751-760. http://www.nature.com/nnano/journal/v2/n12/abs/nnano.2007.387.html
  8. Alonso, M. J. Nanomedicines for overcoming biological barriers. Biomed. Pharmacother. 58, 168–172 2004. http://www.ncbi.nlm.nih.gov/pubmed/15082339
  9. Torchilin, V. P. Recent advances with liposomes as pharmaceutical carriers. Nat. Rev. Drug Discov.4, 145–160 (2005) http://www.chem.umass.edu/~thompson/Courses/chem697a/papers/TorchilinReviewLiposomeCarriers.pdf

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Reporter Aviral Vatsa, PhD MBBS

Annual treatment costs for musculoskeletal diseases in the US are roughly 7.7% (~ $849 billion) of total gross domestic product. Such disorders are the main cause of physical disability in US. Almost half of all chronic conditions in people can be attributed to bone and joint disorders. In addition there is increasing ageing population and associated increases in osteoporosis and other diseases, rising incidences of degenerative intervertebral disk diseases and numbers of revision orthopedic arthroplasty surgeries, and increases in spinal fusions. All these factors contribute towards the increasing requirement of bone regeneration and reconstruction methods and products. Delivery of therapeutic grade products to bone has various challenges. Parenteral administration limits the efficient delivery of drugs to the required site of injury and local delivery methods are often expensive and invasive. The theme issue of Advance Drug Delivery reviews focuses on the current status of drug delivery to bone and the issues facing this field. Here is the first part of these reviews and research articles.

1. Demineralized bone matrix in bone repair: History and use

Abstract

Demineralized bone matrix (DBM) is an osteoconductive and osteoinductive commercial biomaterial and approved medical device used in bone defects with a long track record of clinical use in diverse forms. True to its name and as an acid-extracted organic matrix from human bone sources, DBM retains much of the proteinaceous components native to bone, with small amounts of calcium-based solids, inorganic phosphates and some trace cell debris. Many of DBM’s proteinaceous components (e.g., growth factors) are known to be potent osteogenic agents. Commercially sourced as putty, paste, sheets and flexible pieces, DBM provides a degradable matrix facilitating endogenous release of these compounds to the bone wound sites where it is surgically placed to fill bone defects, inducing new bone formation and accelerating healing. Given DBM’s long clinical track record and commercial accessibility in standard forms and sources, opportunities to further develop and validate DBM as a versatile bone biomaterial in orthopedic repair and regenerative medicine contexts are attractive.

2. Biomimetic hydrogels for controlled biomolecule delivery to augment bone regeneration

Abstract

The regeneration of large bone defects caused by trauma or disease remains a significant clinical problem. Although osteoinductive growth factors such as bone morphogenetic proteins have entered clinics, transplantation of autologous bone remains the gold standard to treat bone defects. The effective treatment of bone defects by protein therapeutics in humans requires quantities that exceed the physiological doses by several orders of magnitude. This not only results in very high treatment costs but also bears considerable risks for adverse side effects. These issues have motivated the development of biomaterials technologies allowing to better control biomolecule delivery from the solid phase. Here we review recent approaches to immobilize biomolecules by affinity binding or by covalent grafting to biomaterial matrices. We focus on biomaterials concepts that are inspired by extracellular matrix (ECM) biology and in particular the dynamic interaction of growth factors with the ECM. We highlight the value of synthetic, ECM-mimicking matrices for future technologies to study bone biology and develop the next generation of ‘smart’ implants.

 

3. Calcium phosphate cements as drug delivery materials

Abstract

Calcium phosphate cements are used as synthetic bone grafts, with several advantages, such as their osteoconductivity and injectability. Moreover, their low-temperature setting reaction and intrinsic porosity allow for the incorporation of drugs and active principles in the material. It is the aim of the present work to: a) provide an overview of the different approaches taken in the application of calcium phosphate cements for drug delivery in the skeletal system, and b) identify the most significant achievements. The drugs or active principles associated to calcium phosphate cements are classified in three groups, i) low molecular weight drugs; ii) high molecular weight biomolecules; and iii) ions.

4. Silk constructs for delivery of musculoskeletal therapeutics

Abstract

Silk fibroin (SF) is a biopolymer with distinguishing features from many other bio- as well as synthetic polymers. From a biomechanical and drug delivery perspective, SF combines remarkable versatility for scaffolding (solid implants, hydrogels, threads, solutions), with advanced mechanical properties and good stabilization and controlled delivery of entrapped protein and small molecule drugs, respectively. It is this combination of mechanical and pharmaceutical features which renders SF so exciting for biomedical applications. This pattern along with the versatility of this biopolymer has been translated into progress for musculoskeletal applications. We review the use and potential of silk fibroin for systemic and localized delivery of therapeutics in diseases affecting the musculoskeletal system. We also present future directions for this biopolymer as well as the necessary research and development steps for their achievement.

5. Demineralized bone matrix as a vehicle for delivering endogenous and exogenous therapeutics in bone repair

Abstract

As a unique human bone extract approved for implant use, demineralized bone matrix (DBM) retains substantial amounts of endogenous osteoconductive and osteoinductive proteins. Commercial preparations of DBM represent a clinically accessible, familiar, widely used and degradable bone-filling device, available in composite solid, strip/piece, and semi-solid paste forms. Surgically placed and/or injected, DBM releases its constituent compounds to bone sites with some evidence for inducing new bone formation and accelerating healing. Significantly, DBM also has preclinical history as a drug carrier by direct loading and delivery of several important classes of therapeutics. Exogenous bioactive agents, including small molecule drugs, protein and peptide drugs, nucleic acid drugs and transgenes and therapeutic cells have been formulated within DBM and released to bone sites to enhance DBM’s intrinsic biological activity. Local release of these agents from DBM directly to surgical sites in bone provides improved control of dosing and targeting of both endogenous and exogenous bioactivity in the context of bone healing using a clinically familiar product. Given DBM’s long clinical track record and commercial accessibility in standard forms and sources, opportunities to formulate DBM as a versatile matrix to deliver therapeutic agents locally to bone sites in orthopedic repair and regenerative medicine contexts are attractive.

6. Nanofiber-based delivery of bioactive agents and stem cells to bone sites

Abstract

Biodegradable nanofibers are important scaffolding materials for bone regeneration. In this paper, the basic concepts and recent advances of self-assembly, electrospinning and thermally induced phase separation techniques that are widely used to generate nanofibrous scaffolds are reviewed. In addition, surface functionalization and bioactive factor delivery within these nanofibrous scaffolds to enhance bone regeneration are also discussed. Moreover, recent progresses in applying these nanofiber-based scaffolds to deliver stem cells for bone regeneration are presented. Along with the significant advances, challenges and obstacles in the field as well as the future perspective are discussed.

 
7. Intra-operatively customized implant coating strategies for local and controlled drug delivery to bone

Abstract

Bone is one of the few tissues in the human body with high endogenous healing capacity. However, failure of the healing process presents a significant clinical challenge; it is a tremendous burden for the individual and has related health and economic consequences. To overcome such healing deficits, various concepts for a local drug delivery to bone have been developed during the last decades. However, in many cases these concepts do not meet the specific requirements of either surgeons who must use these strategies or individual patients who might benefit from them. We describe currently available methods for local drug delivery and their limitations in therapy. Various solutions for drug delivery to bone focusing on clinical applications and intra-operative constraints are discussed and drug delivery by implant coating is highlighted. Finally, a new set of design and performance requirements for intra-operatively customized implant coatings for controlled drug delivery is proposed. In the future, these requirements may improve approaches for local and intra-operative treatment of patients.


8. Local delivery of small and large biomolecules in craniomaxillofacial bone

Abstract

Current state of the art reconstruction of bony defects in the craniomaxillofacial (CMF) area involves transplantation of autogenous or allogenous bone grafts. However, the inherent drawbacks of this approach strongly urge clinicians and researchers to explore alternative treatment options. Currently, a wide interest exists in local delivery of biomolecules from synthetic biomaterials for CMF bone regeneration, in which small biomolecules are rapidly emerging in recent years as an interesting adjunct for upgrading the clinical treatment of CMF bone regeneration under compromised healing conditions. This review highlights recent advances in the local delivery small and large biomolecules for the clinical treatment of CMF bone defects. Further, it provides a perspective on the efficacy of biomolecule delivery in CMF bone regeneration by reviewing presently available reports of pre-clinical studies using various animal models.

9. Immobilized antibiotics to prevent orthopaedic implant infections

Abstract

Many surgical procedures require the placement of an inert or tissue-derived implant deep within the body cavity. While the majority of these implants do not become colonized by bacteria, a small percentage develops a biofilm layer that harbors invasive microorganisms. In orthopaedic surgery, unresolved periprosthetic infections can lead to implant loosening, arthrodeses, amputations and sometimes death. The focus of this review is to describe development of an implant in which an antibiotic tethered to the metal surface is used to prevent bacterial colonization and biofilm formation. Building on well-established chemical syntheses, studies show that antibiotics can be linked to titanium through a self-assembled monolayer of siloxy amines. The stable metal–antibiotic construct resists bacterial colonization and biofilm formation while remaining amenable to osteoblastic cell adhesion and maturation. In an animal model, the antibiotic modified implant resists challenges by bacteria that are commonly present in periprosthetic infections. While the long-term efficacy and stability is still to be established, ongoing studies support the view that this novel type of bioactive surface has a real potential to mitigate or prevent the devastating consequences of orthopaedic infection.

10. Local delivery of nitric oxide: Targeted delivery of therapeutics to bone and connective tissues

Abstract

Non-invasive treatment of injuries and disorders affecting bone and connective tissue remains a significant challenge facing the medical community. A treatment route that has recently been proposed is nitric oxide (NO) therapy. Nitric oxide plays several important roles in physiology with many conditions lacking adequate levels of NO. As NO is a radical, localized delivery via NO donors is essential to promoting biological activity. Herein, we review current literature related to therapeutic NO delivery in the treatment of bone, skin and tendon repair.

Bibliography

  1. Demineralized bone matrix in bone repair: History and use
  2. Biomimetic hydrogels for controlled biomolecule delivery to augment bone regeneration
  3. Calcium phosphate cements as drug delivery materials
  4. Silk constructs for delivery of musculoskeletal therapeutics
  5. Demineralized bone matrix as a vehicle for delivering endogenous and exogenous therapeutics in bone repair
  6. Nanofiber-based delivery of bioactive agents and stem cells to bone sites
  7. Intra-operatively customized implant coating strategies for local and controlled drug delivery to bone
  8. Immobilized antibiotics to prevent orthopaedic implant infections
  9. Local delivery of nitric oxide: Targeted delivery of therapeutics to bone and connective tissues

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Reporter: Venkat Karra, Ph.D.

Researchers at Singapore’s Institute of Bioengineering and Nanotechnology (IBN) have developed a miniaturized biochip that promises to boost the development of more effective cancer drugs.

The Agency for Science, Technology and Research said on Wednesday that its research into the effect of drugs on cancer stem cells (CSCs) would shed light on cells that are resistant to drugs, local TV Channel NewsAsia reported.

It also explained how the technology works on CSCs, which form a small and distinct class of cancer cells in a tumor.

CSCs are more resistant to chemotherapy and if they are not eradicated, CSCs can repopulate the tumor and lead to cancer recurrence. It is therefore important for researchers to understand the efficacy of anti-cancer drugs against CSCs.

However, CSCs are scarce, making up about 1 percent of cancer cells.

This hampers studies using conventional drug screening methods, which require large sample volumes and are slow and expensive.

The IBN researchers found an answer, by developing a miniaturized biological assay, called the Droplet Array. It performs cheaper, faster and more convenient drug screening using limited samples.

In traditional biological assays, microplates — a flat plate with multiple wells in which samples are placed – are commonly used. Each requires at least 2,500 or 5,000 cells, to be present for viable analysis. IBN’s Droplet Array requires only 500 cells for screening. This massive reduction in sample volume saves money and makes it easier to study scarce quantities of target cells, such as CSCs.

IBN executive director, Professor Jackie Y Ying, who led the study, was quoted as saying that the Droplet Array marks a significant breakthrough in nanotechnology and lab-on-a-chip concepts. It also provides an efficient platform to speed up drug screening and development.

source:

http://www.chinadaily.com.cn/xinhua/2012-05-09/content_5868419.html

Reporter: Venkat Karra

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