Functional Biomaterials - Matyjaszewski Polymer Group - Carnegie Mellon University

Functional Biomaterials

Antibacterial Surfaces

Biocidal Magnetic Nanoparticles:

Selective Protein Uptake

Polymer-Protein Conjugates

Block Copolymers for Drug Delivery

Biodegradable Nanogels

Bioengineering Applications:

As noted throughout the web site one of the primary reasons for using a controlled radical copolymerization process for the preparation of a well defined macromolecule is that it is possible to incorporate site selected functional groups into the final copolymer.  On this page we address how the group has worked with others to design materials that express specific bio-responsive properties, including antibacterial, protein conjugates, block copolymers designed for controlled drug delivery and materials designed for intra-cellular interactions. 

Antibacterial Surfaces:

Potentially harmful bacteria abound and pathogenic bacteria are frequently deposited onto surfaces subsequently touched by many people thereby spreading infection.  It would be beneficial to have surfaces that kill bacteria on contact.  Stable non-leaching antimicrobial surfaces are required for long term protection since leaching systems,see following schematic, are eventually exhausted, rendering the material ineffective and posing potential environmental risks.

scheme 1

Quaternary ammonium ion-containing polymers (PQA) are known to effectively kill cells and spores by disrupting cell membranes.  Monomers, such as 2-dimethylaminoethyl methacrylate (DMAEMA), 4-vinyl pyridine (4-VP) and N-substituted acrylamides, that can be quaternized thereby providing biocidal activity, can be polymerized by ATRP.  This means that stable antimicrobial surfaces can be prepared by grafting from(1-3) or grafting onto surfaces.(4)

11k scheme 2

Covalent attachment of PQA via "grafting onto" or "grafting from" provides long-lasting biocidal activity with no danger to the environment. Polymeric surfaces are the most common surfaces encountered in everyday life and recent work has focused on preparing biocidal polymer surfaces.  A non-leachable biocidal polypropylene (PP) surface was created by chemically attaching poly(quaternary ammonium) (PQA) chains to the surface of PP.

A well-defined poly(2-(dimethylamino)ethyl methacrylate) (PDMAEMA), a precursor of a PQA, was grown from the surface of PP via ATRP.(3)  The tertiary ammine groups in PDMAEMA were subsequently converted to a quaternary amine groups in the presence of ethyl bromide

Grafting from:

Polymeric surfaces are the most common surfaces encountered in everyday live and recent work has focused on preparing biocidal polymer surfaces.  A non-leachable biocidal polypropylene (PP) surface was created by chemically attaching poly(quaternary ammonium) (PQA) chains to the surface of PP through a grafting from reaction. A well-defined poly(2-(dimethylamino)ethyl methacrylate) (PDMAEMA), a precursor of a PQA, was grown from the surface of PP via ATRP.(3)  The tertiary ammine groups in PDMAEMA were subsequently converted to quaternary amine groups in the presence of ethyl bromide providing an antibacterial surface that killed over 85% of contacting bacterial even at low graft density.

11k graft from

Successful surface modification was confirmed by ATR-IR, contact angle measurement, and an antibacterial activity test against Escherichia coli (E. coli), (see lower graph in schematic) showed that the biocidal activity of the resultant surfaces depends on the amount of the polymers grafted to the surface, i.e. the number of available quaternary ammonium units.  Surfaces grafted with relatively high MW polymers (Mn > 10,000 g/mol) showed almost 100% killing efficiency, i.e. killing all of the added E. Coli (2.9 × 105) in the shaking test, whereas a lower biocidal activity (85%) was observed for the surface grafted with shorter PQA chains (Mn = 1,500 g/mol).

Many surfaces have inherent functional groups that can be employed to conduct a “grafting from” reaction, the only requirement is the ability to tether initiators to the target substrate.  In the case of paper and glass this is readily accomplished by reacting surface hydroxyl groups with 2-bromoisobutyryl bromide.(2)  ATRP of DMAEMA followed by quaternization with ethyl bromide provided effective tethered biocidal functionality. When paper was treated the modified surfaces were extremely effective at killing E.Coli, reducing the number of cells by four orders of magnitude, from 1.6 x 109 to 4.9 x 105, in one hour.  The surface also showed activity against B. subtilis spores.  The activity of a biocidal film on a glass surface survived repeated washing with aqueous detergent solution.

It is envisioned that such a permanent, nonleaching biocidal surface treatment would find utility in food packaging facilities, household items and military applications.

Grafting onto:

While grafting from is an efficient method of tethering quaternizable polymers to a substrate a more convenient approach for existing household equipment, and even hospital use, would be a "consumer friendly" "grafting onto" approach such as spraying a solution of a reactive copolymer onto a surface.  In order to demonstrate the ‘grafting onto' approach PDMEAMA/PTMSPMA block copolymers of different molecular weights and different backbone topology were prepared via ATRP and immobilized on a glass surface by simple immersion of the glass slide in an aqueous solution of the copolymer.(4)

11k graft to

 The efficiency of the tethering reaction was measured by addition of 1% of the sodium salt of fluorescein to the DMAEMA block prior to immersing the glass slide in the solution.  Desorption of the dye after washing provided a measurement of the concentration of grafted chains on the surface. Grafting density was dependent on concentration and molecular weight of the copolymer as well as reaction time, with higher molecular weight copolymers providing lower graft density.  Antibacterial activity depended only on the concentration of quaternary ammonium units tethered to the surface. 

The interaction between bacteria and poly(quaternary ammonium) was investigated and the ability of the modified surfaces to kill bacteria was tested. Treated glass samples were incubated with a suspension of E. coli.   The test results showed that the treated glass killed 104 ~ 106 of the contacting bacteria.   Biocidal efficiency increased with the amount of quaternary ammonium units on the surface.  Rather surprisingly introduction of hydrophobic units into a poly(quaternary ammonium) segment led to 100 times enhancement of biocidal activity with a log/kill of 7.0.

11kcopolkills 2

Modification of surfaces with tethered/tetherable polymers is applicable to a variety of surfaces. Control of surface morphology can be achieved by patterning the initiator layer and subsequent graft polymerization. Further variation of surface morphology can be achieved by phase separation on the nanoscale thereby providing precision surface modification.

A simple broadly applicable grafting to approach to form an antibacterial surface was developed by conducting an ATRP copolymerization of the precursor to an antibacterial monomer unit and a photoresponsive monomer, e.g. a monomer containing a benzophenone or xanthone functionality that can be modified after controlled radical polymerization to form a radical.  A solution of the antibacterial/photoresponsive copolymer was deposited on a polymeric surface with an abstractable proton, such a polypropylene, and then exposure to light both crosslinks the deposited film and tethers it to the substrate.(7, 8)

11k graft onto surface film

Since the copolymer is both water soluble and photoresponsive it can be deposited as an aqueous film on a surface and exposed to light, or if desired exposed to UV light through a photo-mask to form a patterned hydrogel.
Many different polymeric surfaces could be functionalized using similar chemistry and it is envisioned that such a permanent, nonleaching biocidal surface treatment would find utility in hospitals, food packaging facilities, household items and military applications.

Biocidal Magnetic Nanoparticles:

An extension of the use of preparing biocidal surfaces was the preparation of antibacterial magnetic particles via “grafting from”. (9)   Highly efficient recyclable antibacterial magnetite nanoparticles consisting of a magnetic Fe3O4 core with an antibacterial poly(quaternary ammonium) (PQA) coating.
11k mag particles

The concept was to use these particles to purify water, considering that the EPA indicated that 90% of the world’s water is contaminated.  The advantages of using magnetic particles grafted with polymer chains that provide antibacterial properties over present procedures are:
a)    that there would be no release of chemicals as the biocide is attached to the particle,
b)    as indicated by the test determining killing efficiency the particles could kill bacteria with high efficiency due to the inherent large surface and,
c)    after or during use the particles could be recycled by application of a magnetic field.
11k clean water

The validity of this concept was confirmed when the PQA-modified magnetite nanoparticles were dispersed in water and exhibited a response to an external magnetic field, making the nanoparticles easy to remove from water as shown below.

11k magnetic property

The PQA-modified magnetite nanoparticles retained 100% biocidal efficiency against E. Coli (105 to 106 E. Coli/mg nanoparticles) during eight exposure/collect/recycle procedures without washing with any solvents or water.
Another advantage of surface-initiated ATRP is that it allows one to precisely design the morphology and properties of the tethered polymer brushes. Indeed a gradient surface with varied grafting density and molecular weight of the tethered polymer chains has been successfully prepared by surface-initiated ATRP. (10)

11k gradient formed11k gradient

The dry layer thickness of the polymer brushes was controlled by polymerization time and/or initiator density on the surface.

This ability to control all aspects surface structure allows the properties of the antimicrobial polymer brushes to be rationally tailored. A combinatorial screening tool was developed to elucidate the role of chain length and chain density on cell kill in a single experiment.

11k plus 1

The results indicate that surface charge density, is a critical element in designing a surface for maximum kill efficiency. The biocidal surfaces that were most efficient had charge densities of greater than 1 - 5 X 1015 accessible quaternary amine units/cm2.

11k Killing efficiency

Biocidal surfaces are not the only type of bio-responsive surfaces that can be created from tethered poly(2-(dimethylamino)ethyl methacrylate) (PDMAEMA) brushes.

Selective Protein Uptake:

Surface plasmon resonance was used to measure binding of proteins from solution to poly(2-(dimethylamino)ethyl methacrylate) (PDMAEMA) brushes end-grafted from gold surfaces. (11)   These brushes displayed a high capacity for electrostatically selective protein uptake. The net negatively charged protein BSA was taken up in amounts that approach its aqueous solubility limit in the case of PDMAEMA brushes at high grafting densities. These are among the highest reported protein binding capacities for ion exchange media. BSA binding scaled linearly with the mass of PDMAEMA grafted per unit area, with a constant ratio of approximately 120 DMAEMA monomer units per bound BSA molecule. The kinetics of BSA uptake in the brush is considerably more rapid than the slow asymptotic approach to adsorption saturation that is often seen for BSA adsorption to a solid surface. The high affinity for BSA was evident in the complete lack of desorption from the brush when rinsing with dilute NaCl solutions. BSA desorption from the brush required changes in solution pH and/or ionic strength to eliminate its net electrostatic attraction to PDMAEMA. Desorption could be achieved by using pH and/or ionic strength changes to interfere with the electrostatic attraction for BSA.
In contrast, PDMAEMA had no affinity for the net positively charged protein lysozyme. These results indicate that particles with tethered PDMAEMA chains can provide a charge selective, high capacity ion exchange medium for protein binding.
One important advantage of grafting from method via CRP, specifically ATRP, is the ease with which specific surfaces can be functionalized with initiating moieties for the preparation of well-defined high-density of polymer brushes. The highest grafting density can reach up to 1 chain/nm2.  In that case, the polymer chain has a stretched conformation which is quite different from those of the semi-dilute polymer brushes previously studied, leading to very unique properties.

Polymer-Protein Conjugates:

The field of polymer bioconjugation (i.e. covalent attachment of synthetic polymers to biological entities such as nucleic acids, oligopeptides, proteins, enzymes, carbohydrates, viruses or cells) has evolved rapidly during the last decade. (12, 13)   Polymer bioconjugates were initially developed by biochemists and had been exclusively studied for bio-medical applications. However, within the last few years the utility of this novel class of macromolecules has expanded and they are being examined in many groups in emerging areas of materials science. (14-17)  Both the bio-component and the attached polymer based segment can span a range of complexity and functionality (18) and the synthesis of well-defined functional polymer bioconjugates has emerged as a central topic in macromolecular engineering.
A review paper which describes recent changes and progress in the field of bioconjugation; i.e. covalent attachment of synthetic polymers to biological entities such as nucleic acids, oligopeptides, proteins, enzymes, carbohydrates, viruses or cells, has been provided by two former group members. (16)  The covalent conjugation approach can utilize either “grafting from” a tethered initiator (-I) or “grafting to” a functional group such as (-NH2) in which a preformed telechelic polymer is reacted with the targeted protein. (19)

11k conjugation

The advantage of prior “grafting to” techniques are the ability to form protein-polymer hybrid conjugates with predefined polymers while the disadvantages are that the formed bioconjugates are hard to purify and the “grafting to” reaction can generate non-uniform products.  Nevertheless modern copper catalyzed synthetic methods such as ATRP and ‘‘click’’ chemistry coupling reactions have recently proven to be extremely versatile tools for the preparation of tailor-made polymer bioconjugates. (16, 20)  One widely applied procedure for preparing bioconjugates includes preparation of functional telechelic polymers for direct attachment to the target bioresponsive molecules. (21)  This procedure frequently employs transformation of terminal groups on polymers prepared by ATRP for subsequent click reactions. (22-24)  In a recently published collaboration with Román’s group in Spain smart heparin based bioconjugates were prepared using ATRP and click chemistry. (25)  α-Azido functionalized PMDAETA and P(EO2MA-co-OEOMA300) polymers were prepared by AGET ATRP while the –COOH groups on bemiparin were reacted with propargylamine to generate alkynyl side groups. Click coupling was accomplished in the presence of CuSO4•5H2O and sodium ascorbate and the complex purified by dialysis.  The bio-conjugates were both temperature and pH-responsive with the LCST values of the heparin bioconjugate scaling linearly with the composition of the copolymer segment.

The reverse approach where a targeted bio-responsive molecule is functionalized with an initiator for an ATRP, exemplified below by Streptavidin, followed by “grafting from” to tether a copolymer of desired composition and molecular weight to the functional bio-molecule is also receiving increased levels of attention. (26-28)

11k PPC 1 

An example of a composite structure prepared by this route is the synthesis of near-uniform protein-polymer conjugates by initiating ATRP of monomethoxy poly(ethylene glycol)-methacrylate from 2-bromoisobutyramide derivatives of chymotrypsin, a protein-initiator. (12)  However, initially the protein-polymer conjugates synthesized by this novel technique only retained 50-86% of the original enzyme activity and also suffered from challenging purification of intermediates and/or the inability to efficiently control the number or location of potential polymer connections, all of which compromised the structural integrity of the modified protein.
In order to address this deficiency and exemplify a general method for producing homogeneous recombinant proteins that contain a polymer initiator, or a functionality that can be converted into the desired functionality, at defined sites on the protein an amino acid containing a functional group that can act as an initiator for an ATRP was designed.  The amino acid, 4-(2′-bromoisobutyramido)-phenylalanine, shown on the left hand side in the following scheme, can function as an initiator in ATRP and would also provide a stable linkage between that particular amino acid that was specifically designed to be genetically incorporated into a specific site in a formed protein, and subsequent growing a polymer chain from that specific unit.  
A green fluorescent protein was selected as the exemplary protein as any conformational change in the protein can result in the loss of fluorescence and so the molecule can provide a direct measurment of the “severity” of the conditions employed for the ATRP. Polymerization initiated from the green fluorescent protein genetically modified at position 134 by incorporation of the amino acid modified to contain an ATRP initiator resulted in formation of a conjugate containing a single high MW polymer chain per protein molecule. (29) 

The advantages of genetically engineering proteins are that they maintain the highest possible protein functionality, 95% with retention of tertiary structure in the case of GFP1, by protecting active sites and avoid structural weak regions and protection of immune active sequences while allowing precise control of initiator loading via amber codon. The resulting GFP1-poly(OEOMA) showed thermoresponsive behavior and retained activity.
This work was extended to allow an ARGET ATRP polymerization from a genetically encoded cleavable initiator to allow direct analysis of the grafted polymer after cleavage of the ester linkage in addition to providing enhanced initiation efficiency due to the faster initiation of secondary esters compared to corresponding amides. (30)  The polymerization was conducted under biologically compatible conditions (31) using very low concentrations of catalyst and slow continuous addition of ascorbic acid in the presence of added halide salts to ensure the presence of a stable catalyst deactivator even at concentrations of catalyst as low as 300 ppm.  The cleaved POEMA segments had Mw/Mn lower than 1.3.
11k thermoresponsive

The protein conjugate could be incorporated into nanogels to assist in cellular delivery.  This was accomplished by conducting a copolymerization of PEGMA and a PEG-dimethacrylate coinitiated by a combination of the GFP1-initiator and a PEG-Br initiator.  The resulting nanogels provided a unique platform for protein delivery and enzymatic solid support systems.  The successful incorporation of GFP1 demonstrates that proteins can be encapsulated whilst maintaining their tertiary structure.  Retained terminal functionality was used to attach catalase which converts hydrogen peroxide into water and oxygen thereby providing a simple assay for activity.
Composite structures prepared by this route include synthesis of near-uniform protein-polymer conjugates by initiating atom transfer radical polymerization of monomethoxy poly(ethylene glycol)-methacrylate from 2-bromoisobutyramide derivatives of chymotrypsin (a protein-initiator). (13)  Protein-polymer conjugates synthesized by this novel technique retained 50-86% of the original enzyme activity.
Advantages of genetically engineering proteins are that one maintains highest possible protein functionality by protecting active sites thereby avoiding any structurally weak regions and protection of immune active sequences through precise control of initiator loading via amber codon.  Increasing the number of conjugated 2-bromoisobutyramide initiators per molecule of protein increased the MW and Mw/Mn of the final protein-polymer conjugates. The generic nature of this technique was demonstrated by initiating polymerization of nonionic, cationic, and anionic monomers from the protein-initiator. The technique described herein should be useful in synthesizing well-defined protein-polymer conjugates exhibiting a wide range of physical and chemical properties.
Functional nanoparticles have also been conjugated with bioresponsive molecules. (12)  The synthetic procedure involved combining surface-initiated polymerization from magnetic nanoparticles with subsequent conjugation of the biologically active molecules generated materials. The products exhibited good separation capability and binding-specificity for bio-molecules. Polymeric shells of non-biofouling poly(poly(ethylene glycol) methacrylate) were initially introduced onto the surface of magnetic nanoparticles by surface-initiated ATRP. (32) This step was followed by successful post-functionalization via activation of the polymeric shells and bioconjugation of biotin. The resulting hybrids showed a bio-specific binding property for streptavidin and could be separated by magnet capture. (33)
Non-covalent bioconjugation approaches are based on formation of an ionic complex through electrostatic interactions. (34)  The requirements for delivery are that the bioconjugate forms a stable delivery system that allows prolonged circulation in the blood stream while incorporating functionality for targeted delivery through incorporation of specific ligands for receptors on target cells.  The size of the nanogels control the rate of cellular uptake and incorporation of biodegradable links allows for controlled release of the delivered biomolecules. (35)
Another non-covalent approach involving preparation of delivery systems that does not require direct linkage of the biologically active agent to the synthetic polymer includes synthesis of cationically functionalized degradable star polymers for Short Interfering RNA, (siRNA) delivery. (36) This non-covalent bioconjugation approach is also based on formation of an ionic complex through electrostatic interactions. (35)

siRNA delivery

The requirements for delivery are that the bioconjugate forms a stable delivery system that allows prolonged circulation in the blood stream while incorporating functionality for targeted delivery through incorporation of specific ligands for receptors on target cells on the periphery of the first formed star.  The size of the nanogels control cellular uptake and incorporation of biodegradable links allows for controlled release of the delivered biomolecules. (37)  PEG based stars with cationic cores were evaluated for in vitro nucleic acid delivery. (38)  The star polymers were combined with either plasmid DNA (pDNA) or short interfering RNA (siRNA) duplexes to form polyplexes for intracellular delivery. These polyplexes with either siRNA or pDNA were highly effective for NA delivery, particularly at relatively low star polymer weight or molar ratios, when tested with a dual luciferase reporter assay (Dual-Glo luciferase reporter assay, Promega) in Drosophila Schneider 2 (S2) cells highlighting the importance of NA release in efficient delivery systems.  Most effective transfection results were obtained at lower ratios RW1, RW0.2, and RW0.02. They outperformed the current standard FuGENE-HD/siRNA conjugate.  These results indicate that PEG-based star polymers with a cationic core can be utilized as efficient nonviral carriers for NA delivery, especially at relatively low RW or RM ratios.

Short Interfering RNA, (siRNA) was discovered in 1999. (39)  siRNA is a double stranded RNA with 20-25 nucleotides with the negative charge due to the phosphate groups.  There has been progress in developing cationic vectors for non-viral systemic gene therapy for treating hereditary diseases, but its potential role in the treatment of acquired diseases such as cancer is now widely recognized. (35)  Dendrimers have been developed for siRNA delivery across the cell membrane (40) which would indicate that star macromolecules (41) which possess a similar core/shell structure with multiple arms, multiple surface functionality, and a globular topology should also work. The arm first route to star synthesis (42, 43) was employed to prepare PEG-star macromolecules a degradable core and incorporated peripheral functionality to tailor the stars for siRNA delivery to MC3T3-E1.4 cells. (44)  Details of the synthesis were provided in the paper and successful degradation of PEG Stars using glutathione and under a physiological concentration of GSH demonstrated.  siRNA formed a complex with the cationically charged DMAEMA/QDMAEMA core and confocal microscopy analysis showed complete cellular uptake in 24 hours.  Another approach discussed was the preparation of N3-PEG Stars for siRNA delivery is being conducted in collaboration with Leroux’s group in Switzerland.  The targeting agent is “clicked” to the star prior to siRNA complexation.

Surfaces for cell tissue engineering:

The final “star” topic is preparation of surfaces for cell tissue engineering.  A series of photo-cross-linkable thermoresponsive poly(oligo ethylene oxide)methacrylate star polymers were designed to control of cell-surface interactions.  The star macromolecules were prepared and deposited on a polystyrene surface. The star polymers covalently attached onto surfaces allowed a control of cell shrinkage and attachment in response to temperature changes. (45)

11k surface modification

Continuing efforts focus on preparation of protein-polymer hybrids utilizing biologically compatible ATRP systems to overcome the current disadvantages of grafting-from methods. This requires development of aqueous ATRP systems with very low amounts of catalyst, solvent, and monomer polymerizable at room temperature, eATRP is one approach being evaluated.  siRNA delivery systems are being developed that include biodegradable polymer scaffolds or biodegradable cationic nanogels.

Biodegradable Nanogels:

Stable biodegradable poly(oligo (ethylene oxide) monomethyl ether methacrylate), (POEOMA) nanogels, cross-linked with biodegradable linkages were prepared by conducting ATRP in a cyclohexane inverse miniemulsion copolymerization in the presence of a disulfide-functionalized dimethacrylate crosslinker. (46, 47)  Biodegradable nanogels prepared by ATRP have several advantages over “classical” carriers for drug delivery applications since the networks are more uniform and degradation is more efficient.  These nanogels could be used for targeted drug delivery scaffolds for biomedical applications since they can be degraded into lower molecular weight polymers to release the encapsulated (bio)molecules.  These materials were proven to be nontoxic to cells and were biocompatible. (48)

degrade nanogels

The nanogels consist of a uniform three-dimensional network, since they are prepared by a controlled polymerization process, and are capable of entrapping drugs, proteins, and nucleic acids and delivering them to specific targets.  These nanogels can be degraded to individual polymeric chains using glutathione tripeptide, which is commonly found in cells at mM concentrations, as a reducing agent to release the encapsulated biomolecules. The encapsulation and controlled release of florescent dyes and Doxorubicin (Dox), an anticancer drug, was reported. (49)   Results obtained from optical fluorescence microscope images and live/dead cytotoxicity assays of HeLa cancer cells suggested that the released Dox molecules penetrated cell membranes and therefore could suppress the growth of cancer cells.

Hydroxy-functionalized poly(oligo(ethylene oxide) monomethyl ether methacrylate) (HO-POEOMA) was prepared by AGET ATRP of OEOMA initiated by 2-hydroxyethyl 2-bromoisobutyrate in water, or in an inverse miniemulsion of water/cyclohexane, at ambient temperature to demonstrate facile applicability of the HO-POEOMA toward bioconjugation with biotin, pyrene, and GRGDS peptide. (50)  The number of biotin molecules in each nanogel was determined to be 142,000 and the formation of bioconjugates of nanogels with avidin was confirmed using optical fluorescence microscopy.  In addition, ATRP and click chemistry offered an efficient route for the synthesis of telechelic di-biotin polymers. These general methods can be applied to the formation of different functional materials conjugated with proteins, dyes, nucleic acids, and drugs.

ATRP allows the preparation of nano-gel materials with many useful features.

  • First, the resulting particles preserve a high degree of halide end-functionality to enable further chain extension to form functional block copolymers or functionalization with biorelevant molecules by utilizing click reactions.
  • Second, they are degradable in a reducing environment to individual polymeric chains with predeterminable molecular weight and relatively narrow molecular weight distribution (Mw/Mn < 1.5), indicating the formation of a uniformly cross-linked network in the individual particles. This uniform structure is anticipated to improve control over the release of encapsulated agents.
  • Third, properties including swelling ratio, degradation behavior, and colloidal stability of particles prepared by ATRP are superior to those prepared by conventional free radical inverse miniemulsion polymerization.
  • Fourth, nanogels will enhance circulation time in the blood, because they can consist of poly(oligo(ethylene oxide) monomethyl ether methacrylate) (POEOMA), an analogue of linear poly(ethylene oxide) (PEO) that can prevent nanoparticle uptake by reticuloendothelial system (RES).

These unique properties suggest that the well-defined functional nanogels prepared by this newly developed method hold great potential as useful biomaterials for biological and biomedical applications  The procedure was also used to entrapped rhodamine isothiocyanate-dextran (RITC-Dx) as a model for water-soluble biomacromolecular drugs. (17)  UV-Vis spectroscopy was used to characterize the extent of incorporation of RITC-Dx into the nanogels. The loading efficiency of RITC-Dx into the nanogels exceeded 80%. These nanogels were degraded into polymeric solutions in a reducing environment to release the encapsulated carbohydrate drugs. The released carbohydrate biomolecules specifically interacted with Concanavalin A in water, suggesting that the biodegradable nanogels could be used as carriers to deliver carbohydrate drugs that can be released upon degradation to bind to pathogens based on lectins.

release 5

The images above show (a) a suspension of nanogels containing RITC-dextran in water before and after the addition of dithiothreitol (DTT) and optical fluorescence microscopy images of nanogels loaded with RITC-dextran before (b) and after (c) degradation in water. The scale bars in images b and c are 50 μm. These results demonstrate that biodegradation of the functional nanogels can trigger the release of encapsulated molecules including RTIC-Dx and rhodamine 6G (fluorescent dyes), and Doxorubicin (Dox), an anticancer drug, as well as facilitate the removal of empty vesicles from the body.  A review of this topic was provided by the research group in conjunction with the collaborators. (51)
Another example of the synthesis of biodegradable materials for a specific envisioned application was the preparation of poly(N-isopropylacrylamide-co-5,6-benzo-2-methylene-1,3-dioxepane) (poly(NIPAAm-co-BMDO)) copolymer which was synthesized by a combination of ATRP and reversible addition-fragmentation chain transfer (RAFT) polymerization. The lower critical solution temperature (LCST) of the poly (NIPAAm) and poly(NIPAAm-co-BMDO) copolymers were measured using UV-vis spectroscopy to determine the effect of varying the amount of incorporated BMDO. (52)   The material prepared is degradable and possesses a LCST above room temperature and below body temperature, making it a potential candidate for use as an injectable tissue engineering scaffold to enhance fracture repair.
The combination of ATRP and RAFT enabled preparation of polymers with control over molecular weight, up to Mn = 50,000 g/mol and Mw/Mn < 1.2.  Degradation studies were performed in basic solution and in complete Dulbecco's modified Eagle medium. The cytotoxicity of the material and its degradation products were analyzed by in vitro cell culture analyses, including cytotoxicity live/dead and CyQUANT cell proliferation assays.  The materials consisted of crosslinked scaffolds with degradable units within the polymer backbone and at the crosslinking sites and were prepared using an ester-containing diacrylate crosslinker. Furthermore, incorporation of a GRGDS peptide sequence improved cell attachment to the gels providing further evidence that controlled/living radical polymerization techniques allow for precise control over macromolecular structure exemplified in this paper by synthesis of materials suitable as a scaffold for tissue engineering.
11k nano 6

The influence of the degree of methacrylation on hyaluronic acid hydrogels properties was examined. (52)  The properties of hyaluronic acid (HA) hydrogels having a broad range of degree of methacrylation were determined and it was shown that increasing the solubility of glycidyl methacrylate (GM) in a co-solvent mixture during the methacrylation of HA with GM produced photopolymerizable HAGM conjugates with degrees of methacrylation (DM) ranging from 14% up to 90%. Aqueous solutions of HAGM macromonomers were photocross-linked to yield hydrogels with nearly complete vinyl group conversions after 10 min exposure under ultraviolet light (UV). The hydrogels were characterized by uniaxial compression and volumetric swelling measurements. In one series of examples, keeping the DM constant, the shear modulus was varied from 16 kPa up to 73 kPa by varying the macromonomer concentration. However, at a given macromonomer concentration while varying the degree of methacrylation of the hyaluronic acid (HA) hydrogels the shear modulus varied from 22 kPa up to 65 kPa. Preliminary in-vitro cell culture studies showed that GRGDS modified HAGM hydrogels promoted similar cell interactions at both low and high degrees of methacrylation, 32% and 60%, respectively. Densely cross-linked hydrogels with high degrees of methacrylation have been shown to be more mechanically robust while maintaining cytocompability and cell adhesion.
Extending this the work on hyaluronic acid hydrogels resulted in development of a new method to prepare nanostructured hybrid hydrogels by incorporating well-defined poly(oligo (ethylene oxide) monomethyl ether methacrylate) (POEO300MA) nanogels of sizes 110-120 nm into larger three-dimensional (3D) matrix forming hydrogels that are suitable for drug delivery scaffolds for tissue engineering applications. (53)  Rhodamine B isothiocyanate-labeled dextran (RITC-Dx) or fluorescein isothiocyanate-labeled dextran (FITC-Dx)-loaded POEO300MA nanogels with pendant hydroxyl groups were prepared by activators generated electron transfer atom transfer radical polymerization (AGET ATRP) in cyclohexane inverse miniemulsion. Hydroxyl-containing nanogels were functionalized with methacrylated groups to generate photoreactive nanospheres. 1H NMR spectroscopy confirmed that copolymerizable nanogels were successfully incorporated covalently into 3D hyaluronic acid-glycidyl methacrylate (HAGM) hydrogels after free radical photopolymerization.  The introduction of disulfide moieties into the polymerizable groups resulted in a controlled release of nanogels from the cross-linked HAGM hydrogels in the presence of a reducing environment. The effect of gel hybridization on the macroscopic properties (swelling and mechanics) was studied and the results showed that swelling and nanogel content are independent of scaffold mechanics.  In-vitro assays showed the nanostructured hybrid hydrogels were cytocompatible and the GRGDS (Gly-Arg-Gly-Asp-Ser) contained in the nanogel structure promoted cell-substrate interactions within 4 days of incubation.  These nanostructured hydrogels provide potential utility as an artificial extracellular matrix (ECM) impermeable to low molecular weight bio-active molecules with controlled pharmaceutical release capability. Moreover, the nanogels can provide controlled drug or bio-molecule delivery, while hyaluronic acid based-hydrogels can act as a macroscopic scaffold for tissue regeneration and regulator for nanogel release.
A further extension of biocompatible nanogels for bio-engineering applications was demonstrated by in situ entrapment of gold nanoparticles (AuNPs), bovine serum albumin (BSA), rhodamine B isothiocyanate-dextran (RITC-Dx), and fluoresceine isothiocyanate-dextran (FITC-Dx) during an atom transfer radical polymerization (ATRP) in cyclohexane inverse miniemulsion. (54)  The nanogels consisted of poly(oligo(ethylene oxide) monomethyl ether methacrylate) (POEOMA), an analog of linear poly(ethylene oxide) which can prevent nanoparticle uptake by reticuloendothelial systems, that were covalently attached to a GRGDS peptide sequence for targeted delivery.  The nanogels were cross-linked using poly(ethylene oxide) dimethacrylate and initiated by a hydroxyl-functionalized initiator. Cell uptake of the AuNP-loaded nanogels was verified using transmission electron microscopy (TEM). Cell internalization of BSA-loaded nanogels was confirmed using fluorescence microscopy after the addition of a fluorescently tagged antibody for BSA, and by running a western blot of the cell extracts. Confocal imaging of RITC-Dx-loaded nanogels demonstrated that the nanogels were internalized, and the location of the nanogels was confirmed by staining for actin and nuclei, as well as by following along the z-axis. Furthermore, co-localization of the RITC signal with a signal for an FITC-conjugated antibody for clathrin indicated that the nanogels enter via clathrin mediated endocytosis. The internalization of FITC-Dx-loaded nanogels with and without GRGDS into cells was quantified using flow cytometry and exceeded 95%.
These results confirmed that uniform nanogels prepared by ATRP in inverse miniemulsion are endocytosed and are applicable as drug delivery devices.

11k GRDS

These results, and examples discussed in a more recent review article, (55) confirm that uniform nanogels prepared by ATRP in inverse miniemulsion are endocytosed and are applicable as drug delivery devices.  Indeed the review article highlighted the fact that inverse miniemulsion ATRP was able to prepare stable sub-micron sized particles with diameter from 100 to 300 nm and narrow size distribution in the presence of a disulfide or polyester-functionalized crosslinker forming crosslinked biodegradable nanogels that were non-toxic when exposed to cells.  The nanogel particles were capable of being loaded with various water soluble biomolecules and inorganic nanoparticles at high loading levels and high yield. Fluorescent dyes, AuNPs, and anticancer drugs were incorporated by physical loading, high molecular weight carbohydrates and proteins were incorporated by in-situ physical incorporation, and star branched polymeric nanoparticles by in-situ covalent incorporation. The nanogels crosslinked with polyester or disulfide linkages were biodegraded either in aqueous media or in the presence of biocompatible reducing agents such as glutathione, naturally present within cells. Upon degradation, encapsulated anticancer drugs such as Dox were released in a controlled manner to kill cancer cells. Carbohydrate drugs released from nanogels were bound to lectin such as ConA.
Since the nanogels preserved bromine chain end functionality this enabled further chain extension and selected modification and functionalization of the nanogels with biorelated molecules. Functional nanogels were also prepared by copolymerization with functional monomers or through the use of functional ATRP initiators. They were further functionalized with biorelated molecules, such as cell-adhesive peptides, targeting proteins and antibodies, resulting in the formation of nanogel bioconjugates. Finally, ATRP-nanogels had higher swelling ratios, better colloidal stability, and more controlled degradation than FRP-nanogels. These overall results suggest that well-defined functional nanogels may have potential as carriers for controlled drug delivery scaffolds to target specific cells.
Future design and development of effective microgel/nanogel based DDS utilizing CRP methods (not only ATRP) for in vivo applications to target cancer cells require a higher degree of control over properties. Targeted dimensions are in the range of 100 nm diameter, with a rapid environmental response for enhanced loading level, novel functionality for further bioconjugation, and biodegradability for sustained release of drugs. CRP in inverse microemulsion polymerization could produce nanogels with diameter less than 50 nm and with a uniform crosslinked network for better swelling.  Appropriate selection of environmentally responsive water-soluble and water-swellable monomers will enable development of biomaterials responsive to external stimuli. In addition, introduction of acid-labile degradation linkages with/or without disulfide linkages will allow the DDS to be effectively degraded in the presence of targeted cancer cells.

Block Copolymers for Drug Delivery:

Acrylate-based block copolymers were prepared by ATRP as matrices for paclitaxel delivery from coronary stents. (56, 57)  A series of multiblock acrylate-based copolymers, synthesized by ATRP were evaluated as drug delivery matrixes for the controlled release of paclitaxel from coronary stents. The copolymers consisted of poly(butyl acrylate) or poly(lauryl acrylate) soft blocks and hard blocks composed of poly(methyl methacrylate), poly(isobornyl acrylate), or poly(styrene) homo- or copolymers. Depending on the ratio of hard to soft blocks in the copolymers, coating formulations were produced that possessed variable elastomeric properties, resulting in stent coatings that maintained their integrity when assessed by SEM imaging of over-expanded stents. In vitro paclitaxel release kinetics from coronary stents coated with these copolymers typically showed an early release burst followed by sustained release behavior, which permitted the elution of the majority of the paclitaxel over a 10-day time period. It was determined that neither the nature of the polyacrylate (butyl or lauryl) nor that of the hard block appeared to affect the release kinetics of paclitaxel at a loading of 25% drug by weight, whereas some effects were observed at lower drug loading levels.  Differential scanning calorimetry (DSC) analysis indicated that the paclitaxel was at least partially miscible with the poly(butyl acrylate) phase of those block copolymers.
The copolymers were also evaluated for sterilization stability by exposing both the copolymer alone and copolymer/paclitaxel coated stents to e-beam radiation at doses of 1-3 times the nominal dose used for medical device sterilization (25 kGy). It was found that the copolymers containing blocks bearing quaternary carbons within the polymer backbone were less stable to the radiation and showed a decrease in molecular weight as determined by GPC. Conversely, those block copolymers without quaternary carbons showed no significant change in molecular weight when exposed to 3 times the standard radiation dose. There was no significant change in drug release profile from any of the acrylate-based copolymers after exposure to 75 kGy of e-beam radiation, and this was attributed to the inherent radiation stability of the poly(butyl acrylate) center block.
A “greener” SARA ATRP catalyst was developed for the synthesis of PDMAEMA segmented copolymers by chain extension from cholesterol (CHO-Br) and PEG-Br. The iron0/CuII PMDETA based catalyst provided linear kinetics for the chain extension reactions with the PEG-Br initiator.  The poor solubility of IPA CHO-Br in water was expected to lead to poor initiation efficiency but kinetics were linear generating bio-relevant block copolymers with narrow molecular weight distribution. (58)

Degradable Nanogels for Drug Delivery:

RDRP procedures have several inherent advantages for the preparation of functional materials for bio-related applications since in vivo applications require a high degree of control over the properties of the materials targeting specific environments. The requirements include particle stability for prolonged circulation in the blood stream, incorporation of peripheral functionality for further bioconjugation, controlled particle size with uniform diameter, and biodegradability for sustained release of drugs over a desired period of time and facile removal/degradation of empty devices.  RDRP procedures such as ATRP provide a versatile route for preparation of (co)polymers with controlled molecular weight, narrow molecular weight distribution (i.e., Mw/Mn, or PDI < 1.5), designed architectures, and useful site specific chain end-functionality.
One of the initial steps towards preparing materials for bio-applications, within the Matyjaszewski group, started with incorporation of cross-linkers with degradable functionality, consisting of reversible redox cleavage of disulfide groups, into well-defined copolymers. (59) The evolution of the concept to resulted in formation of star macromolecules with bio-degradable cores (60) and bio-degradable gels (61)  Such microgel/nanogel particles were evaluated as drug delivery carriers for biological and other biomedical applications.  Disulfide linkages were selected as the degradable linkage to exploit tumor hypoxia in cancer treatment. (62)
The concept was further expanded by the evaluation of the utility of inverse miniemulsion ATRP to prepare well defined functionalized stable nanoparticles of water/swellable crosslinked polymers. The particles consisted of poly(oligo(ethylene glycol) monomethyl ether methacrylate) (POEOMA) containing a fraction, up to 100%, of degradable cross-linkages. (46)  The use of ATRP for the formation of the degradable nanogels provided particles with higher degrees of swelling than materials prepared by standard free radical polymerization methods in both water, and organic solvents in addition to providing the ability to incorporate site selected functionality into the delivery vehicles. These nanogels could be used as targeted drug delivery scaffolds for biomedical applications, since the uniformly cross-linked network improved control over the rate of release of encapsulated agents.  The nanogels underwent biodegradation forming water-soluble polymeric fragments, with a relatively narrow molecular weight distribution (Mw/Mn =1.5), and molecular weight below the renal threshold, confirming the formation of a uniformly crosslinked network in the individual particles.
degradable particle
The uniform structure of the dual crosslinked particle was anticipated to improve control over the release of encapsulated agents in the presence of a biocompatible glutathione tripeptide, which is commonly found in cells. The biodegradation of the nanogels was exemplified by the triggered release of encapsulated molecules, including a fluorescent dye rhodamine 6G, and doxorubicin, an anticancer drug, as well as facilitating the removal of empty vehicles.

11k degrade

These nanogels can be degraded to individual polymeric chains using a reducing agent, including glutathione tripeptide, which is commonly found in cells at mM concentrations, to release the encapsulated biomolecules.  These materials were proven to be nontoxic to cells and are biocompatible.


Results obtained from optical fluorescence microscope images and live/dead cytotoxicity assays of HeLa cancer cells suggested that the released doxorubicin molecules penetrated cell membranes and therefore could suppress the growth of cancer cells.
Biodegradable nanogels loaded with rhodamine B isothiocyanate-dextran (RITC-Dx) as a model for water-soluble biomacromolecular drugs were prepared using ATRP in a cyclohexane inverse miniemulsion in the presence of a disulfide-functionalized dimethacrylate cross linker. UV-vis spectroscopy was used to characterize the extent of incorporation of RITC-Dx into the nanogels. The loading efficiency of RITC-Dx into the nanogels exceeded 80%. These nanogels were degraded into polymeric sols in a reducing environment to release the encapsulated carbohydrate drugs. The released carbohydrate biomolecules specifically interacted with Con A in water, suggesting that the biodegradable nanogels could be used as carriers to deliver carbohydrate drugs that can be released upon degradation to bind to pathogens based on lectins. A similar procedure was used to load Dox and gold nanoparticles (AuNP) and loading was between 5.4.and16.4 wt% Dox depending upon initial ratio of Dox to nanogel and approximately 42% by mass of incorporated AuNP. (50, 54)  
An extension of the work reported in earlier papers (18, 46)  allowed the preparation of biomaterials with many useful features incorporated into the nanoparticles during the polymerization and using the incorporated site specific functionalities for post polymerization click functionalization providing a final product which can encapsulate bio-related molecules and/or inorganic nanoparticles such as pigments silica or quantum dots.  The halogen functionality can be converted to another desired functionality, such as a group that will partake in a click conjugation reaction (63) while retaining the ability to be degraded in specific environments and release the encapsulated agents at a controlled rate. (17)
11k click onto

The procedures employed for this work have been summarized in reference (55) and a recent paper provided details on the cellular uptake of functional nanogels prepared by inverse miniemulsion ATRP with encapsulated proteins, carbohydrates, and gold nanoparticles and confirmed cellular uptake of nanogels was verified by transmission electron microscopy, gel electrophoresis, western blotting, confocal microscopy, and flow cytometry. (54)

The following figure shows the viability of HeLa cells after incubation for 48, 72, and 96 h. in three different systems that together show the validity of this approach to drug delivery, where the three colored bars represent:

(a) basic control without nanogels;

(b) Dox-loaded nanogels (0.4 mg/mL), where glutathione (0.08 mg/mL) was added after 48 h incubation to release Dox from Dox-loaded nanogels;

(c) control, where free Dox (0.064 mg/mL) was added after 48 h incubation.

11k ghs addition

11k nanogel degrade 2

Polyplex formation between the qNG and nucleic acid exemplified by plasmid DNA (pDNA) and short interfering RNA (siRNA duplexes) were prepared and evaluated.

11k siren pdna complexes

The delivery of the polyplexes was optimized for the delivery of pDNA and siRNA to the Drosophila Schneider 2 (S2) cell-line. The qNG/nucleic acid (i.e., siRNA and pDNA) polyplexes were found to be highly effective in their capabilities to deliver their respective payloads.  The qNGs complexed pDNA and siRNA at relatively low weight ratios of qNG to DNA (R5) and qNG to siRNA (R15), respectively, as observed in agarose gel electrophoresi and provided a robust delivery system for nucleic acids, both plasmid DNA (~5 kb) as well as siRNA. In order to characterize the ability of different ratios of qNG to transfect siRNA, a Dual-luciferase reporter assay was utilized to rapidly and accurately screen knockdown efficiency. A maximum reporter knockdown was obtained at R0.2, suggesting more effective transfection than the current standard siRNA-Fugene-HD.

11k star kill ratio

For plasmid DNA transfection, the maximum firefly luciferase reporter signal was observed at R30. These results confirm that qNGs are a promising platform for pDNA and siRNA delivery.

11k delivery dna

The use of magnetically directed nanoparticles for delivery of a drug is another application for bioactive nanoparticles. (65)  A nanogel particle prepared by copolymerization of (diethyleneglycol) methyl ether methacrylate and a disulfide crosslinker in a microemulsion polymerization (66) was loaded with ferric oxide nanoparticles modified by oleic acid, size ~15 nm.  The formed PM(EO)2MA displays a lower critical solution temperature (LCST) ~ 25oC. The magnetic nanoparticles were then loaded with ropivacaine to form a MNP/Ropiv complex.

 11k ropivacaine

The MNP/Ropiv complex with magnetic application at the ankle of a rat resulted in irreversible release of the ropivacaine. The free drug acted on the nerves with which it came in contact. Delivery of a safe dose of ropivacaine via the MNP/Ropiv complex was 14 times higher than delivery by injection.

Another exemplification of the utility of nanostructured polymers for siRNA delivery was provided by a study on delivery targeting a mammalian cell line, murine calvarial preosteoblastlike cells embryonic day 1 subclone 4 (MC3T3-E1.4).  Both stars and nanogels were tested for delivery and lower quantities of nanogels were needed to attain the same level of knockdown as the star polymers; there was no statistical difference between the knockdown efficiencies of the nanogel 5:1 and star 200:1 groups. The level of Gapdh knockdown in a mammalian cell is consistent with other cationic polymeric systems. The conclusion was that both star polymers and nanogels were biocompatible, and successfully complexed and delivered Gapdh siRNA, and suppressed Gapdh mRNA production to levels comparable to that of Lipofectamine® RNAiMAX. This underscores that the architecture of these NSPs do not compromise biocompatibility while maintaining knockdown efficiency.

Functional star molecules

As indicated above functional star molecules provide another approach to prepare functional materials for cellular internalization of transported agents. This was exemplified by the preparation of poly(ethylene glycol) (PEG) star polymers containing GRGDS (Gly-Arg-Gly-Asp-Ser) peptide sequences on the star periphery. The functionalized star molecules were synthesized by ATRP of poly(ethylene glycol) methyl ether methacrylate (PEGMA), GRGDS modified poly(ethylene glycol) acrylate (GRGDS-PEG-Acryl), fluorescein o-methacrylate (FMA) macromonomer, and ethylene glycol dimethacrylate (EGDMA) via an “arm-first” method.

11k GRDS 7

The star polymers were approximately 20 nm in diameter, as measured by dynamic light scattering and atomic force microscopy.  Conjugation of FMA to the stars was confirmed by fluorescence microscopy, and successful attachment of GRGDS segments to the star periphery was confirmed by 1H NMR spectroscopy. Both fluorescent PEG star polymers with and without peripheral GRGDS peptide segments were cultured with MC3T3-E1.4 cells. These star polymers were biocompatible with greater than 90% cell viability after 24 h of incubation. Cellular uptake of PEG star polymers in MC3T3-E1.4 cells was observed by confocal microscopy. Rapid uptake of PEG star polymers with GRGDS peptides (100% of FITC-positive cells in 15 min measured by flow cytometry) was observed, suggesting enhanced delivery potential of these functional star polymers. (44)

The concept behind using stars for delivery applications was that the size of the core of the star could be adjusted to provide an appropriate degree of complexation that allowed good siRNA complexation but also sufficiently week complexation that allowed release. This balance could be attained by adjusting the degree of protonation in the core. (36, 44)  The conditions for the preparation of the star copolymer that provided the best result is shown below.


Mw, THF GPC(×103)




Mw, MALLS(×103)



Dh (nm)




81 %

87 %





 There was complexation between the core of the star and siRNA at low star to siRNA ratios as measured by zeta potential and a star ratio to siRNA of 0.02 to 0.2 provided better enzyme silencing than FuGENE while DNA star delivery for enzyme expression was improved, with a performance better than FUGENE-HD, at ratio of star to DNA of 15.

11k sirna delivery plot


(1)    Yu, W. H.;  Kang, E. T.;  Neoh, K. G.; Zhu, S. Journal of Physical Chemistry B 2003, 107, 10198-10205.
(2)    Lee, S. B.;  Koepsel, R. R.;  Morley, S. W.;  Matyjaszewski, K.;  Sun, Y.; Russell, A. J. Biomacromolecules 2004, 5, 877-882.
(3)    Huang, J.;  Murata, H.;  Koepsel, R. R.;  Russell, A. J.; Matyjaszewski, K. Biomacromolecules 2007, 8, 1396-1399.
(4)    Huang, J.;  Koepsel, R. R.;  Murata, H.;  Wu, W.;  Lee, S. B.;  Kowalewski, T.;  Russell, A. J.; Matyjaszewski, K. Langmuir 2008, 24, 6785-6795.
(5)    Xing, T.;  Hu, W.;  Li, S.; Chen, G. Applied Surface Science 2012, 258, 3208-3213.
(6)    Xing, T.;  Liu, J.; Li, S. Textile Research Journal 2013, 83, 363-370, 368 pp.
(7)    Huang, J.;  Cusick, B.;  Pietrasik, J.;  Wang, L.;  Kowalewski, T.;  Lin, Q.; Matyjaszewski, K. Langmuir 2007, 23, 241-249.
(8)    Huang, J.;  Russell, A. J.;  Tsarevsky, N. V.; Matyjaszewski, K. In PCT Int. Appl.; (University of Pittsburgh-Of the Commonwealth System of Higher Education, USA; Carnegie Mellon University). WO 2008021500, WO 2008021500; p 77pp.
(9)    Dong, H.;  Huang, J.;  Koepsel, R. R.;  Ye, P.;  Russell, A. J.; Matyjaszewski, K. Biomacromolecules 2011, 12, 1305-1311.
(10)    Murata, H.;  Koepsel, R. R.;  Matyjaszewski, K.; Russell, A. J. Biomaterials 2007, 28, 4870-4879.
(11)    Kusumo, A.;  Bombalski, L.;  Lin, Q.;  Matyjaszewski, K.;  Schneider, J. W.; Tilton, R. D. Langmuir 2007, 23, 4448-4454.
(12)    Lele, B. S.;  Murata, H.;  Matyjaszewski, K.; Russell, A. J. Biomacromolecules 2005, 6, 3380-3387.
(13)    Jones, M.-C.;  Ranger, M.; Leroux, J.-C. Bioconjugate Chemistry 2003, 14, 774-781.
(14)    Nicolas, J.;  Mantovani, G.; Haddleton, D. M. Macromolecular Rapid Communications 2007, 28, 1083-1111.
(15)    Lutz, J.-F.;  Boerner, H. G.; Weichenhan, K. Aust. J. Chem. 2007, 60, 410-413.
(16)    Lutz, J.-F.; Boerner, H. G. Progress in Polymer Science 2008, 33, 1-39.
(17)    Oh, J. K.;  Drumright, R.;  Siegwart, D. J.; Matyjaszewski, K. Prog. Polym. Sci. 2008, 33, 448-477.
(18)    Oh, J. K.;  Siegwart, D. J.;  Lee, H.-i.;  Sherwood, G.;  Peteanu, L.;  Hollinger, J. O.;  Kataoka, K.; Matyjaszewski, K. J. Am. Chem. Soc. 2007, 129, 5939-5945.
(19)    Heredia, K. L.; Maynard, H. D. Organic & Biomolecular Chemistry 2007, 5, 45-53.
(20)    Kolb, H. C.;  Finn, M. G.; Sharpless, K. B. Angew. Chem., Int. Ed. 2001, 40, 2004-2021.
(21)    Sumerlin, B. S.;  Tsarevsky, N. V.;  Louche, G.;  Lee, R. Y.; Matyjaszewski, K. Macromolecules 2005, 38, 7540-7545.
(22)    Bontempo, D.;  Heredia, K. L.;  Fish, B. A.; Maynard, H. D. J. Am. Chem. Soc. 2004, 126, 15372-15373.
(23)    Le Droumaguet, B.;  Mantovani, G.;  Haddleton, D. M.; Velonia, K. J. Mat.Chem. 2007, 17, 1916-1922.
(24)    Geng, J.;  Mantovani, G.;  Tao, L.;  Nicolas, J.;  Chen, G.;  Wallis, R.;  Mitchell, D. A.;  Johnson, B. R. G.;  Evans, S. D.; Haddleton, D. M. J. Am. Chem. Soc. 2007, 129, 15156-15163.
(25)    Reyes-Ortega, F.;  Parra-Ruiz, F. J.;  Averick, S. E.;  Rodriguez, G.;  Aguilar, M. R.;  Matyjaszewski, K.; San Roman, J. Polym. Chem. 2013, 4, 2800-2814.
(26)    Golas, P. L.; Matyjaszewski, K. Chemical Society Reviews 2010, 39, 1338-1354.
(27)    Heredia, K. L.;  Bontempo, D.;  Ly, T.;  Byers, J. T.;  Halstenberg, S.; Maynard, H. D. J. Am. Chem. Soc. 2005, 127, 16955-16960.
(28)    Broyer, R. M.;  Quaker, G. M.; Maynard, H. D. J. Am. Chem. Soc. 2008, 130, 1041-1047.
(29)    Peeler, J. C.;  Woodman, B. F.;  Averick, S.;  Miyake-Stoner, S. J.;  Stokes, A. L.;  Hess, K. R.;  Matyjaszewski, K.; Mehl, R. A. J. Am. Chem. Soc. 2010, 132, 13575-13577.
(30)    Averick, S. E.;  Bazewicz, C. G.;  Woodman, B. F.;  Simakova, A.;  Mehl, R. A.; Matyjaszewski, K. European Polymer Journal 2013, 49, 2919-2924.
(31)    Averick, S.;  Simakova, A.;  Park, S.;  Konkolewicz, D.;  Magenau, A. J. D.;  Mehl, R. A.; Matyjaszewski, K. ACS Macro Lett. 2012, 1, 6-10.
(32)    Kang, S. M.;  Choi, I. S.;  Lee, K.-B.; Kim, Y. Macromol. Res. 2009, 17, 259-264.
(33)    Kang, S. M.;  Lee, B. S.;  Kim, W.-J.;  Choi, I. S.;  Kil, M.;  Jung, H.-j.; Oh, E. Macromol. Res. 2009, 17, 174-180.
(34)    Averick, S. E.;  Magenau, A. J. D.;  Simakova, A.;  Woodman, B. F.;  Seong, A.;  Mehl, R. A.; Matyjaszewski, K. Polym. Chem. 2011, 2, 1476-1478.
(35)    Morille, M.;  Passirani, C.;  Vonarbourg, A.;  Clavreul, A.; Benoit, J.-P. Biomaterials 2008, 29, 3477-3496.
(36)    Cho, H.-Y.;  Srinivasan, A.;  Hong, J.;  Hsu, E.;  Liu, S.-G.;  Shrivats, A.;  Kwak, D.;  Bohaty, A. K.;  Paik, H.-J.;  Hollinger, J. O.; Matyjaszewski, K. Biomacromolecules 2011, 12, 3478–3486.
(37)    Allen, T. M.; Cullis, P. R. Science 2004, 303, 1818-1822.
(38)    Cho, H. Y.;  Averick, S. E.;  Paredes, E.;  Wegner, K.;  Averick, A.;  Jurga, S.;  Das, S. R.; Matyjaszewski, K. Biomacromolecules 2013, 14, 1262-1267.
(39)    Hamilton, A. J.; Baulcombe, D. C. Science 1999, 286, 950-952.
(40)    Blow, N. Nat. Methods 2009, 6, 305-309.
(41)    Gao, H.; Matyjaszewski, K. Prog. Polym. Sci. 2009, 34, 317-350.
(42)    Gao, H.; Matyjaszewski, K. Macromolecules 2006, 39, 3154-3160.
(43)    Zhang, X.;  Xia, J.; Matyjaszewski, K. Macromolecules 2000, 33, 2340-2345.
(44)    Cho, H. Y.;  Gao, H.;  Srinivasan, A.;  Hong, J.;  Bencherif, S. A.;  Siegwart, D. J.;  Paik, H.-j.;  Hollinger, J. O.; Matyjaszewski, K. Biomacromolecules 2010, 11, 2199-2203.
(45)    Park, S.;  Cho, H. Y.;  Yoon, J. A.;  Kwak, Y.;  Srinivasan, A.;  Hollinger, J. O.;  Paik, H.-j.; Matyjaszewski, K. Biomacromolecules 2010, 11, 2647-2652.
(46)    Oh, J. K.;  Tang, C.;  Gao, H.;  Tsarevsky, N. V.; Matyjaszewski, K. J. Am. Chem. Soc. 2006, 128, 5578-5584.
(47)    Oh, J. K.;  Perineau, F.; Matyjaszewski, K. Macromolecules 2006, 39, 8003-8010.
(48)    Siegwart, D. J.;  Oh, J. K.; Matyjaszewski, K. Prog. Polym. Sci. 2012, 37, 18-37.
(49)    Siegwart, D. J.;  Oh, J. K.;  Gao, H.;  Bencherif, S. A.;  Perineau, F.;  Bohaty, A. K.;  Hollinger, J. O.; Matyjaszewski, K. Macromol. Chem. Phys. 2008, 209, 2179-2193.
(50)    Oh, J. K.;  Siegwart, D. J.; Matyjaszewski, K. Biomacromolecules 2007, 8, 3326-3331.
(51)    Siegwart, D. J.;  Bencherif, S. A.;  Srinivasan, A.;  Hollinger, J. O.; Matyjaszewski, K. J. Biomed. Mater. Res., Part A 2008, 87A, 345-358.
(52)    Bencherif Sidi, A.;  Srinivasan, A.;  Horkay, F.;  Hollinger Jeffrey, O.;  Matyjaszewski, K.; Washburn Newell, R. Biomaterials 2008, 29, 1739-1749.
(53)    Bencherif, S. A.;  Siegwart, D. J.;  Srinivasan, A.;  Horkay, F.;  Hollinger, J. O.;  Washburn, N. R.; Matyjaszewski, K. Biomaterials 2009, 30, 5270-5278.
(54)    Siegwart, D. J.;  Srinivasan, A.;  Bencherif, S. A.;  Karunanidhi, A.;  Oh, J. K.;  Vaidya, S.;  Jin, R.;  Hollinger, J. O.; Matyjaszewski, K. Biomacromolecules 2009, 10, 2300-2309.
(55)    Oh, J. K.;  Bencherif, S. A.; Matyjaszewski, K. Polymer 2009, 50, 4407-4423.
(56)    Richard, R. E.;  Schwarz, M.;  Ranade, S.;  Chan, A. K.;  Matyjaszewski, K.; Sumerlin, B. Biomacromolecules 2005, 6, 3410-3418.
(57)    Richard, R. E.;  Schwarz, M.;  Ranade, S.;  Chan, A. K.;  Matyjaszewski, K.; Sumerlin, B. ACS Symposium Series 2006, 944, 234-251.
(58)    Cordeiro, R. A.;  Rocha, N.;  Mendes, J. P.;  Matyjaszewski, K.;  Guliashvili, T.;  Serra, A. C.; Coelho, J. F. J. Polym. Chem. 2013, 4, 3088-3097.
(59)    Tsarevsky, N. V.; Matyjaszewski, K. Macromolecules 2002, 35, 9009-9014.
(60)    Gao, H.;  Tsarevsky, N. V.; Matyjaszewski, K. Macromolecules 2005, 38, 5995-6004.
(61)    Tsarevsky, N. V.; Matyjaszewski, K. Macromolecules 2005, 38, 3087-3092.
(62)    Brown, J. M.; Wilson, W. R. Nat. Rev. Cancer 2004, 4, 437-447.
(63)    Lutz, J.-F.;  Boerner, H. G.; Weichenhan, K. Macromolecular Rapid Communications 2005, 26, 514-518.
(64)    Averick, S. E.;  Paredes, E.;  Irastorza, A.;  Shrivats, A. R.;  Srinivasan, A.;  Siegwart, D. J.;  Magenau, A. J.;  Cho, H. Y.;  Hsu, E.;  Averick, A. A.;  Kim, J.;  Liu, S.;  Hollinger, J. O.;  Das, S. R.; Matyjaszewski, K. Biomacromolecules 2012, 13, 3445-3449.
(65)    Mantha Venkat, R. R.;  Nair Harsha, K.;  Venkataramanan, R.;  Gao Yuan, Y.;  Matyjaszewski, K.;  Dong, H.;  Li, W.;  Landsittel, D.;  Cohen, E.; Lariviere William, R. Anesthesia and analgesia 2014.
(66)    Dong, H.;  Mantha, V.; Matyjaszewski, K. Chem. Mater. 2009, 21, 3965-3972