Table of Contents

Cover

Title Page

Related Titles
Copyright
List of Contributors
Preface

Chapter 1: Biomaterials for Biomedical Applications

1.1 Introduction
1.2 Polymers as Hydrogels in Cell Encapsulation and Soft Tissue Replacement
1.3 Biomaterials for Drug Delivery Systems
1.4 Biomaterials for Heart Valves and Arteries
1.5 Biomaterials for Bone Repair
1.6 Conclusion
Abbreviations
References

Chapter 2: Conducting Polymers: An Introduction

2.1 Introduction
2.2 Types of Conducting Polymers
2.3 Synthesis of Conducting Polymers
2.4 Surface Functionalization of Conducting Polymers
Abbreviations
References

Chapter 3: Conducting Polymers: Biomedical Applications

3.1 Applications
3.2 Conclusions
Abbreviations
References

Chapter 4: Plasma-Assisted Fabrication and Processing of Biomaterials

4.1 Introduction
4.2 Conclusion
References

Chapter 5: Smart Electroactive Polymers and Composite Materials

5.1 Introduction
5.2 Types of Electroactive Polymers
5.3 Polymer Gels
5.4 Conducting Polymers
5.5 Ionic Polymer–Metal Composites (IPMC)
5.6 Conjugated Polymer
5.7 Piezoelectric and Electrostrictive Polymers
5.8 Dielectric Elastomers
5.9 Summary
References

Chapter 6: Synthetic Polymer Hydrogels

6.1 Introduction
6.2 Polymer Hydrogels
6.3 Synthetic Polymer Hydrogels
6.4 Applications of Synthetic Polymer Hydrogels
6.5 Conclusion
Abbreviations
References

Chapter 7: Hydrophilic Polymers

7.1 Introduction
7.2 Classification
7.3 Applications of Hydrophilic Polymers
7.4 Conclusions
Abbreviations
References

Chapter 8: Properties of Stimuli-Responsive Polymers

8.1 Introduction
8.2 Physically Dependent Stimuli
8.3 Chemically Dependent Stimuli
8.4 Biologically Dependent Stimuli
8.5 Dual Stimuli
8.6 Multistimuli-Responsive Materials
8.7 Conclusion
Abbreviations
References

Chapter 9: Stimuli-Responsive Polymers: Biomedical Applications

9.1 Introduction
9.2 Imaging
9.3 Sensing
9.4 Delivery of Therapeutic Molecules
9.5 Other Applications
9.6 Conclusion
Abbreviations
References

Chapter 10: Functionally Engineered Sol–Gel Derived Inorganic Gels and Hybrid Nanoarchitectures for Biomedical Applications

10.1 Introduction
10.2 Some of the Useful Definitions of Various Gel Forms
10.3 Inorganic Metal-Oxide Gels and Hybrid Nanoarchitectures
10.4 Sol–Gel Synthesis of Inorganic Metal-Oxide Gels
10.5 Physically Cross-Linked Inorganic and Hybrid Gel
10.6 Sol–Gel Derived Hybrid Metal-Oxides Nanostructures
10.7 Biomedical Applications of Sol–Gel Derived Inorganic and Hybrid Nanoarchitectures for Both Therapeutic and Diagnostic (Theranostics) Functions
10.8 Sol–Gel Matrices for Controlled Drug Delivery
10.9 Stimuli-Responsive Drug Delivery Systems
10.10 Sol–Gel Matrix Targeted Cancer Therapy
10.11 Sol–Gel Matrices for Imaging and Radiotherapy (Radiolabeling)
10.12 Concluding Remarks and Future Perspectives
Acknowledgment
Abbreviations
References

Chapter 11: Relevance of Natural Degradable Polymers in the Biomedical Field

11.1 Introduction
11.2 Natural Biopolymers and Its Application
11.3 Conclusion
Abbreviations
References

Chapter 12: Synthetic Biodegradable Polymers for Medical and Clinical Applications

12.1 Introduction
12.2 Polyesters/Poly(α-hydroxy acids)
12.3 Poly(glycolide)
12.4 Polylactide
12.5 Poly(lactic-co-glycolic) Acid
12.6 Poly(-caprolactone)
12.7 Polyurethanes
12.8 Polyanhydrides
12.9 Polyphosphazenes
12.10 Polyhydroxyalkanoates
12.11 Polyorthoesters
12.12 Poly(propylene fumarate)
12.13 Polyacetals
12.14 Polycarbonates
12.15 Polyphosphoesters
12.16 Synthesis and Application of Different Modified Synthetic Biopolymer
12.17 Conclusion
Abbreviations
References

Index

End User License Agreement

List of Illustrations

Chapter 1: Biomaterials for Biomedical Applications

Figure 1.1 Polymer hydrogels used for tissue replacement.
Figure 1.2 Biomaterials utilized for various drug delivery systems.
Figure 1.3 Polymers for artificial vascular grafts.
Figure 1.4 Polymer based matrix for bone repair.

Chapter 2: Conducting Polymers: An Introduction

Figure 2.1 A schematic of the electrochemical synthesis setup [72].

Chapter 3: Conducting Polymers: Biomedical Applications

Figure 3.1 Everything is connected in the world of conductive polymers [28].
Figure 3.2 Schematic representation of functioning of polypyrrole microcontainer electrochemical system.
Figure 3.3 Biosensors classification.
Figure 3.4 TEM and log impedance (Z) versus time plot of the PANI-CSA-Ni nanowire (red line) after exposure to cigarette smoke and log impedance response with time of PANI-CSA (black line) in the presence of cigarette smoke.
Figure 3.5 PANI-NF sensors.
Figure 3.6 Scheme of self-assembled monolayers of ATQD-RGD.
Figure 3.7 Conductive wrinkle topographies on PDMS. (a) Schematic diagram of wPPy formation. (b) Images of PPy wrinkle-coated PDMS for cell culture applications: a photograph of the wPPy-on-PDMS (top), its optical microscopic image (middle), and a fluorescent image of NIH3T3 cells grown on the wPPy substrate (bottom).
Figure 3.8 (a) The preparation of NGF-doped porous polypyrrole surfaces and (b) cellular interaction with a porous surface in the presence of electrical stimulation.

Chapter 4: Plasma-Assisted Fabrication and Processing of Biomaterials

Figure 4.1 (a, b) Optical images of myoblast cells cultured on the single-cell patterning substrates. (c) AFM image of a single cell adopting the triangular shape of the pattern feature.
Figure 4.2 Optical images of live neurons cultured on the hexagonal grid pattern, after incubation times of (a, b) 4 days, (c) 7 days, and (d) 21 days.
Figure 4.3 VSMC adhered (first day) and grown (fifth day) on pristine and plasma treated PE (a), and 3T3 adhered (first day) and grown (third day) on pristine and plasma treated PE (b).
Figure 4.4 Surface dependent focal adhesion formation (denoted by arrows). Cells were seeded on (a) PLLA, (b) PLLA-gAA-chitosan, and (c) PLLA-gAA-gelatin at a seeding density of 10⁴ cell cm⁻² and cultured for 12 h. Scale = 20 µm.
Figure 4.5 Cell morphology observed on (a) PLLA, (b) PLLA-gAA-gelatin, and (c) PLLA-gAA-chitosan by SEM at day 7. Complete endothelialization was observed on both modified PLLA substrates, but not on PLLA substrate. Scale = 100 µm.
Figure 4.6 (A) Optical microscopic images of DI water droplets showing the difference of oxygen and nitrogen plasma treatment on maintaining the hydrophilic nature of Si-DLC surface. The oxygen treated surfaces exhibit prolonged wettability by showing consistent wetting angle measured for a period of 20 days, whereas nitrogen treated surface lost its hydrophilic nature. (Orlanda 2010 [143]. American Chemical Society.) (B) Variation of sp³/sp² ratio with respect to silicon doping concentration in DLC film. (Ahmed 2013 [144]. Reproduced with permission of Elsevier.) (C) SEM images showing platelet adhesion on substrates coated with TIN, A-Si and F-DLC coatings. The adhered platelets are significantly reduced in F-DLC films (g and h) compared to others.
Figure 4.7 (A) The SEM images showing the antibacterial activity of DLC film against bacterium E. coli and P. aeruginosa. The bacterium tends to lose its shape with cytoplasmic projections indicating the rupturing of cell wall when bacteria come in contact with DLC films. (Marciano 2011 [153]. Reproduced with permission of Elsevier.) (B) The TEM images describing the antibacterial activity of Cu embedded nanostructured DLC film against bacterium S. aureus and E. coli. The cytoplasm leakage is clearly visible (arrow marked region) due to destruction of cell walls by Cu diffusion. The inset picture represents the adhered bacterium S. aureus (round morphology) and E. coli (tubular morphology) on glass substrate for the same incubation time.
Figure 4.8 (A) The SEM micrographs showing the stability of DLC films over TIN coatings for 10⁴ cycles of impact fatigue test. The DLC film does not show cohesive or adhesive failure during the course of the experiment. (Wang 2010 [164]. Reproduced with permission of Elsevier.) (B) Wear volume produced by metal-on-metal and DLC-on-DLC pairs with respect to number of test runtime. The smooth DLC pairs exhibit significantly reduced wear volume compared to MoM pairs.

Chapter 5: Smart Electroactive Polymers and Composite Materials

Figure 5.1 Conventional self-oscillating gel.
Figure 5.2 Poly(hydroxyethyl methacrylate).
Figure 5.3 Structures of common conducting polymers.
Figure 5.4 Mechanism of ionic polymer–metal composites.
Figure 5.5 Schematic of direct piezoelectric effect; (a) piezoelectric material, (b) energy generation under tension, (c) energy generation under compression.
Figure 5.6 Principle of dielectric elastomer actuators.

Chapter 6: Synthetic Polymer Hydrogels

Figure 6.1 Classification of hydrogels.
Figure 6.2 Structure of PNIPAM.
Figure 6.3 PNIPAM solution (a) below and (b) above sol–gel transition temperature [23].
Figure 6.4 Structure of poly acrylic acid.
Figure 6.5 Structure of poly(HEMA).
Figure 6.6 Structure of PEG.
Figure 6.7 Structure of (a) poly(ethylene glycol methacrylate) (PEGMA) and (b) poly(ethylene glycol dimethacrylate) (PEGDMA).
Figure 6.8 Structure of PEGMA.
Figure 6.9 Chemical structure of (a) poly(glycolic acid), (b) poly(lactic acid).
Figure 6.10 Structure of Polyvinyl pyrrolidone.

Chapter 7: Hydrophilic Polymers

Figure 7.1 Classification of hydrophilic polymers based on source.
Figure 7.2 Structure of Agarose.
Figure 7.3 Structure of inulin.
Figure 7.4 Structure of chitosan.
Figure 7.5 Schematic illustration of chitosan's versatility. At low pH (less than about 6), chitosan's amine groups are protonated conferring polycationic behavior to chitosan. At higher pH (above about 6.5), chitosan's amines are deprotonated and reactive.
Figure 7.6 Structure of cellulose.
Figure 7.7 Structure of HPMC.
Figure 7.8 Structure of HEC.
Figure 7.9 Structure of Na-CMC [62].
Figure 7.10 Structure of HPCTS.
Figure 7.11 N-Carboxybutyl chitosan and 5-methylpyrrolidinone chitosan.
Figure 7.12 Structure of PAAM.
Figure 7.13 Structure of PAA.
Figure 7.14 Structure of PEO.
Figure 7.15 Generic structure of poly[(organo)phosphazenes].
Figure 7.16 Structure of PHPMA.
Figure 7.17 Structure of DIVEMA and sodium salt of DIVEMA.
Figure 7.18 Chemical structures of three types of POZ [117].
Figure 7.19 Structure of PVP.
Figure 7.20 Structure of PNIPAM.
Figure 7.21 Structure of PVA.

Chapter 8: Properties of Stimuli-Responsive Polymers

Figure 8.1 Classification of stimuli-responsive polymers.
Figure 8.2 Thermoresponsive gelation mechanisms of PNIPAM-HA and PNIPAM-gelatin [7].
Figure 8.3 Formation of nanocages from polymers of PEG (blue), PPG (red), and methacrylate groups (green).
Figure 8.4 Molecular structures of oligo(ethylene glycol) methacrylates frequently used for synthesizing thermoresponsive biocompatible polymers [85].
Figure 8.5 l-Asparagines and aspartic acid [89].
Figure 8.6 (a, b) AFM topographical images and (c, d) schematics of PDMS–PEO brushes ((a, c) 33% PDMS, (b, d) 56% PDMS) in air z scale – 10 nm.
Figure 8.7 (a, b) AFM topographical images and (c, d) schematics of PDMS–PEO brushes ((a, c) PDMS 33%, (b, d) PDMS 56%) in water z scale – 25 nm.
Figure 8.8 Schematic illustration for fabricating a stretchable dry adhesive with micropillars.
Figure 8.9 PDMAEMA polymer end functionalized with azobenzene, which can be stimulated by light, temperature, and change of the pH value [187].
Figure 8.10 Stimuli-responsive polymer system with causal interaction [190].

Chapter 9: Stimuli-Responsive Polymers: Biomedical Applications

Figure 9.1 Classification of biomedical application of smart polymer.
Figure 9.2 Demonstrations of the pNIPAM actuators stimulated by human skin temperature and sunlight. (a) Wearable sheet actuated by skin temperature wraps around a finger. (b) Schematic of the smart curtain design. Photos of (c) before sunlight exposure (closed), (d) after exposure for 15 min (open), and (e) after terminating sunlight exposure (closed).
Figure 9.3 Fluorescence reflectance imaging of a nude mouse (a, b, c) before and (d, e, f) 3 h after the injection of GadoSiPEG2C (K, kidneys; B, bladder). Fluorescence reflectance imaging of some organs after dissection (g) of a control mouse (no particles injection) and (h) of the nude mouse visualized on pictures (a–f). (i) Fluorescence reflectance imaging of a nude mouse after the injection of GadoSi2C (particles without PEG). Each image is acquired with an exposure time of 200 ms.
Figure 9.4 Fluorescence images of solutions containing 7 at (a) pH 7.6 and (b) pH 6.8 when the solutions are irradiated at 330 nm.
Figure 9.5 Dispersion–flocculation behavior of magnetite-PNIPAM nanoparticles, as a function of temperature and magnetic field (concentration = 20 mg ml⁻¹).
Figure 9.6 (a) Light-controlled formation of DNA duplex based on azobenzene isomerization in the hydrogel. (b) Reversible volume transition of the DNA-cross-linked hydrogel regulated by UV and visible light.
Figure 9.7 Cumulative drug releases from micelles at different temperatures.
Figure 9.8 Biological testing of membranes: (b–g) tissue response to implanted nanogelloaded membrane (25% nanogel, 27% ferrofluid) after 4 and 45 days of implantation: (b) top view, 4 days postimplantation; (c) histological section of membrane–tissue interface, 400× magnification; (d) histological section of capsule inflammatory response, 100× magnification; (e) top view, 45 days postimplantation; (f) histological section of membrane–tissue interface, 40× magnification; (g) histological section of capsule inflammatory response, 400× magnification.
Figure 9.9 Targeting mechanism of gene delivery in nanoparticle systems.
Figure 9.10 Various drug delivery systems for drug and gene delivery.
Figure 9.11 Cells (in red, with blue nuclei) interact with the tissue-engineered scaffold through chemical (green ovals) and mechanical stimuli and with each other (yellow circles). These interactions define the cell microenvironment and guide cellular function and differentiation.
Figure 9.12 L929 cell culture on NIPAM–MMA copolymer. (a) Phase-contrast micrograph after 72 h and (b) neutral red-stained cells indicating their viability on copolymer.

Chapter 10: Functionally Engineered Sol–Gel Derived Inorganic Gels and Hybrid Nanoarchitectures for Biomedical Applications

Figure 10.1 Classification of various types of gels.
Figure 10.2 Classification of gels based on nature of solvent.
Figure 10.3 Classification of gels based on physical interactions.
Figure 10.4 Classification of gels based on drying techniques.
Figure 10.5 (a) Flow curve representing various types of rheological behavior. (b) Viscosity curve of a pseudoplastic and dilatant gel. (c) Viscosity–time curve of thixotropic gels.
Figure 10.6 The two main types inorganic gels derived from sol–gel technique are colloidal and polymeric gel.
Figure 10.7 Basic synthesis scheme for the metal-oxide aerogels.
Figure 10.8 Various materials obtained by sol–gel technology and its processing route.
Figure 10.9 An overview of various external stimuli-triggered formation of soft gel for designing functional soft biomaterial.
Figure 10.10 (a) Photograph of thixotropically reversible alumino-siloxane gel. (b) Step-strain time dependent rheological analysis of the alumino-siloxane gel. (c) Schematic representation of possible structural changes in aquagel subjected to shear flow.
Figure 10.11 General synthetic pathway for (A) mesoporous silica (B) mesoporous inorganic–organic hybrid silica.
Figure 10.12 Different methods adopted for drug loading in aerogel matrix. (a) Addition of drug before gelation in sol–gel synthesis. (b) Addition of drug during aging process in sol–gel process. (c) Addition of drugs in pure (dried) aerogels obtained after sol–gel synthesis.
Figure 10.13 (a) Step-strain time-dependent rheological analysis demonstrating the mechano-responsive (thixotropic) behavior of alumino-siloxane gels. (b) In vitro release profile of fluconazole from various alumino-siloxane gels formulations and marketed Flucos gel, with 0.5% (w/w) fluconazole loading, at physiological pH 7.4 and temperature 37 ± 1 °C.
Figure 10.14 (a) Ordered mesoporous materials new perspective for controlled drug delivery systems and (b) bone regeneration for tissue engineering.
Figure 10.15 Various external and internal stimuli suitable for a smart drug delivery system from sol–gel mesoporous silica.
Figure 10.16 Schematic of the stimuli-responsive delivery system (magnet-MSN) based on mesoporous silica nanorods capped with superparamagnetic iron oxide nanoparticles. The controlled release mechanism of the system is based on reduction of the disulfide linkage between the Fe₃O₄ nanoparticle caps and the linker-MSN hosts by reducing agents such as DHLA.
Figure 10.17 Schematic representation of the CdS nanoparticle-capped mesoporous silica-based drug/neurotransmitter delivery system. The controlled release mechanism of the system is based on chemical reduction of the disulfide linkage between the CdS caps and the mesoporous silica-hosts.
Figure 10.18 Schematic representations of administrative route followed by mesoporous nanostructured material developed for cancer targeted therapy.
Figure 10.19 Schematic illustration of a multi-responsive nanogated ensemble based on supramolecular polymeric network-capped mesoporous silica.
Figure 10.20 Schemes of the immobilizations of (i) APTES and (ii) FA-NHS molecules on the luminescent Eu:NPS surfaces and (iii) targeting and (iv) imaging of the proliferated HeLa cells by visible-light excitation and luminescence.
Figure 10.21 (A) A schematic illustration of the synthesis of 64Cu-NOTA-mSiO₂-PEG-TRC105. Uniform mSiO₂ nanoparticles (1) were first modified with –SH groups to form mSiO₂-SH (2). mSiO₂-SH was PEGylated with Mal-PEG5k-NH₂ to form mSiO₂-PEG-NH₂ (3), which was subjected to NOTA conjugation and subsequent PEGylation to yield NOTA-mSiO₂-PEG-Mal (4). NOTA-mSiO₂-PEGTRC105 (5) could be obtained by reacting TRC105-SH with (4) ⁶⁴Cu-labelingwasperformed in the last step to generate ⁶⁴Cu-NOTAmSiO₂-PEG-TRC105. (B) Serial coronal PET images of 4T1 tumor-bearing mice at different time points post injection of (a) ⁶⁴Cu-NOTA-mSiO₂-PEG-TRC105, (b) ⁶⁴Cu-NOTA-mSiO₂-PEG, or (c) ⁶⁴Cu-NOTA-mSiO₂-PEG-TRC105 with a blocking dose of TRC105. Tumors were indicated by yellow arrowheads.
Figure 10.22 (a) PET image co-registered with the corresponding CT image of mice taken 1 h after injection ⁸⁹Zr-DFO-MSNs (b) ⁸⁹ZrCl4 solution into the tail vein. (c) Biodistribution curve of ⁸⁹Zr-DFO-MSNs as compared to ⁸⁹ZrCl4 in salt form.
Figure 10.23 In vivo SPECT/CT imaging of a nude mouse injected with DT10 141Ce-rCONPs, at (a) 2 h, (b) 24 h, (c) 72 h, and (d) 144 h post injection. Images shown here were obtained from volume renderings that were adjusted to a uniform scale.

Chapter 11: Relevance of Natural Degradable Polymers in the Biomedical Field

Figure 11.1 Chemical structures of chitosan modified with different sulfate groups. 2-N-Sulfated chitosan, 2SCS;6-O-Sulfated chitosan, 6SCS; 2-N, 6-O-Sulfated chitosan, 26SCS [14].
Figure 11.2 Biological activities modulated by the interaction of proteins with heparan sulfate [60].
Figure 11.3 Morphologies of keratin nanoparticles in a TEM image.
Figure 11.4 Chemical structure of dextran [79].
Figure 11.5 Antifungal properties of dextran-based hydrogels with or without AmB. (a) Schematic representation of the preparation of amphogels, (c) SEM images of dextran-based gels without (c1) and with (c2) AmB incubated with Candida albicans for 48 h.
Figure 11.6 Schematic illustration of the formation of the zein/chitosan complex for encapsulation of α-tocopherol [202].
Figure 11.7 Possible cross-linking mechanism for the reaction of casein with genipin in an aqueous system [261].

Chapter 12: Synthetic Biodegradable Polymers for Medical and Clinical Applications

Figure 12.1 Classification of biodegradable polymer.
Figure 12.2 Cycling performance of LiFePO₄ electrodes prepared using different binders, at 0.1 °C between 2.7 and 4.3 V at room temperature.
Figure 12.3 Concept of a hemostatic foam to treat noncompressible hemorrhage. (a) Hemorrhage occurring from a wound in the torso region cannot be treated by applying compression of a bandage. (b) Hemostatic foam can be sprayed into the wound cavity. (c) The foam expands into the cavity and forms a solid barrier that counteracts the expulsion of blood. Active ingredients in the foam can also interact with the blood, promoting blood clotting or gelation. (d) The net result is that hemostasis is rapidly achieved, and the bleeding is thereby contained.
Figure 12.4 Endocytic uptake and intracellular trafficking of hyperbranched copolymer-based micelles in cells.
Figure 12.5 PEI in red fluorescent protein (RFP). (a) Cyclic PEI RFP expression and (b) linear PEI RFP expression.

List of Tables

Chapter 1: Biomaterials for Biomedical Applications

Table 1.1 Natural and synthetic polymers commonly used in the synthesis of hydrogels [10]
Table 1.2 Types of biomaterials used for preparation of scaffolds for bone tissue Engineering
Table 1.3 Types of biomaterials (polymers, ceramics, and composite) used for preparation of scaffolds for bone tissue Engineering

Chapter 2: Conducting Polymers: An Introduction

Table 2.1 Various conducting polymers
Table 2.2 Types of conducting polymers and their properties and applications
Table 2.3 Comparison of chemical and electrochemical polymerization methods used to prepare CPs

Chapter 5: Smart Electroactive Polymers and Composite Materials

Table 5.1 Conductivity of common CPs.^a

Chapter 6: Synthetic Polymer Hydrogels

Table 6.1 Applications of synthetic polymer hydrogels

Chapter 7: Hydrophilic Polymers

Table 7.1 Use of cellulose and chitosan derivatives [125]

Chapter 8: Properties of Stimuli-Responsive Polymers

Table 8.1 Various applications of pH-sensitive polymers for drug delivery systems

Chapter 9: Stimuli-Responsive Polymers: Biomedical Applications

Table 9.1 Advantages and limitations of various stimuli-responsive polymers

Chapter 11: Relevance of Natural Degradable Polymers in the Biomedical Field

Table 11.1 Pectin-containing hydrocolloid wound dressings [110]

Related Titles

Bagchi, D., Bagchi, M., Moriyama, H., Fereidoon, S. (eds.)

Bio-Nanotechnology – A Revolution in Food, Biomedical and Health Sciences

2013

Print ISBN: 978-0-470-67037-8

WOL obook PDF ISBN: 978-1-118-45191-5

eMobi ISBN: 978-1-118-45192-2

ePub ISBN: 978-1-118-45193-9

Adobe PDF ISBN: 978-1-118-45194-6

Smela, E.E., Carpi, F.F. (eds.)

Biomedical Applications of Electroactive PolymerActuators

2009

Print ISBN: 978-0-470-77305-5

Adobe PDF ISBN: 978-0-470-74468-0

ISBN: 978-0-470-74469-7

Narain, R. (ed.)

Chemistry of Bioconjugates

Synthesis, Characterization, and Biomedical Applications

2014

Print ISBN: 978-1-118-35914-3

WOL obook PDF ISBN: 978-1-118-77588-2

ePub ISBN: 978-1-118-77637-7

Adobe PDF ISBN: 978-1-118-77640-7

Kabasci, S. (ed.)

Bio-based Plastics – Materials and Applications

2014

Print ISBN: 978-1-119-99400-8

eMobi ISBN: 978-1-118-67662-2

ISBN: 978-1-118-67664-6

ePub ISBN: 978-1-118-67673-8

Adobe PDF ISBN: 978-1-118-67678-3

Kumar, C.S. (ed.)

Biofunctionalization of Nanomaterials

2015

Print ISBN: 978-3-527-31381-5

Taubert, A., Mano, J.F., Rodríguez-Cabello, J.C. (eds.)

Biomaterials Surface Science

2013

Print ISBN: 978-3-527-33031-7

ISBN: 978-3-527-64960-0

eMobi ISBN: 978-3-527-64961-7

ePub ISBN: 978-3-527-64962-4

Adobe PDF ISBN: 978-3-527-64963-1

Zhao, Y., Shen, Y. (eds.)

Biomedical Nanomaterials

2016

Print ISBN: 978-3-527-33798-9

WOL obook PDF ISBN: 978-3-527-69439-6

ePub ISBN: 978-3-527-69441-9

eMobi ISBN: 978-3-527-69442-6

Adobe PDF ISBN: 978-3-527-69443-3

Deng, T. (ed.)

Bioinspired Engineering of Thermal Materials

2016

Print ISBN: 978-3-527-33834-4

WOL obook PDF ISBN: 978-3-527-68759-6

ePub ISBN: 978-3-527-68761-9

eMobi ISBN: 978-3-527-68764-0

Adobe PDF ISBN: 978-3-527-68765-7

Pompe, W., Rödel, G., Weiss, H., Mertig, M.

Bio-Nanomaterials

Designing materials inspired by nature

2013

Print ISBN: 978-3-527-41015-6

ISBN: 978-3-527-65526-7

eMobi ISBN: 978-3-527-65527-4

ePub ISBN: 978-3-527-65528-1

Adobe PDF ISBN: 978-3-527-65529-8

Kargarzadeh, H., Ahmad, I., Thomas, S., Dufresne, A. (eds.)

Handbook of Cellulose Nanocomposites

2016

Print ISBN: 978-3-527-33866-5

WOL obook PDF ISBN: 978-3-527-68997-2

Adobe PDF ISBN: 978-3-527-68998-9

ePub ISBN: 978-3-527-68999-6

eMobi ISBN: 978-3-527-69004-6

Jawaid, M., Faruq, M. (eds.)

Nanocellulose and Nanohydrogel Matrices

Biotechnological and Biomedical Applications

2017

Print ISBN: 978-3-527-34172-6

Adobe PDF ISBN: 978-3-527-80382-8

WOL obook PDF ISBN: 978-3-527-80383-5

eMobi ISBN: 978-3-527-80384-2

ePub ISBN: 978-3-527-80385-9

All books published by Wiley-VCH are carefully produced. Nevertheless, authors, editors, and publisher do not warrant the information contained in these books, including this book, to be free of errors. Readers are advised to keep in mind that statements, data, illustrations, procedural details or other items may inadvertently be inaccurate.

The Deutsche Nationalbibliothek lists this publication in the Deutsche Nationalbibliografie; detailed bibliographic data are available on the Internet at <http://dnb.d-nb.de>.

All rights reserved (including those of translation into other languages). No part of this book may be reproduced in any form – by photoprinting, microfilm, or any other means – nor transmitted or translated into a machine language without written permission from the publishers. Registered names, trademarks, etc. used in this book, even when not specifically marked as such, are not to be considered unprotected by law.

Natural and synthetic polymer materials and composites are extensively used as biomaterials for various biomedical applications such as tissue engineering, implantable devices, drug delivery, gene delivery, bioimaging, and so on. Advances in polymer chemistry have allowed the creation of a wide range of biomaterials based on polymers and composites for different biomedical applications according to the nature of their use. The versatility and ease of modification of the chemical, physical, surface, and biomimetic properties of polymers have made them very much dear to the researchers working in the biomedical field. Applications of biomaterials have led to the development of polymers that are biocompatible, biodegradable, and/or resorbable.

A variety of research results are published almost daily on polymers and composites by enhancing their properties as biomaterials to meet the ongoing and evolving challenges in the biomedical field. This book, Biomedical Applications of Polymeric Materials and Composites, is intended to update and provide detailed information to students, technicians, researchers, scientists, and teachers working in the biomedical field by taking the contents only from the very latest results and presenting an extensive summary of the various polymeric materials used in biomedical applications.

Chapter 1, “Biomaterials for biomedical applications,” provides an introduction to the various biomaterials currently used in biomedical applications. Selection of the appropriate biomaterials plays a key role in the design and development of the biomedical product. Nowadays, the strategy for biomaterials to be used as biomedical devices is that they should be biocompatible and must elicit a desirable cellular response to harness control over cellular interactions during its usage. This chapter provides detailed information on the current approach for developing biomaterials that can create cellular response by including protein growth factors, anti-inflammatory drugs, gene delivery vectors, and other bioactive vectors. Polymers are generally known to be insulating materials; however, it has been discovered that some polymers can be conductors and semiconductors. Chapter 2, “Conducting polymers – An introduction,” provides information on conducting polymers, as these polymers can be used for different applications in biomedical devices. Chapter 3, “Conducting Polymers: Biomedical Applications,” details the importance of using conducting biopolymers in the biomedical field and provides information of various biopolymers that are used in this field.

Chapter 4, “Plasma-assisted fabrication and processing of biomaterials,” provides information on low-temperature plasma-assisted methods to fabricate and modify the surface of biomaterials. Plasma is also used for sterilization and disease management. Chapter 5, “Smart electroactive polymers and composite materials,” describes such materials. Upon application of an electric voltage, the shape of some polymeric materials can be modified, which can be used as actuators and sensors. Because of their similarities with some biological tissues based on the achievable stress and force, these polymers can be used as artificial muscles. Chapter 6, “Synthetic polymer hydrogels,” provides information of some of the rapidly developing groups of materials that find applications in many fields such as pharmacy, medicine, and agriculture. Chapter 7, “Hydrophilic polymers,” describes various natural, synthetic, and semisynthetic hydrophilic polymers. These types of polymers have the lion's share of applications in the field of biomaterials.

Chapter 8 describes the “Properties of stimuli-responsive polymers.” These types of polymers are the most exciting and emerging class of materials, and have the ability to respond to external stimuli such as temperature, pH, ionic strength, light, and electric and magnetic fields. Since these materials can respond to external stimuli, they find many applications in the biomedical field. Chapter 9, “Stimuli-responsive polymers: Biomedical applications,” provides details about various polymers that find applications in the biomedical field based on their stimuli-responsive properties. This interesting property has enabled the development of smart systems that are useful in bioimaging, sensing (diagnosis), controlled drug delivery, regenerative medicine (therapy), bioseparation, gating valves for transport, and microfluidics. Chapter 10, “Functionally engineered sol–gel inorganic gels and hybrid nanostructures for biomedical applications,” describes nanostructured inorganic gels, mostly metal oxide gels and hybrid nanoarchitectures developed through sol–gel synthesis, and their various biomedical applications.

Chapter 11, “Relevance of Natural Degradable Polymers in the Biomedical field,” highlights the importance of natural degradable polymers for biomedical applications. In modern medicine, natural degradable polymers have their own indisputable place, particularly in drug delivery applications, because they degrade after serving their specific roles. Natural degradable polymers alone cannot meet the demand for applications in the biomedical field. Therefore, with the help of modern chemistry, many biodegradable synthetic polymers have been developed with a wide range of applications such as sutures, implants, drug delivery vehicles, and so on. A variety of synthetic methods have allowed the development of many polymers that meet the functional demands and materials with the desired physical, chemical, biological, biochemical, and degradation properties. Chapter 12, “Synthetic biodegradable polymers for Medical and Clinical Applications,” is included to describe the various synthetic degradable polymers that find interesting applications in the biomedical field.

We believe that this book provides in-depth discussions and details on the polymers and their composites that have applications in the biomedical field based on recent research results in this magnificent field. Throughout the book, we have focused on recent applications, with worked examples and case studies for training purposes, which will serve the purpose of this book, that is, to update students, technicians, researchers, scientists, and teachers who work in the biomedical field.

We express our sincere thanks and appreciation to the 20 scientists for contributing chapters to this book and their constant cooperation from submission of the first drafts to revision and final fine-tuning of their chapters commensurate with the reviews. We extend our appreciation to our respective host institutions, namely Mahatma Gandhi University, Kottayam, India, and Toyo University, Japan, for their encouragement and support.

Finally, we wish to extend our thanks to Wiley-VCH and all their staff involved in the publication and promotion of this book, which will hopefully be useful to those working in the biomedical field.