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Файл:Ординатура / Хирургия / Библиотека им академика М.И. Перельмана / Книга_5361_Библиотеки_им_академика_М_И_Перельмана.pdf
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- •Aim and Scope
- •Preface
- •Acknowledgments
- •Contents
- •Contributors
- •About the Editors
- •1.1 Introduction
- •1.2.1 Friction
- •1.2.1.3 Friction Under Lubricated Conditions
- •1.7.1 Joint Tribology
- •1.7.2 Skin Tribology
- •1.7.3 Oral Tribology
- •1.8 Summary
- •References
- •2.1 Introduction
- •2.3.1 Fluid Pressurization/Fluid-Film Lubrication
- •2.3.2 Boundary Lubrication
- •2.3.3 Hydrodynamic Lubrication
- •2.3.4 Squeeze-Film Lubrication
- •2.3.5 Synovial Fluid
- •2.3.6 Hydration Lubrication
- •2.5.2 Scaffolds
- •2.5.3 Synthetic Polymer
- •2.5.4 Polyacrylamide
- •2.5.5 PEG Hydrogel
- •2.5.6 PVA Hydrogel
- •2.5.7 Double Network Hydrogel
- •2.5.8 Triple Network Hydrogel
- •2.6.1 Polyacrylamide
- •2.6.2 PEG Hydrogel
- •2.6.3 PVA Hydrogel
- •2.6.4 Double Network Hydrogel
- •2.6.5 Triple Network Hydrogel
- •2.7.1 Mechanical Properties
- •2.7.2 Structural Properties
- •2.8 Conclusion
- •References
- •3.1 Introduction
- •3.3.1 Label-Based Biosensors
- •3.3.2 Label-Free Biosensors
- •3.4 Different Nanobiosensing Techniques
- •3.4.1 Optical Sensing
- •3.4.2 Electrochemical/Electrical Sensing
- •3.4.3 Magnetic Sensing
- •3.4.4 Mass-Based Sensing
- •3.6.2 Neurodegenerative Diseases
- •3.6.3 Infectious Diseases
- •3.6.4 Metabolic Diseases
- •References
- •4.1 Introduction
- •4.2.1 Surface Functionalization
- •4.2.2 Bioconjugation
- •4.3 Synthesis Approach
- •4.3.1 Hydrothermal Method
- •4.3.2 Chemical Vapor Deposition (CVD)
- •4.3.3 Wet Chemical Method
- •4.4 Plasmonic Black Bodies (PBBs)
- •4.4.1 Gold NP (AuNPs)-Based PBB
- •4.4.2 Silver NPs (Ag NPs)-Based PBB
- •4.4.3 Platinum NPs (Pt NPs)-Based PBB
- •4.5 Biomimetic NP
- •4.6 Upconverting NP (UCNP)
- •4.6.1 Synthesis
- •4.7 Inorganic NP
- •4.7.1 Synthesis
- •4.8 Photothermal Therapy (PTT)
- •4.9 Conclusion
- •References
- •5.1 Introduction
- •5.2 Human Skin
- •5.10 Future Scope
- •5.11 Conclusion
- •References
- •6.1 Introduction
- •6.1.1 Class 1
- •6.1.2 Class 2
- •6.1.3 Class 3
- •6.4.1.1 Surface Patterning
- •6.4.1.2 Direct-Write Patterning
- •6.4.1.5 Dip-Pen Nanotechnology
- •6.4.1.7 Composing Using Beams
- •6.4.1.8 Direct Write Photolithography (DWP)
- •6.4.1.9 Light-Beam Lithography Electron
- •6.4.1.10 Focused Ion Beam Lithography
- •6.4.2 Fabrication Techniques
- •6.4.2.4 Non-invasive Glucose Monitoring Devices Technique
- •6.4.2.6 Cost-Effective Electrochemical Voltametric Sensors Techniques
- •6.4.2.7 Three-Dimensional (3D) Printing Techniques
- •6.4.2.8 UV-LED Stereolithography Printer Technique
- •6.4.2.9 4D Printing Techniques
- •6.4.2.10 Advanced Biomedical Techniques Involving Biorobots
- •References
- •7.1 Introduction
- •7.6 Mechanical Biocompatibility Challenges
- •7.7 Poor Bio-Printing Resolution
- •7.9 Limited Biomaterial Selection
- •7.11 Conclusion
- •8.2 Animal Tribology
- •8.2.1 Joint
- •8.2.3 Integumentary Change
- •References
- •8.1 Introduction
- •8.3.1 Nanotribology
- •8.4 Green Tribology
- •8.5 Conclusion
- •References
- •9.1 Introduction
- •9.2 Bio-Tribological Issues
- •9.3.2 Bone Fracture Fixation
- •9.3.4 Cardiovascular Devices
- •9.3.5 Minimal Invasive Surgical Devices
- •References
- •10.1 Introduction
- •10.2.2.1 Structural Integrity
- •10.2.2.2 Controlled Release Properties
- •10.2.2.3 Enhanced Drug Loading Capacity
- •10.2.2.4 Tailored Material Properties
- •10.2.3.1 Biocompatibility
- •10.2.3.3 Mechanical Properties
- •10.2.3.4 Drug Compatibility
- •10.2.3.5 Fabrication Compatibility
- •10.3.1 Matrix Material Properties
- •10.3.4 Biocompatibility Assessment
- •10.3.4.1 In Vitro Cell Culture Studies
- •10.3.4.2 Hemocompatibility Studies
- •10.3.4.3 In Vivo Animal Studies
- •10.3.4.4 Histological Analysis
- •10.3.4.5 Immune Response Evaluation
- •10.3.4.6 Biodegradation Assessment
- •10.4 Surface Engineering Considerations
- •10.4.2.1 Surface Coatings
- •10.4.2.2 Plasma Treatment
- •10.4.2.3 Surface Grafting
- •10.4.2.4 Dip Coating
- •10.4.2.5 Spray Coating System
- •10.4.2.6 Electrotreated Coating
- •10.4.2.9 Microfabrication Techniques
- •10.4.2.10 Surface Roughness Control
- •10.5.1.2 Mechanical Properties
- •10.5.1.3 Surface Characteristics
- •10.5.1.4 Release Kinetics Analysis
- •10.5.1.5 Biological Compatibility
- •10.5.1.7 Other Analyses
- •10.6 Advanced Fabrication Techniques
- •10.8 Conclusion
- •References
- •11.1 Introduction
- •11.2 Shape Memory Alloys (SMA)
- •11.3 Shape Memory Polymers
- •11.3.1 Heat
- •11.3.2 Light
- •11.3.3 Magnetic Field
- •11.4 Shape-Changing Hydrogels
- •11.5 Biomedical Applications
- •11.6 Conclusion
- •References
- •12.1 Introduction
- •12.3 Bioresorbable Orthopedic Implants
- •12.4.1 Polylactides
- •12.4.2 Poly (Ortho Esters)
- •12.4.3 Polyphosphoesters
- •12.4.4 Polyphosphazenes
- •12.4.5 Polycaprolactone
- •12.4.6 Polyurethanes
- •12.4.7 Polycarbonates
- •12.5.1 Compression Molding
- •12.5.2 Transfer Molding
- •12.5.3 Injection Molding
- •12.5.4 Extrusion
- •12.5.5 Blow Molding
- •12.5.6 Calendering Process
- •12.5.7 Fiber Spinning
- •12.5.8 Thermoforming
- •12.5.9 Polymer Foaming
- •12.7 Challenges
- •12.8 Conclusion
- •References
- •13.1 Introduction
- •13.3.1.1 Total Hip Replacement (THR)
- •13.3.2 Resurfacing Hip Replacement (RHR)
- •13.5.1 Adhesive Wear
- •13.5.2 Abrasive Wear
- •13.5.3 Fatigue Wear
- •13.5.4 Corrosion/Oxidative Wear
- •13.5.5 Surface Cracking
- •13.6.1 Metallic Implants
- •13.6.1.1 Stainless Steel
- •13.6.1.2 Co-Cr Alloys
- •13.6.1.3 Ti-Alloy
- •13.6.2 Ceramic Implants
- •13.6.3 Polymer Implants
- •13.6.4 Composite Implants
- •13.6.5.2 Surface Coatings
- •13.7.2.1 Hydrodynamic Lubrication
- •13.7.2.2 Boundary Lubrication
- •13.7.2.3 Elastohydrodynamic Lubrication
- •13.7.3 Biomimetic Lubrication Approaches
- •13.7.3.1 Replicating Natural Lubrication Mechanisms
- •13.7.4.1 Implant Wear
- •13.7.4.3 Synovial Fluid Degradation
- •13.8.1 Hydroxyapatite Coatings
- •13.8.1.1 Bone Integration
- •13.8.1.2 Implant Stability
- •13.8.1.4 Biocompatibility
- •13.8.2 Diamond-Like Carbon Coatings
- •13.8.3 Metal Nitride Coatings
- •13.8.4 Polymeric Coatings
- •13.8.5 Nanocomposite Coatings
- •13.9.1 Pin-on-Disk Testing
- •13.9.2 Hip Joint Simulators
- •13.9.3 Knee Joint Simulators
- •13.9.4 Tribo-Corrosion Testing
- •13.9.5 Wear Debris Analysis Techniques
- •13.9.5.1 Scanning Electron Microscopy (SEM)
- •13.9.5.2 Energy-Dispersive X-Ray Spectroscopy (EDS)
- •13.10.1.1 Tailored Geometries
- •13.10.1.2 Improved Wear Characteristics
- •13.10.1.3 Accelerated Innovation
- •13.10.2.1 Real-Time Wear Monitoring
- •13.10.2.2 Functionality Assessment
- •13.10.2.3 Implant Status Monitoring
- •13.10.2.4 Patient-Centric Healthcare
- •13.10.3.1 Advanced Biomaterials
- •13.10.3.4 Multidisciplinary Approaches
- •13.10.4.1 Wear Data Analysis
- •13.10.4.2 Predictive Wear Patterns
- •13.10.4.3 Early Intervention Strategies
- •13.10.4.4 Personalized Treatment Plans
- •13.11 Conclusion
- •References
- •14.1 Introduction
- •14.2.1 Powder Bed Fusion (PBF)
- •14.2.2 Directed Energy Deposition
- •14.3.1 Extrusion-Based AM
- •14.5 Biomanufacturing
- •14.5.1 Tissue Engineering
- •14.5.2 Organ-on-a-Chip Models
- •14.6 Conclusion
- •References
- •Index

4 Biological Smart Materials: Materials forCancer Treatment
Fig. 4.7 Synthesize and characterization of biodegradable BGVs. (a) Schematic representation of
the proposed design of the biodegradable BGVs. (b) SEM image of BGVs. (c) TEM image of
BGVs. (d) SEM images of different types of vesicle. (e) UV-vis spectroscopy of BGVs. (f) Thermal
images of mice with MDA-MB-435 tumors. (g) Temperature of the tumor changes over time during laser irradiation for different treatments. (h) In vivo ultrasound (US) and photoacoustic (PA)
images of tumor tissues. (i) Photoacoustic (PA) intensities of tumor tissues after the i.t. administration. (Reprinted with permission from Wiley [86])
133
tuning of the LSPR peak to the near-infrared (NIR) region. These BGVs demonstrated robust NIR absorption, excellent PA response, and heightened photothermal
conversion efciency upon laser irradiation. Figure4.7b displays the SEM image, a
collection of vesicular assemblies, known as BGVs, formed from GNPs. The inset
image within this SEM picture provides a three-dimensional electron-density mapping of a broken BGV, giving a detailed view of the internal hollow structure of the
BGVs, emphasizing their unique geometry and self-assembly characteristics.
Figure4.7c represents TEM image and inset TEM image shows the closer view of
the individual BGVs, demonstrating its distinct vesicular morphology. Figure4.7d
represents the SEM images of different types of vesicles like gold vesicles (GVs),
biodegradable gold vesicles (BGV1, BGV2, and BGV3) with varying properties.
Figure4.7e shows the UV/Vis/NIR spectra of different NPs like gold NPs (GNPs),
gold vesicles (GVs), and biodegradable gold vesicles (BGVs) produced by the dialysis of GNP solutions. The spectra show the plasmon resonance peaks, which are
indicative of the collective oscillations of electrons in the GNPs.
4.8 Photothermal Therapy (PTT)
PTT emerges as a pioneering approach that harnesses the power of light for therapeutic benets. This innovative technique capitalizes on the photothermal conversion properties of specic materials to selectively generate localized heat, providing
a precise and controlled means to target and treat various medical conditions, notably cancer [87]. By exploiting the unique interactions between light and matter,
PTT holds the potential to revolutionize the way we approach disease treatment,
offering enhanced precision, minimal invasiveness, and improved therapeutic outcomes. Some 2D materials, such as graphene or black phosphorus, possess

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excellent photothermal conversion properties. This means they can efciently convert absorbed light energy into heat [88]. Surface modication can be employed to
optimize their photothermal efciency and improve their application in PTT, a technique that utilizes heat generated by light absorption to selectively destroy cancer
cells or deliver heat-sensitive therapeutics. By embedding or connecting these plasmonic NPs onto the surface of 2D materials, light absorption can be signicantly
heightened, promising an improved efcacy of PTT [89]. This section of the book
chapter provides an overview of the diverse range of NP approaches, including
PBB, biomimetic NPs, inorganic NPs, and upconverting NPs, poised to revolutionize PTT and redene the landscape of medical treatments.
4.8.1 PTT ofPBB
4.8.1.1 Au NP forPTT
Choi etal. [50] used tiny structures called nanoworms to do a special kind of treatment, called photothermal therapy (PTT), on HeLa cells. They mixed the nanoworms with the cells for 24h and then shone a special laser on them that produced
heat. This made the cells less alive, and when they checked the cells later, they saw
that the higher the amount of nanoworms, the less alive the cells were. Moreover, Li
et al. [52] conducted a study using special nanoparticles known as GNRs@
PDA−PEG NPs to treat cancer cells and tumors. They coated these nanoparticles
with a substance called DOX.In Fig. 4.1e they examined the light absorption of
these nanoparticles, and they noticed a small peak in the spectrum that matched the
absorption of DOX.In vitro experiments were involved evaluating the photothermal
efciency of GNRs-based nanocomposites upon exposure to an 808nm diode laser.
The stability of the photothermal effect was examined through four on/off laser
cycles, demonstrating consistent temperatures in Fig.4.1f. The correlation between
pH, laser irradiation, and DOX release prole was unveiled in pioneering studies
shown in Fig.4.1g. Evaluation in nude mice with xenografts demonstrated the anticancer efcacy of GNRs@PDA-PEG-DOX nanocomposites. In vivo photothermal
impact and PA imaging led to random grouping of xenograft-bearing mice (Fig.4.1j,
k). While laser-only treatment showed inadequate tumor ablation (Fig. 4.1h),
GNRs@PDA-PEG-DOX exhibited substantial inhibition of tumor growth due to
DOX release in the acidic TME. Notably, combined chemotherapy and PTT
enhanced the inhibitory effect. Tumor weight comparisons in Fig.4.1i indicated the
efcacy of the treatment. Photothermal conversion efciencies at different concentrations (Fig.4.1l, m) highlighted dose-dependent temperature increases. Despite
this, there was no signicant weight loss or systemic toxicity. Reduced tumor volume and cell proliferation afrmed the nanocomposites’ preventive impact on
tumor development.

4 Biological Smart Materials: Materials forCancer Treatment
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4.8.1.2 Ag NP forPTT
Mondal et al. [56] conducted an assessment of the photothermal and chemophotothermal effects of QRC-FA-AgNPs in an invitro setting. MDA-MB-231 cells
were exposed to varying concentrations of AgNPs, QRC-AgNPs, and QRC-FAAgNPs for a duration of 3h, followed by 5min of laser irradiation at 800nm.
Subsequently, calcein-AM and PI staining were employed to gauge cell viability.
The outcomes demonstrated that QRC-FA-AgNPs, in conjunction with NIR laser
irradiation, displayed the highest degree of cytotoxicity. This was attributed to their
heightened internalization and accumulation within cancer cells via targeted endocytosis. Consequently, this phenomenon led to an enhanced cytotoxic impact of
QRC and the induction of localized hyperthermia, ultimately heightening the thermal sensitivity of breast cancer cells. The study’s conclusions imply that QRC-FAAgNPs, when paired with NIR irradiation, exhibit a potent chemo-photothermal
effect, showcasing their potential as a promising strategy for augmenting the therapeutic efciency of QRC.Moreover, Bose etal. [57] conducted invitro photothermal experiments in which varying concentrations of PVA-SNT were subjected to an
808nm laser, leading to temperature elevations that were monitored using an infrared (IR) thermal camera. The photothermal conversion efciency of PVA-SNT was
quantied at 30.44%. Additionally, the nanoparticles underwent evaluation through
photoacoustic imaging (PAI) to gauge their imaging capabilities. Subsequent to
this, invivo PTT experiments were carried out on mice bearing tumors. PVA-SNT
was administered intratumorally, followed by exposure of the tumors to an 808nm
laser. The resulting increase in temperature within the tumor region proved sufcient for effective cancer treatment, all without notable toxicity or unfavorable
effects observed in the mice.
4.8.1.3 Pt NP forPTT
Qi etal. [61] conducted invitro experiments with Pt@PDA-c NPs, revealing their
efcient photothermal conversion capability, raising the temperature up to 52.5°C
within 10min of laser irradiation. For invivo experiments on HepG2 tumor-bearing
mice, the NPs were intravenously administered, and the NIR-II PACT system continuously monitored the PA signal at the tumor site over the next 24h. The NPs’
accumulation peaked around 12h after injection (Fig.4.2h, i), attributed to their
optimal size, biocompatibility, and targeted tumor homing. Laser irradiation of the
tumor site using Pt@PDA-c NPs led to effective tumor ablation, with the local temperature quickly reaching 55°C in 5min and sustaining for 5min under 1064nm
laser irradiation (1W•cm−2) (Fig.4.2j, k). In contrast, laser + PBS treatment only
raised the tumor site temperature to around 40°C, insufcient for Pt@PDA-c and
NIR-II laser-induced ablation. The mice’s body weight remained stable throughout
the treatment period (Fig.4.2l), and tumor growth curves and relative volumes were
displayed in Fig.4.2m, demonstrating substantial tumor inhibition in the laser +

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NPs group. Pt@PDA-c NPs exhibited high stability, excellent biocompatibility, and
an impressive photothermal conversion efciency of 71.3%, surpassing other
organic and inorganic materials.
4.8.1.4 PTT ofBiomimetic Materials
Chirivì etal. [68] use biomimetic keratin-coated gold nanoparticles (Ker-AuNPs) as
part of a novel strategy that combines 3D bioprinting (3DB) with PTT for potential
cancer treatment. The 3DB construct integrates glioblastoma U87-MG cells within
a 3D architecture, incorporating Ker-AuNPs as a photo-thermal agent. When
exposed to a laser with a wavelength of 532nm, the Ker-AuNPs produce considerable heating that causes the temperature to rise by roughly 16°C in less than 2min.
The study also covers future directions, such as experimenting with various NP
geometries and compositions for improved nanomedicine applications, including
synergistic effects with chemotherapeutic agents and selective accumulation in cancer cells. Qin etal. [69] focused on combining phototherapy and immunotherapy to
overcome the limitations of photothermal therapy (PTT) in cancer treatment. They
aimed to improve its effectiveness against primary and distant tumors, enhance
tumor accumulation, and boost antitumor immunity. To achieve this, they used outer
membrane vesicles (OMVs) derived from Escherichia coli Nissle 1917 to create
biomimetic copper sulde nanoparticles (CuS-OMVs). These nanoparticles were
designed to bring together photothermal and immunotherapeutic effects. The CuSOMVs had advantageous features like strong photothermal conversion, stability,
and accurate tumor targeting. When exposed to near-infrared light, the CuS-OMVs
generated heat within tumor tissues, causing tumor cell damage. This heat also triggered a process called immunogenic cell death, leading to the activation of immune
cells like dendritic cells and CD8+ T cells. Moreover, the CuS-OMVs acted as
immune boosters, promoting the maturation of dendritic cells and switching tumorassociated macrophages to an immune-activating state. Overall, the CuS-OMVs
showed impressive antitumor effects on both primary and distant tumors when
exposed to near-infrared light. This research presents a promising new strategy for
effective photothermo-immunotherapy in cancer treatment. Yang etal. [70] introduced a novel type of nanoparticles termed DC@BPBBT dots for advancing photothermal cancer therapy. These nanoparticles were engineered by combining
near-infrared uorescent agents (BPBBT dots) with dendritic cell membranes. The
core of the nanoparticles exhibited impressive photothermal conversion and emitted
bright near-infrared uorescence, while the outer DC membrane facilitated their
attachment to T cells. This T cell-bound nanoparticle system displayed enhanced
efciency in delivering treatment to tumors, triggering the activation of T cells to
secrete cytokines that lower the expression of heat shock protein (HSP70) in tumor
cells. Subsequent to photothermal therapy, tumor samples were extracted from mice
in each group, and immunouorescence analysis revealed a substantial reduction in
HSP70 expression in tumor cells treated with DC@BPBBT dots, as depicted in
Fig. 4.3c. The researchers conducted in vivo experiments involving 4T1

4 Biological Smart Materials: Materials forCancer Treatment
137
tumor- bearing mice and administered DC@BPBBT dots and BPBBT dots intravenously to explore the synergistic effects of mild photothermal therapy and immunotherapy, as demonstrated in Fig.4.3d. Mice received either DC@BPBBT dots or
BPBBT dots (1mgkg−1) through intravenous injection. Subsequently, the tumors
were subjected to 808 nm laser treatment after 24 h, maintaining a comfortable
temperature (42°C) for 5min. The tumor’s progression was tracked by measuring
its size every 2days, as depicted in Fig.4.3e. Remarkably, after treatment with
DC@BPBBT dots and mild photothermal therapy (42°C), there were no noticeable
uctuations in the body weight of the mice over the course of several days, as illustrated in Fig.4.3f. This study effectively demonstrated an innovative solution that
tackles the challenge of heat-induced resistance and offers a promising approach for
cancer treatment by harnessing photothermal therapy and interactions with immune
cells. Li etal. [71] employed PTT to induce immunogenic cell death (ICD) in cancer cells, a phenomenon where dying tumor cells release molecules that attract
immune cells and trigger a robust immune response. The researchers delved into the
impact of PTT on key ICD-related signals, including calreticulin exposure, HMGB1
release, and ATP secretion. They utilized NPs loaded with indocyanine green (ICG)
and NLG919, named CFIN, to enhance the ICD effect driven by PTT. Upon exposure to an 808 nm laser, the CFIN NPs effectively targeted and eradicated 4T1
cancer cells, resulting in heightened CRT exposure, HMGB1 release, and ATP
secretion, signifying the activation of ICD pathways. These ICD signals play a pivotal role in drawing immune cells, particularly dendritic cells (DCs), which are
instrumental in initiating immune responses. CFIN treatment led to DC maturation
and an increase in cytotoxic T lymphocytes (CTLs). Furthermore, CFIN curbed the
activity of IDO-1, an enzyme responsible for immune suppression within the
TME. The amalgamation of PTT with immunotherapy generated a more potent
immune response, evidenced by increased secretion of cytokines TNF-α, IL-6, and
IFN-γ, which are associated with activating cellular immunity, fostering immune
cell proliferation, and regulating antitumor immunity. In vivo experiments using a
bilateral 4T1 tumor model underscored the signicance of CFIN treatment, especially in conjunction with PTT, in markedly impeding the growth of both primary
and distant tumors. This approach showcases the potential of synergizing photothermal and immunotherapeutic effects to enhance antitumor responses. Xiao etal. [72]
introduced an innovative approach to enhance colorectal cancer immunotherapy by
integrating immune checkpoint blockade and PTT. They developed NPs known as
PDA/GNS@aPD-L1 NPs, composed of photothermal nanoparticles coated with a
cell membrane containing anti- PD- L1 antibodies. This design aimed to disrupt
immunosuppressive signals through PD-1/PD-L1 blockade and induce targeted
tumor cell destruction upon laser irradiation. The NPs effectively accumulated at
tumor sites due to their tumor-targeting capability. Upon laser irradiation, the NPs
generated heat, causing tumor cell ablation and promoting tumor vascular permeability. Spectroscopic analysis demonstrated the high NIR absorption of PDA/GNS@
aPD-L1 NPs compared to plain PDA-GNS (Fig.4.4c). Furthermore, the membrane-
coated NPs maintained their photothermal conversion efciency. Under 808-nm
laser irradiation, the PDA/GNS@aPD-L1 NP solution rapidly reached

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approximately 54 °C within 5 min and exhibited strong photothermal stability
(Fig.4.4d, e). The NPs’ photothermal conversion was assessed under different con-
centrations and irradiation power densities (Fig.4.4f, g), with temperatures below
60°C maintaining their blocking effectiveness. The combination of PTT and PD-1/
PD-L1 blockade facilitated immune cell inltration, decreased immunosuppressive
cells, and signicantly curtailed tumor growth in both primary and distant tumors.
This novel strategy holds potential for reshaping the TME and enhancing colorectal
cancer therapy. Notably, the cytotoxic substance Dox was used as a positive control
for cell viability assessment using the CCK-8 test. PDA/GNS@aPD-L1 NPs without 808-nm laser irradiation, PDA/GNS@Free NPs, and PDA-GNS did not show
harm to DLD-1 cells across tested doses (Fig.4.4h). Moreover, intravenous drug
injection and tumor volume analysis were carried out (Fig. 4.4i, j). While this
approach offers promising therapeutic implications, challenges related to NP accumulation and immune-related adverse events must be addressed before clinical
translation.
4.8.2 Photothermal Therapy ofUpconverting Materials
4.8.2.1 PTT Activity ofUCNPs UPLNs@mSiO
2
In the study by Zhao etal. [76], a combination of UPLNs and ICG-loaded mSiO2
NPs was synthesized and introduced intravenously into SCID mice with
MDA-MB-231 breast cancer. Utilizing the enhanced permeability and retention
(EPR) effect, the nanoparticles circulated through the bloodstream and aggregated
ed. at the tumor location. Subsequently, when the nanoparticles had accumulated at
the tumor site, external exposure to a near-infrared (NIR) light source (808nm
laser) was administered to the mice. UPLNs within the NPs absorb NIR light and
allow real-time imaging of the tumor site. This approach offers a notable advantage
as it effectively addresses the inherent restriction of UPLNs in terms of their limited
imaging time. The emission of visible light facilitates a clear and accurate image of
the tumor, hence augmenting the ability to perceive its precise location and size.
The imaging process intensies the accuracy of the subsequent therapeutic intervention. After obtaining a precise image of the tumor site using the emitted visible
light from UPLNs, the same NIR light source was employed for PTT. ICG, acting
as a light-absorbing agent, captured NIR light and converted it into heat. This localized heating phenomenon induced hyperthermia specically at the tumor site, leading to the destruction of tumor tissue, as depicted in Fig.4.5b. The integration of
UPLN-guided imaging with ICG-mediated PTT allowed for a controlled and targeted approach to tumor treatment, thereby minimizing potential harm to surrounding tissues. The outcomes were demonstrated through various means, including
hematoxylin and eosin staining of mouse tumors treated with different samples
(10g/ml), the presentation of tumor weight and volume curves after 30days of
treatment with various samples in Figure 4.5c–e. The survival curve of the

4 Biological Smart Materials: Materials forCancer Treatment
139
subcutaneous tumor model when treated with different substances showcased
diverse therapeutic effects. Specically, the localized hyperthermia triggered by
PTT effectively led to the demise of cancer cells at the tumor site. The incorporation
of UPLN- guided imaging played a pivotal role in accurately dening tumor boundaries, ensuring precise treatment delivery. This heightened imaging precision and
treatment localization signicantly contributed to improved therapeutic outcomes
while reducing toxicity.
4.8.2.2 PTT Activity ofUCNPs-PANPs
Xing etal. [77] explored the potential of UCNPs-PANPs, by conducting a study
involving photothermal cancer therapy on a mice model with U87MG tumors
(human colon carcinoma). The research compared four groups: the experimental
group receiving both UCNP-PANPs injection and laser irradiation, a group subjected only to laser irradiation, the UCNP-PANPs injected group without laser treatment, and a blank group. Under laser irradiation at an 808 nm wavelength and
specic power, the tumor in the experimental group displayed size reduction within
just 10min of treatment. Remarkably, by the sixth day, complete tumor regression
was observed, leaving behind only residual scars. There was no known instance of
tumor regrowth between days 6 and 10 after surgery. On the other hand, during the
course of the 10-day period, the tumors in the control and blank groups consistently
demonstrated a trend of rapid growth. On day 6, the test group’s relative tumor volume (V/V0), which measures tumor size, showed a dramatic reduction with values
nearing zero, but the control and blank values gradually increased to 5. This highlights the effective tumor-suppressing effect of using UCNPs-PANPs along with
laser therapy. The UCNPs-PANPs demonstrated effective upconversion luminescence (UCL) in two separate wavelength intervals (520–560nm and 640–680nm),
which is advantageous for imaging applications. These NPs were capable of successfully converting light energy into heat for PTT due to their high photothermal
conversion efciency of 47.8%. They showed exceptional photostability and low
toxicity to animals and live cells, demonstrating their promise for secure biomedical
applications.
4.8.3 PTT ofInorganic Materials
Cheng etal. [85] aimed to develop a new class of nanomaterials for cancer treatment. They selected 2D nanosheets made of tungsten disulde (WS2), which shows
strong near-infrared light absorption capabilities. To enhance their biocompatibility
and stability within biological systems they have coated the nanosheets with polyethylene glycol (PEG). To determine their potential as cancer treatments, the
researchers conducted a series of in-depth studies. They rst tested the nanosheet’s
toxicity invitro by exposing various cell lines to it. Surprisingly, the nanosheets

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showed little toxicity. They then assessed how WS2-PEG nanosheets affected cancer
cells in a photothermal manner. The nanosheets effectively turned light energy into
heat when exposed to NIR laser light, killing cancer cells. The biodistribution of the
nanosheets was studied in mice-bearing tumor models in animal research. The ndings showed that tumors and reticuloendothelial systems were the places where
nanosheets were collected most frequently. Further, they employed imaging techniques, including CT and photoacoustic tomography, to visualize the distribution of
nanosheets in living organisms and offer a clear understanding of the precise distribution of the nanosheets within tumors. Signicantly, the researchers proceeded
with invivo PTT experiments using mice hosting tumors. Upon administering WS2PEG nanosheets and subjecting the mice to NIR laser irradiation, a swift elevation
in temperature was witnessed at the tumor sites, indicative of successful photothermal conversion. This therapeutic approach led to complete eradication of tumors
and prolonged survival in treated mice, outperforming the control groups. Notably,
rigorous evaluations of toxicity demonstrated minimal adverse effects on the animals throughout the study duration. In essence, the WS2-PEG nanosheets were a
viable contender for cancer therapy and imaging applications due to their potent
photothermal ablation and multimodal imaging characteristics. The results of photoacoustic imaging tomography (PAT) on a mouse model with 4T1 tumours are
shown in Fig.4.6f. These tumors underwent intravenous or intratumoral injections
of WS2-PEG nanosheets, and then PAT pictures were captured using a 700nm laser
as the excitation source. Untreated tumors frequently show little to no visualization
of major blood arteries. In contrast, post-injection with WS2-PEG nanosheets,
robust photoacoustic signals emerge within the tumor region, underscoring the successful accumulation of the nanosheets.
Strong photoacoustic signals do, however, appear within the tumor site after
injection with WS2-PEG nanosheets, demonstrating the nanosheets’ effective accumulation. In Fig.4.6g, a contrast is drawn between the absolute photoacoustic signals within tumors originating from mice subjected to i.t. injection and i.v. injection
of WS2-PEG nanosheets. While the i.t. injection approach might yield heightened
signals, opting for i.v. injection results in a more evenly spread signal distribution
across the entirety of the tumor. The rationale behind this lies in the fact that intravenous injection enables the nanosheets to access all regions of the tumor through
the bloodstream circulation. Figure4.6h demonstrates the temperature changes in
the tumor region due to different treatment strategies and shows the signicant temperature increase in tumors following WS2-PEG injection and NIR laser irradiation.
Figure4.6i provides a quantitative comparison of tumor growth among different
treatment groups and indicates the efcacy of WS2-PEG-based PTT in inhibiting
tumor growth. The side graph illustrates the survival rates of mice subjected to different treatments and shows the positive impact of WS2-PEG-based PTT on mice
survival compared to control groups. Figure4.6j offers visual evidence of the treatment outcomes on mice tumors and shows the regression of tumors in WS2-PEGtreated mice after PTT.

4 Biological Smart Materials: Materials forCancer Treatment
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Huang etal. [90] introduced an innovative approach involving BGVs to elevate
cancer therapy and imaging capabilities. These specialized nanovesicles were created by adding a disulde bond to a block copolymer, which made it easier for gold
nanoparticles (GNPs) to be arranged densely during assembly and created a strong
plasmonic coupling effect between nearby GNPs. A crucial component of efcient
PTT, the LSPR peak emerged as a result of this interaction in the NIR spectrum. The
amazing photothermal inuence of BGVs, which showed a signicant temperature
increase in response to laser irradiation, was conrmed by invitro tests. Importantly,
this behavior was more obvious in the case of BGVs and became stronger with
increasing radiant energy and particle concentration. BGVs were assessed using
cell viability tests and shown to exhibit selective and dose-dependent cytotoxicity to
cancer cells when exposed to laser light. Moving on to invivo studies employing a
tumor-xenograft mice model, intratumoral BGV injection was successful in considerably raising tumor temperatures using laser irradiation, resulting to targeted tumor
ablation without affecting nearby body parts. Notably, BGV injection guidance and
treatment monitoring were made easier by the inclusion of photoacoustic imaging.
BGVs were found to have noteworthy therapeutic activity, delaying tumor growth
noticeably and prolonged survival in mice. By combining superior PTT, imaging
capabilities, and quick removal of dissociated particles from the biological system,
the study highlighted the potential of BGVs as a multifunctional platform with positive implications for the treatment of cancer. In Fig.4.7f, thermal images of mice
with MDA-MB-435 tumors are contrasted with various therapies, such as intravenous injections of phosphate-buffered saline (PBS) and BGVs. The 808nm laser is
applied to the tumors for 5min before the thermal images are taken. Figure4.7g
displays heat curves that depict the temperature changes that occur in the tumor over
time as a result of different laser treatments. These parts of the gure demonstrate
the ability of BGVs to rapidly elevate the local tumor temperature upon laser exposure, a crucial aspect of PTT, which can lead to tumor cell death. The graph below
it shows the photoacoustic (PA) signals of BGVs and GNRs as a function of their
optical density (OD) and illustrates how PA imaging could be used to quantify the
presence of BGVs by demonstrating that the intensity of the PA signal increases
linearly with the concentration of BGVs. Figure4.7h displays images of cancer tissues acquired using in vivo ultrasonography and photoacoustic (PA) before and
after the injection of BGVs. On the images, arrows point to the locations of the
injected BGVs. The 3D PA images clearly show the distribution of BGVs within the
cancer tissue. Figure4.7i illustrates a comparison of the photoacoustic (PA) intensities of cancer tissues after intravenous injection of the same quantity of GVs or
BGVs. The results show that the average tumor PA intensity induced by BGV injections is much higher than that induced by GV injections, as well as considerably

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4.9 Conclusion
This work covers the basic information about the nanomaterial, which is the most
emerging material for cancer phototherapy. This chapter provides an idea about
specic types of NPs and their synthesized process and use in cancer treatment.
Plasmonic NPs, known for their unique optical properties, are examined for their
applications in cancer therapy. Their use in PTT is discussed, highlighting their
potential in targeted cancer cell destruction. Inspired by nature’s mechanisms, biomimetic-based materials for cancer treatment are examined. These materials mimic
biological systems to enhance PTT as discussed. Then we discussed upconverting
NPs, which can convert low-energy photons into high-energy emissions, in the context of cancer treatment. Their applications in PTT are explored. Inorganic- based
NPs, specically those employed in PTT also discussed. However, despite their
potential, these NPs face challenges. Ensuring their biocompatibility and safety is
crucial to avoid adverse effects. Achieving efcient and precise targeting of NPs to
tumor sites remains a challenge, requiring further advancements in targeting
strategies.
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