4. What are quantum dots
• Unique Spectral properties
Broad absorption
Narrow emission
Wavelength depends on size
CdSe/ZnS
QD
samples
Annu. Rev. Anal. Chem. 2013. 6:143–62, Michalet , X. et al. Science. 2005, 307 , 538 – 44
5. Making hydrophobic quantum dots biocompatible
• Various methods for
making them watersoluble
– Derivatizing surface
with bifunctional
ligands
– Encapsulating in
phospholipid
micelles or liposomes
– Polymer coating
Gao , X. et al. Adv.Experim.Med.
Biol. 2007, 620,57-73
6. Conjugating quantum dots to biomolecules
• Avidin or protein-G with
positively charged tail conjugated
to negatively charged DHLA coat
of quantum dots
Goldman E.R. et al.( 2002 ) JACS,124 , 6378 – 82 ;
Analytical Chemistry , 74 , 841 – 7 .
Avidin
protein G
7. Quantum
dots v/s other fluorescent
probes
• Broader excitation spectrum and narrower gaussian
emission spectrum
• No spectral overlap between dots of different size – better
for multiplexing
Jaiswal & Simon 2004
9. Quantum dots for multiplexing
benign prostate
gland
Multiplex
Immunostaining
gland with a single
malignant cell
Malignant
HRS cells
To differentiate
Hodgkin’s from
non-Hodgkin’s
lymphoma
B cells
T cells
Liu J et al. Anal. Chem. 2010, 82, 6237–6243; Am. Chem. Soc. Nano 4:2755–65
10. Quantum dots v/s other fluorescent
probes
Photostability (quantum dots do not photobleach)
3T3 cells
Scale bar 10 µm.
Red: qdot 605 Conjugate
Green: Alexa488 Conjugate
Wu et al. Nat. Biotechnol. 2003;21(1):41-62
11. Quantum dots v/s other fluorescent probes
• Brighter than other fluorophores
Quantum dots
Fluorescein
Larson et al. 2003
12. Quantum dots and imaging
In vivo visualization of capillaries
Quantum dots
FITC-Dextran
Larson et al. 2003, Science 300:1434-1436
13. Quantum dots and imaging
anti-α-tubulin
antibody
anti-Her2
antibody
Cancer cell surface marker red & green Microfilaments
biotinylated
phalloidin
Actin filaments
Nuclear antigens
Wu et al. Nat. Biotechnol. 2003;21(1):41-62
14. Quantum dots and imaging
Glycine Receptors
Diffusion of single
Qdot-GlyRs in
synaptic boutons
Primary antibody ↔ secondary Antibody – biotin ↔ QD Streptavidin
Dahan et al. Science. 2003, 302:442-445
15. Quantum dots and imaging
EGF receptor
EGF-QD
Live imaging of receptor mediated endocytosis
Lidke et al. Nat. Biotechnol. 2004, 22:198
16. Quantum dots and imaging
1 µm
200 nm
200 nm
Single quantum dot crystals can be observed in electron micrographs
18. Quantum dots and imaging: FRET
• Quantum dots have been used in FRET
• In conjunction with Texas Red
• In conjunction with fluorescent quenchers
Willard et al. Nat Materials. 2003, 2:575
20. Advantages
•
•
•
•
Specific labeling of cells and tissues
Useful for long-term imaging
Useful for multi-color multiplexing
Suitable for dynamic imaging of
subcellular structures
• May be used for FRET-based analysis
21. Disadvantages
• Colloidal polymer-coated quantum dots can
aggregate irreversibly
• Toxic in vivo
• Quantum dots are bulkier than many organic
fluorophores
– Accessibility issues
– Mobility issues
• Cannot diffuse through cell membrane
– Use of invasive techniques may change physiology
25. Imaging techniques and related contrast agents
X-ray Iodinated contrast materials
Au
MRI Gadolinium-based
Fe-based
19
F-based
PET Radioactively labelled agents (11C, 18F)
26. X-ray CT
CT is ubiquitous in the clinical setting as. The increasing use
and development of micro-CT and hybrid systems that with PET,
MRI.
The most investigated NPs in this field are gold NPs, since they
have large absorption coefficients against the x-ray source used
for CT imaging and may increase the signal-to-noise ratio of the
technique.
To date, different types of gold NPs have been tested in a
preclinical setting as contrast agents for molecular imaging:
nanospheres, nanocages, nanorods and nanoshells. Gold NPs
formulations as an injectable imaging agent have been utilized to
study the distribution in rodent brain ex vivo
28. PET
The strategy utilized is consisting in incorporating PET emitters
within the components of the NP, or entrapping them within the
core.
brain cancer
Oku et al (2011), Int. J. Pharm. 403 :170–177
29. MRI
MRI relies upon the enhancement of local water proton relaxation in the
presence of a contrast agent (CA). CA are compounds that catalytically shorten
the relaxation times of bulk water protons.
T1 (longitudinal relaxation– in simple terms, the time taken for the protons to
realign with the external magnetic field) Positive CA (Gd)
T2 (transverse relaxation –in simple terms, the time taken for the protons to
exchange energy with other nuclei) Negative CA (Iron oxide agents )
30. Gd-based NP
several nanotechnological approaches have been devised, based on
2 ideas:
-carrying many Gd chelates;
-slow down the rotation of the complex
Examples include liposomes micelles dendrimers fullerenes.
However, this approach has not yet achieved clinical applications.
31. Magnetic Nanoparticles
magnetic NPs (MNPs) are of considerable interest because they
may behave either as contrast agents or carriers for drug
delivery. Among these, the most promising and developed NP
system is represented by superparamagnetic iron oxide agents
31
32. Types of Magnets
•
Ferromagnetic materials: the magnetic moments of
neighboring atoms align resulting in a net magnetic moment.
•
Paramagnetic materials are randomly oriented due to Brownian
motion, except in the presence of external magnetic field
.
• Superparamagnetic Combination of paramagnetic and ferromagnetic
properties. Made of nano-sized ferrous magnetic particles, but
affected by Brownian Motion. They will align in the presence of an
external magnetic field.
B
32
33. The most promising and developed NP system is
represented by superparamagnetic iron oxide
agents, consisting of a magnetite (Fe3O4) and/or
maghemite (Fe2O3) crystalline core surrounded by a
low molecular weight carbohydrate (usually
dextran or carboxydextran) or polymer coat.
Iron oxide NPs can be classified according to their
core structure, such as Monocrystalline (MION;
10–30 nm diameter), or according to their size as
ultra-small superparamagnetic (USPIO) (20–50 nm
diameter), superparamagnetic (SPIO) (60–250 nm).
36. Formation of Nanoparticles
• Solution of Dextran, FeCl3.6H2O and FeCl2.4H2O (acidic
solution)
–
Less Dextran Larger Particles
• Drip in Ammonium hydroxide (basic) at ~2oC
• Stirred at 75oC for 75 min.
• Purified by washing and
ultra-centrifugation
• Resulting Size ~ 10-20 nm
• Plasma half-life: 200 min
36
37. Variation of Formation
• Change Coating Material
• Crosslinking coating material
–
Increases plasma half-life
–
Same Particle Size
Lee H et al. J. AM. CHEM. SOC. 2007,129, 1273-12745
38. Magnetite Cationic Liposomes (MCL)
Fe3O4
• Why Cationic?
–
Interaction between + liposome and – cell
–
membrane results in 10x uptake.
39. Formation of MCL
• magnetite NP dispersed in distilled water
• N-(α-trimethyl-amminoacetyl)-didodecyl-D-glutamate
chloride (TMAG) Dilauroylphosphatidylcholine (DLPC)
Dioleoylphosphatidyl-ethanolamine (DOPE) added to
dispersion at ratio of 1:2:2
• Stirred and sonicated for 15 min
• pH raised to 7.4 by NaCl and Na phosphate buffered and
then sonicated
DLPC
DOPE
40. Uses of Nano Magnets
• Hyperthermia
– An oscillating magnetic field on nanomagnets result
in local heating by (1) hysteresis, (2) frictional losses
(3) Neel or Brown relaxation
41.
42. Cancer Treatment
• Heating due to magnetic field results in two possibilities
Death due to overheating
Increase in heat shock
proteins result in
anti-cancer immunity.
Ito A., Honda H., Kobayashi T. Cancer Immunol Immunother Res 2006 55; 320-328
42
43. Delivery Magnetic nanoparticles
• Magnetite nanoparticles
encapsulated in liposomes
– (1) Antibody conjugated
(AML)
– (2) Positive Surface Charge
(MCL)
• Sprague-Dawley rats injected with
two human tumors.
– Liposomes injected into 1
tumor (black) and applied
Alternating Magnetic Field
Ito A., Honda H., Kobayashi T. Cancer Immunol Immunother Res 2006 55; 320-328
43
45. Uses of Nano Magnets
• External Magnetic field for nanoparticle delivery
– Magnetic nanoparticles loaded with drug can be
directed to diseased site for Drug Delivery or MRI
imaging.
46. Magnetic Drug Delivery System
• Using Magnetic Nanoparticles for Drug
Delivery
• Widder & others developed method in late 1970s
• Drug loaded magnetic nanoparticles introduced through IV or IA
injection and directed with External Magnets
• Requires smaller dosage because of targeting, resulting in fewer side
effects
46
47. Magnetic Nanoparticles/Carriers
M
• Magnetite Core
• Starch Polymer Coating
M
M
M
• Bioavailable
• Phosphate in coating for functionalization
• Chemo Drug attached to Coating
M
Magnetite
Core
Starch Polymer
M
M
• Mitoxantrone
• Drug Delivered to Rabbit with Carcinoma
47
48. Results of Drug Delivery
• External magnetic
field (dark)
• deliver more
nanoparticles to tumor
• No magnetic field
(white)
• most nanoparticles in
non tumor regions
Alexiou C et al ANTICANCER RES 27: 2019-2022 (2007)
48
49. Magnetic nanoparticles in medicine
They consist of a metal or metallic oxide core, encapsulated in
an inorganic or a polymeric coating, that renders the particles
biocompatible, stable, and may serve as a support for
biomolecules.
• Drug or therapeutic radionuclide is bound to a magnetic NP,
introduced in the body, and then concentrated in the target area
by means of a magnetic field.
• Depending on the application, the particles release the drug or
give rise to a local effect (hyperthermia).
• Drug release can proceed by simple diffusion or take place
through mechanisms requiring enzymatic activity or changes in
physiological conditions (pH, osmolality, temperature, etc…).
50. Multifunctional Magnetic Nanoparticles
•
•
•
•
Magnetic nanocrystals as ultrasensitive MR contrast agents: MnFe2O4
Anticancer drugs as chemotherapeutic agents: doxorubicin, DOX
Amphiphilic block copolymers as stabilizers: PLGA-PEG
Antibodies to target cancer cells: anti-HER antibody (HER, herceptin)
conjugated by carboxyl group on the surface of the MMPNs
50
Yang, etal. Angew. Chem. 2007, 119, 8992 –8995.
51. Magnetic nanoparticles
The application of magnetic nanoparticles in cancer therapy is one
of the most successful biomedical exploitations of nanotechnology.
The efficacy of the particles in the treatment depends upon the
specific targeting capacity of the nanoparticles to the cancer cells.
Efficient, surface-engineered magnetic nanoparticles open up new
possibilities for their therapeutic potential.
… effective conjugation of folic acid on the surface of
superparamagnetic iron oxide nanoparticles (SPION) enables their
high intracellular uptake by cancer cells.
Such magnetic-folate conjugate nanoparticles are stable for a long
time over a wide biological pH range: additionally, such particles
show remarkably low phagocytosis as verified with peritoneal
macrophages.
52. Conclusions
• Nanomagnets can be made bioavailable by
liposomal encapsulation with targeting
• Nanoparticles smaller than 20 nm can be useful
for local heat generation
• Intracellular hyperthermia kills the cancer cell
and releases heat shock proteins. These are used
to target and kill other cancer cells.
• Results in reduction in growth of tumor size
• Nanomagnets can be used for MR Imaging in
52
vivo
53. MICROBUBBLES
• Used with ultrasound echocardiography and
magnetic resonance imaging (MRI)
• Diagnostic imaging - Traces blood flow and
outlines images
• Drug Delivery and Cancer Therapy
54. MICROBUBBLES
• Small (1-7 µm) bubbles of air (CO2, Helium) or
high molecular weight gases (perfluorocarbon).
• Enveloped by a shell (proteins, fatty acid esters).
• Exist - For a limited time only! 4 minutes-24
hours; gases diffuse into liquid medium after
use.
• Size varies according to Ideal Gas Law
(PV=nRT) and thickness of shell.
55. ultrasound
• Ultrasound uses high frequency sound
waves to image internal structures
• The wave reflects off different density
liquids and tissues at different rates and
magnitudes
• It is harmless, but not very accurate
56. Ultrasound and Microbubbles
• Air in microbubbles in the blood stream have almost 0
density and have a distinct reflection in ultrasound
• The bubbles must be able to fit through all capillaries and
remain stable
Soft Matter, 2008, 4, 2350–2359
Shell:protects the core from oxidation, prevents the leaching of highly toxic Cd 2+ions, improves the quantum yield and the fluorescence efficiency.
(A) Fluorescent capillaries containing
1 M QDs were clearly visible through the skin at the base of the dermis (100 m deep).
Excitation at 900 nm was delivered through a 20 0.95 NA water-immersion objective lens (40
mW out of the objective, average power at the focal plane unknown); the skin was stabilized by a
dorsal skin clamp. Blue pseudocolor is collagen imaged via its second harmonic signal at
450 nm. Dashed line indicates position of line scan shown in (D).
uspio COATING: it reduces the aggregation tendency of the uncoated particles, thus improving their dispersibility and colloidal stability; protects their surface from oxidation;
provides a surface for conjugation of drug molecules and targeting ligands; increases the blood circulation time by avoiding clearance by the reticuloendothelial system;
makes the particles biocompatible and minimizes nonspecific interactions, thus reducing toxicity;
Without coating, opsonin proteins deposit on Magnetite and mark them for removal by RES
Fe+2Fe2+3O4 = Fe3O4
DDS techniques to develop antibody-conjugated liposomes (immunoliposomes) containing magnetite nanoparticles (antibody-conjugated magnetoliposomes, AMLs). The targeting ability of AMLs mainly depends on the specificity of the antibody and the quantity and quality (including homogenous antigen expression) of the antigen on the tumor cell surface.
enhanced by conferring a positive surface charge to liposomes. We have developed ‘‘magnetite cationic liposomes’’ (MCLs) with improved adsorption and accumulation properties.
Unless tumor specific, damage can be done to all cells.
Intracellular hyperthermia is based on the principle that a magnetic particle can generate heat by hysteresis loss under an alternating magnetic field (AMF). In 1979, Gordon et al. A causa del fenomeno dell’isteresi magnetica, l’energia fornita al nucleo durante la fase di magnetizzazione non viene interamente restituita durante quella di smagnetizzazione, ma, ad ogni ciclo,
rimane immagazzinata nel nucleo. Poi si dissipa in calore
Schematic representation of Néel relaxation of nanoparticles, where the magnetic moment rotates within each particle and Brownian relaxation, where the particle rotates as a whole.
Widder and others developed magnetic micro- and nanoparticles to which cytotoxic drugs could be attached in late 1970s (1978).
The drug/carrier complex is then injected into the subject either via intravenous or intra-arterial injection.
High-gradient, external magnetic fields generated by rare earth permanent magnets (generally NdFeB, neodymium magnet, Neodymium, Iron & Boron) are used to guide and concentrate the drugs at target site (ie: tumor locations).
Once the magnetic carrier is concentrated at the tumor or other target in vivo, the therapeutic agent is then released from the magnetic carrier, either via enzymatic activity or through changes in physiological conditions such as pH, osmolality, or temperature, leading to increased uptake of the drug by the tumor cells at the target sites.
Core-shell structure:
Core = magnetic iron oxide (usually magnetite – [Fe3O4] or maghemite [gamma-Fe2O3])
Shell = generally a polymer such as silica, dextran, or PVA, or metals such as gold to which functional groups can be attached vis cross-linkers
Can be synthesized using both ionic and non-ionic surfactant techniques or encapsulated within a structure such as carbon cage or ferritin protein
Functionalized by attaching carboxyl groups, amines, biotin, streptavidin, antibodies, and others.
A number of groups have developed techniques for the synthesis of magnetoliposomes.
Core = magnetic iron oxide
Shell = artificial liposome
Generally used for magnetic hyperthermia (JAMES), but may be useful in drug delivery
More recently, gold/cobalt nanoparticles with core-shell structure and tailorable morphology have been synthesized in the size range of 5-25 nm
Produced via the rapid decomposition of organometallic precursors in the presence of surfactants that control the size and shape of the particles.
Major advantage = cobalt has a magnetic moment nearly twice that of magnetite or maghemite.
Another strategy for synthesis involves the precipitation of magnetic iron oxide nanoparticles within a porous polymer micro- or nanoparticle scaffold.
Advantage = possible to produce particles with a relatively tight size distribution and well-defined, spherical morphology.