Watch our webinar where Professor Marc-Andre Fortin presented about the 3D printing of hydrogels and hydrated substances that have been introduced in various fields of biomedical research including regenerative medicine, cosmetic surgery, orthopedics, and medical physics.
However, one of the main challenges faced by 3D printing and bioprinting is geometrical conformity. In this presentation, studies requiring hydrogel 3D printing in the fields of ophthalmology, regenerative medicine, and medical physics, were described. MRI scanning procedures were developed and optimized for these specific applications.
The presentation highlighted the potential role of MRI in the development of more accurate, more precise 3D-printed hydrogel objects.
(October 12, 2021) Webinar: Clinical Field MRI As A Measurement Instrument for 3D Printing and Bioprinting
1. Clinical Field MRI as a
Measurement
Instrument for 3D
Printing and Bioprinting Marc-André Fortin Ing., Ph.D.
Professor in Biomedical Engineering
Centre de Recherche du Centre
Hospitalier Universitaire de
Québec (CR-CHU de Qc)
Université Laval, Québec, Canada
2. Marc-André Fortin, Ing. PhD
Professor in Materials Engineering, Université Laval and CR-CHU de Québec
Webinar presented for Scintica/Aspect MR, October 12, 2021
Centre de recherche du Centre hospitalier universitaire de Québec – Université Laval, axe Médecine
Régénératrice, Québec, G1L 3L5, QC, Canada; marc-andre.fortin@gmn.ulaval.ca
Clinical field MRI, 3D printing
and bioprinting
2
3. Université Laval in Québec City
• 40 000 students
• 4th oldest higher education institution in North America
• 6th in research funding in Canada
• Areas of excellence (medicine, engineering and science):
– Photonics, Optics, Lasers
– Neurosciences
– Cancer, oncology, medical physics
– Functional materials, biomaterials and regenerative
medicine
4. Fortin’s lab: Laboratoire de Biomatériaux pour l’Imagerie
Médicale (BIM)
Centre Hospitalier Universitaire de Quebec – U. Laval
• Largest Health Research center in Quebec
– 1 600 clinicians, 329 researchers, 208 associated researchers)
• 7th academic health research center in Canada (funding)
• Cancer and oncology, regenerative medicine,
neurology, immunology/infectiology, biomaterials
Biomaterials for Imaging Laboratory’s main topics:
• GOAL: Innovation in biomedical materials for enhanced
visibility in imaging through:
– A) Materials synthesis, B) Materials characterization,
C) Implementation in vivo
5. Biomaterials in Imaging (BIM) laboratory
5
Nanoparticle
synthesis
• One-pot syntheses with
biocompatible precursors
• Plasma nanoparticle synthesis
(several patents);
• 3D printing inks with
nanoparticle-based materials
Advanced Nanomaterials
Characterization
• Bio/organic materials analysis
in scanning electron
microscopy (SEM)
• Elemental analysis of
nanomaterials in transmission
electron microscopy (TEM)
• Surface analysis hybrid (nano)
materials (X-ray photoelectron
spectroscopy (XPS)
In vivo imaging
• Small-animal imaging platform: magnetic resonance
imaging (MRI), X-ray computed tomography (CT),
positron emission tomography (PET)
• Fortin et al; Advanced Healthcare Materials 2018 Aug;7(16):e1701460.
• Fortin et al; in Clinical applications of Magnetic materials, ch 8, CRC press, 2018.
Reviews:
MRI,
CT,PET
6. 2 technology platforms in the lab
Biomaterials
characterization platform
• Nanotechnology lab (DLS,
NMR, UV-Vis)
• XPS, FTIR microscopy,
SEM, AFM (in clean
room), cell culture labs,
3D printing
Small-animal imaging platform
• MRI, CT, PET, ultrasound
imaging
• Radiolabeling lab
8. Outline and content
1. Introduction: contrast agents for T1-w MRI
2. MR-visible paramagnetic coatings for devices
3. Biocompatible ultra-small FeNPs “inks” for 3D
printing
4. 3D-printed contrast-enhanced biogels for eye
cancer phantoms
5. 3D-printed hydrogel implants for cervix
cancer therapy
8
9. Outline and content
• One decade of operation of ASPECT MR 1T :
chronology
9
2010 – 2013: cell tracking with Gd-based agents
2013 – 2018: Development of ultra-small FeNPs to replace Gd-based agents
2018 – : MRI contrast agents for 3D printing, bioprinting, medical physics
2010: installation
2013 – 2016: Gd-based coatings (biopsy needles)
2012
2015
2018
2020
2021
11. Main “whole-body” clinical imaging tools
X-ray computed
tomography (CT)
Magnetic resonance
imaging (MRI)
Positron emission
Tomography (PET)
Res.: 1-2 mm
For: Anatomical
imaging
Ex.:
-skeletal
impairment
-bone density
Res.: ≈1 mm
For: Anatomical
and functional
imaging
Ex.:
-brain, liver, fat
-neural networks
-joint imaging
-inflammation
Res.: ≈ 5 mm
For: Metabolic
and functional
Imaging
(coupled with CT
or MRI)
Ex.:
-glucose met.;
-proteins, fat;
Etc.
12. wavelength l (m)
Nuclear imaging
(PET, SPECT)
X-rays Optical imaging (fluorescence,
bioluminescence, …)
MRI ultrasound imaging
X-ray CT
Principle: attenuation of X-rays
through high-Z elements
Ionizing radiation → number of
repeats limited
Anatomical imaging
Specific applications:
Bone density, structure,
regeneration
Bone regeneration 12
Magnetic resonance imaging (MRI)
Principle: stimulation of hydrogen
protons with radiofrequency
Non-ionizing radiation → no limitation on
the number of scans
Anatomical and functional imaging
Specific applications:
Soft tissue imaging (brain, liver, fat)
Blood flow, oxygenation, water
diffusion
g-rays X-rays Radar
waves
Infra-red Microwave Radio
waves
13. Probes and contrast media for biomedical imaging
13
MRI
• Magnetic nanoparticles and
paramagnetic metal complexes
Review: Laurent S et al, Chem. Rev.
108, 6, 2064-2110 (2008)
X-ray computed
tomography (CT)
• Attenuation of X-rays by
higher-Z elements
Review: Lusic, Grinstaff et al,
Chem. Rev.201311331641-1666
Optical (fluorescent,
luminescent, opto-
acoustic)
• Fluorescent molecules
• Up-converting
luminescent particles
• Near-infrared optical
probes
• Quantum dots
• Review: Kobayashi Chem
Rev. 2010 May 12;
110(5): 2620–2640
Ultrasound imaging
• Micro/nanobubbles
• Review: Paefgen, Kiessling et al, Front. Pharmacol.,
15 Sept. 2015; Du et al, Sci Rep (2018) 8:3887
Nuclear imaging (PET,
SPECT)
• Radiolabeled
molecules;
detection of high-
energy photons
Review: Molecular imaging
with PET; Chem. Rev.108, 5,
1501-1516 (2008)
• Image source: Ghambir et al; Chem. Rev. 117, 3, 901-986 (2017)
14. Introduction: contrast agents for T1-w MRI
• Magnetization of biological
tissues in MRI: dipolar magnetic
moment (m)
– When 1H protons are submitted
to B0, a strong magnetic field,
they align in the direction of this
field
– m is parallel or antiparallel with
respect to B0
– Slightly more on the parallel
energy level.
– Generate Mz
15. Introduction: contrast agents for T1-w MRI
• T1 and T2 are intrinsic characteristics of a tissue
T1: time constant describing
the return of 63% of the spins
to equilibrium
16. Principles of MRI
• Then the RF pulse is turned-off…
The spins progressively re-align in
the direction of B0 (z) … T1
… and meanwhile the spins mutually
influence each-other, giving rise to
dephasing and extinction of the Mxy
component …. T2.
T1: time at 63%
Mz recovery T2: time at 37%
Mxy dephasing
17. Principles of MRI
• By varying TR and TE, spin echo sequences can generate T1- weighted or T2 -
weighted images
– If TR , then 1 − e−TR/T1 1 ; If TR 0 , then 1 − e−TR/T1 = 0
– If TE 0 , then e−TE/T2 1; If TE , then e−TE/T2 = 0
– For ideal T1 – weighting : TR T1,
2
/
1
/
)
1
( T
TE
T
TR
H
xy e
e
M
S
18. Principles of MRI
• T1 and T2 are values intrinsic to each tissue
To change the T1 and T2 of a given tissue, it is necessary to introduce a
CONTRAST AGENT
19. Principles of MRI
• Contrast agents made of gadolinium (Gd) or manganese (Mn)
chelates, as well as Fe-based nanoparticles (NPs) are
currently used in many diagnostic applications performed
under magnetic resonance imaging (MRI).
• MRI detects the signals from hydrogen (1H) protons
stimulated with radiofrequencies
– Biological tissues contain > 60% of 1H protons
“negative contrast agents”:
Fe-based
“positive contrast agents”:
Gd and Mn-based
20. Introduction: contrast agents for T1-w MRI
• T1 relaxation in MRI
– « Positive » CAs: mostly based on
paramagnetic gadolinium (7
unpaired electrons in the 4f orbital)
– Water (1H) protons bind to Gd
contrast agents and influence their
T1 (acceleration of proton
relaxation rate)
– By decreasing the T1 of H, Gd
enhance the MRI signal
2
/
1
/
)
1
( T
TE
T
TR
H
xy e
e
M
S
Faucher, Fortin et al, Nanotechnology. 2011 Jul 22;22(29):295103
Faucher, Fortin et al, ACS Appl. Mater. Interfaces 2012 49, 4506-4515
21. Principles of contrast agents (CAs) in MRI
• « Negative» CAs : iron oxide nanoparticles (5 nm diam. and +)
• Hepatic diagnostics, cell tracking, molecular imaging…
T2*
22. Principles of contrast agents (CAs) in MRI
In brief, MRI signal depends on:
1H : ; T1 ; T2
Short T1 = signal
Long T2 = signal
For optimal signal
enhancement, or
« positive » contrast:
• r1
• T1/T2 (r2/r1) 1
For signal decrease
(« negative contrast» :
• T1/T2 (r2/r1) 10
2
/
1
/
)
1
( T
TE
T
TR
H
xy e
e
M
S
“Positive” CA:
Gd2O3 nanoparticles;
Fortin et al, Langmuir 2011
“Negative” CA:
Fe3O4 nanoparticles;
Fortin, Oh et al,
Biomacromolecules 2014
23. Outline and content
1. Introduction: contrast agents for T1-w MRI
2. MR-visible paramagnetic coatings for
devices
3. Biocompatible ultra-small FeNPs “inks” for 3D
printing
4. 3D-printed contrast-enhanced biogels for eye
cancer phantoms
5. 3D-printed hydrogel implants for cervix
cancer therapy
23
24. MRI-visible biopsy needles
Prostate and breast cancers account for
more than 25% of all cases of cancer
• MRI is the best imaging modality to
detect small nodules (breast) and
focal points of tumor growth
(prostate)
• However: needles are not visible
enough!
• Precision is of utmost importance in
MRI-guided biopsy
– Nodes are small (mm)
– The needle must be precisely
positioned (mm)
– Strong image artifacts:
C.R. Weiss, et al., Journal of Magnetic Resonance Imaging, 2008, 27(2), 311-325
E.R. Price and E.A. Morris, Canadian Association of Radiologists Journal, 2011, 62(1), 15-21
K.M. Pondman, et al., European Urology, 2008, 54(3), 517-527.
Biopsy needle
(7 mm image
artifact)
[4] Penzkofer, T., et al.,
Cardiovasc. Intervent.
Radiol., 2010
25. What happens when a needle is inserted in a MRI voxel?
• MRI voxel (typical size)
• Filled with water (1H2O)
• Insertion of a 23G biopsy
needle
• (0.64 mm OD, 0.36 ID)
• 23% less 1H signal
• Insertion of a 23G biopsy needle
with 70% porous coating
• (1,04 mm OD, 0.36 ID)
• 61% equivalent voxel size filled
with water
• 1 mM of Gd in porous coating
• signal enhancement
26. Conditions for achieving signal enhancement in a small MRI voxel
T1-weighted MRI acquisitions (short TE, medium TR):
less magnetic susceptibility artifacts
Conditions for achieving high signal enhancement:
1. Voxel filled with water (0.2 x 0.2 x 1 mm; >
50% volume)
– A thick, dense polymer coating = NO
– Use water-rich hydrogels instead = YES
2. Contrast agent (Gd) homogeneously
distributed in the voxel
– Optimal balance: between 0.1 and 1.0 mM Gd
3. Direct contact between Gd ions and H2O
– Gd must be sequestrated in a 3D, water-filled
network to constitute functional coatings
Gd
Gd
Gd
MRI
signal
without
contrast
agent
MRI
signal
with
contrast
agent
1
mm
27. Gd-grafted onto mesoporous silica nanoparticles
27
Collaboration: Dr Freddy Kleitz, U.Laval/U.Wien
Laprise-Pelletier, Bouchoucha, Fortin et al, J Mat Chem
B; J. Mater. Chem. B, 2015,3, 748-758
Bouchoucha, Fortin, et al, Chem. Mater.2016, 28, 12,
4243-4258; Langmuir 2017, 3340, 10531-10542
H2O
28. Hydrogel coating (PEG-acrylate +
nanoparticles ) ≈ 50 – 200 microns
thick
titanium needle
(low magnetic
susceptibility;
less MRI artifacts)
Paramagnetic silica
nanoparticles
(Gd3+-labeled)
• Biocompatible
coating
• Large pore volume
for drug elution
function (silica
nanoparticles)
Preparation of TiO2/Ti surface
(phosphonate/acrylate for
hydrogel grafting)
28
Step 1
Step 2
Paramagnetic hybrid silica-PEG coatings for high MRI signal
Nanoparticle synthesis in: Bouchoucha, Fortin,
Kleitz, et al, Chem. Mater.2016, 28, 12, 4243-4258
Silencieux, Fortin et al (submitted)
Step 3
29. 29
1.6 mm diam.
1.05 mm diam.
0.51 mm diam.
T1-w MRI
T = 4h
T = 2 months
T = 4 hours
30. Toward MRI-visible, in vivo implantable 3D
bioprinted objects
MRI-visible coating materials
… used in 3D printing as MRI-
visible bioinks
General problematics of MRI
follow-up with hydrogel
scaffolds: lack of visibility
• ↑ Visibility of bioprinted
objects
• Verification of geometrical
conformity after 3D printing
• Volume and shape follow-up
post-implantation studies
Main problems of Gd-based
contrast agents: potential toxicity
(nephrogenic systemic fibrosis)
• Grobneret al; Nephrol Dial
Transplant. 2006;21(4):1104–
1108.
• No long-term implantation of
Gd-containing objects
• Necessity to use
biocompatible « positive »
MRI contrast agents:
• Ultra-small iron oxide
nanoparticles (< 6 nm diam.)
30
31. Outline and content
1. Introduction: contrast agents for T1-w MRI
2. MR-visible paramagnetic coatings for devices
3. Biocompatible ultra-small FeNPs “inks” for
3D printing
4. 3D-printed contrast-enhanced biogels for eye
cancer phantoms
5. 3D-printed hydrogel implants for cervix
cancer therapy
31
32. Ultra-small iron oxide nanoparticles (USPIONs) for
positive contrast in MRI
32
Collaboration: Dr John Oh, Concordia University, Montreal
Chan, Chevallier, Fortin, Oh et al, Biomacromolecules. 2014 Jun 9;15(6):2146-56.
Xiao, Legros, Fortin, Oh et al, ACS Appl. Nano Mater.2018, 12, 894-907
33. Ultra-small iron oxide nanoparticles (USPIONs) for
positive contrast in MRI
Fortin, Oh et al,
Biomacromolecules, 15, 6,
2146–2156, 2014
34. Ultra-small iron oxide nanoparticles (USPIONs) for
positive contrast in MRI
34
10 mm
0
25
50
75
100
125
0.00
0.50
1.00
1.50
2.00
0 h 24 h 48 h 7 d 14 d 30 d
Contrast-to-noise
ratio
(CNR)
S
x
/S
0
Time
Hydrogel+SPIONs-PEG
CNR
0 h
7 d
30 d
Hydrogel
Water
2 1
3
1. Hydrogel-SPIONs standard
2. Hydrogel standard
3. Water control
A) B)
Iron oxide nanoparticles
(USPIONs) + alginate (2% w/w)
After 30 days, USPIONs progressively diffuse
out of the hydrogels …
+
Fortin et al ACS Appl. Nano Mater. 2018, 1, 894−907
Fortin, Oh et al, Biomacromol., 15, 6, 2146–2156, 2014
35. Ultra-small iron oxide nanoparticles (USPIONs) for
positive contrast in MRI
Fortin et al ACS Appl. Nano Mater. 2018, 1, 894−907
Fortin, Oh et al, Biomacromol., 15, 6, 2146–2156, 2014
abdominal vasculature
liver
gall bladder
41. Biocompatible MRI-visible USPIONs hydrogels
41
Published: WMIC 2021
4M. Vallée, J. F. Côté and J. Fradette, Pathol. Biol., 2009, 57, 309–317.
Collaboration: Dr Julie Fradette, U.Laval LOEX
42. Follow-up of hydrogel implants by MRI
• USPIONs (FeNPs) do not cause
cell toxicity at the concentration
used for positive contrast (paper
submitted)
• USPIONs can be used as an
additive to hydrogel scaffolds
used for 3D printing of
anatomically-relevant implants
• Regenerative medicine
applications where MRI is
needed for the follow-up of soft
tissue:
– Breast reconstruction (e.g. post-
oncology)
– Facial reconstruction
– Fat tissues…
42
Source:www.3dnatives.com
Source: 3dprintingindustry.com;
MRI
Alginate +
adipose cells
+ USPIONs
44. Outline and content
1. Introduction: contrast agents for T1-w MRI
2. MR-visible paramagnetic coatings for devices
3. Biocompatible ultra-small FeNPs “inks” for 3D
printing
4. 3D-printed contrast-enhanced biogels for
eye cancer phantoms
5. 3D-printed hydrogel implants for cervix
cancer therapy
44
45. Current treatment for uveal melanoma
• Brachytherapy implants (episcleral plaques) = radioactive
plaques
• Plaques are sutured on the sclera by surgery
• Removed after 2-7 days by another surgery
45
[2,3]
Eye
Episcleral
plaque
Radioactive
sources Episcleral
plaque
1. Chiu‐Tsao, S. T. et al., (2012). Medical physics, 39(10), 6161-6184.
2. Société canadienne du cancer. https://www.cancer.ca/fr-ca/cancer-information/cancer-type/retinoblastoma/treatment/radiation-therapy/?region=qc
3. Singh, A.D. et al. 2014: Springer Science & Business Media
46. Treatment planning by dose calculations in medical physics
• Radioactive source position in
the plaque must be known
before surgery→ Medical
physicists
• Dose: energy deposited in
matter by ionizing radiation per
unit mass
• The dose profile must match
with the contours of the tumor
as precisely as possible →
isodose
46
1. Schubert, L.K. and M. Miften, 2016, Springer International Publishing: Cham. p. 13-27.
2. Chiu‐Tsao, S. T. et al., (2012). Medical physics, 39(10), 6161-6184.
3. Lesperance, M. et al., Medical Physics, 2014. 41(2): p. 12.
47. Biological
phantom
Hydrogel for a phantom in eye cancer dose planning
To develop by 3D printing, an eye-shaped cell-laden hydrogel
scaffold that could be used for studying the effect of
radiotherapeutic treatments on different types of cells that are
associated with different radiosensitivity levels.
47
2. Development of a 3D printing
procedure for fabricating hydrogel
in the shape of an eye ball
3. Demonstration
of cell viability
1. Development of a
functional hydrogel
formulation
[1]
1. Branco da Cunha, C., et al., Biomaterials, 2014. 35(32)
48. Hydrogel for a phantom in eye cancer dose planning
48
Sclera Choroid
Collagen
Collagen
Proteins Fibers
Fibroblast Fibroblast
Melanocyt
e
1. Institut de l’œil, http://www.institutdeloeil.com/traitement-de-loeil/anatomie-de-loeil.html
2. DENNISTON, Alastair et al. Oxford handbook of ophthalmology. OUP Oxford, 2009.
3. Trier, K., The Sclera, in Advances in Organ Biology, J. Fischbarg, Editor. 2005, Elsevier. p. 353-373.
4. Djigo, A. D. et al., Acta Biomater. (84), 305-316, 2019.
[1]
Melanocyt
e
49. Hydrogel for a phantom in eye cancer dose planning
• Hydrogel: 3D networks of hydrophilic
polymers
• Bioprinting: Layer-by-layer production method
allowing complex geometry printing
• Criteria:
Mechanical properties
High cell proliferation
Biocompatibility
49
1. Lee, K.Y. et al., Progress in Polymer Science, 2012. 37(1): p. 106-126.
2. Di Giuseppe, M., et al., Journal of the Mechanical Behavior of Biomedical Materials, 2018. 79: p. 150-157.
3. Cidonio, G., et al., Biomaterials, 2019. 209: p. 10-24.
4. Hospodiuk, M., et al., 3D printing and biofabrication, 2016: p. 1-27.
50. Hydrogel for a phantom in eye cancer dose planning
• Mechanical function: Alginate (ALG)
– Molecular weight 80-120 kDa, M/G ratio 1.56
• Cellular function: Collagen type I (COL)
– From rat tail tendons
• Printing function: Xanthan gum (XG)
– Thickener material
50
[2]
1. Ozbolat, I.T. et al., Biomaterials, 2016. 76: p. 321-343.
2. Gelinsky, M., et al., Editors. 2018, Woodhead Publishing. p. 125-136
51. Hydrogel for a phantom in eye cancer dose planning
• Optimisation of the printability with xanthan gum
• Goal: obtain a continuous filament
51
XG 1% (w/v), ALG and COL XG 1,7% (w/v), ALG and COL
Addition of xanthan gum improved printability
52. Step 2: development of a 3D printing procedure for
fabricating hydrogels in the shape of an eye ball
• Size close to that of a human eye
• In the hydrogel: diffusion of oxygen and nutrients limited
to only on few millimeters
• Support allows a better oxygen and nutrients supply to the
cells compared to a full hydrogel model
52
1. Denniston, A. and P. Murray, Oxford handbook of ophthalmology. 2009: OUP Oxford.
2. Watson, P.G. and R.D. Young, Experimental Eye Research, 2004. 78(3): p. 609-623.
3. Shanjani, Y., et al., Biofabrication, 2015. 7(4): p. 16.
Sclera
Lattice support
25 mm diameter
53. Step 2: development of a 3D printing procedure for
fabricating hydrogel in the shape of an eye ball
• Development of a
lattice support:
supports cell-containing
hydrogel
• 3D printing: provides a
thin layer of hydrogel
53
54. Step 2: development of a 3D printing procedure for
fabricating hydrogel in the shape of an eye ball
• Evaluation of accuracy of the 3D printing process → Magnetic
resonance imaging (MRI)
• Images are produced by the excitation of hydrogen atoms
• Tridimensional images of the hydrogel
• T1-weighted spin-echo sequence (TR/TE: 742 ms/10.4 ms, FOV 36
mm, 248 x 248, 30 min)
54
55. Step 2: development of a 3D printing procedure for
fabricating hydrogel in the shape of an eye ball
• Measurement of the diameter and the thickness of the hydrogel eye ball
• Diameter (26.2 ± 0.2) mm (eye diameter between 23 and 26 mm)
• Thickness of the hydrogel eye ball (1.3 ± 0.1) mm (sclera thickness at the
back 1-1.35 mm)
55
Eye ball
Eye ball
Axial view Coronal view
T1-weighted spin-echo sequence; TR/TE: 742
ms/10.4 ms, FOV 36 mm, 248 x 248, 30 min
56. Step 3: Demonstration of cell viability
• Cancer cells: cancer cell lines with different radiosensitivity levels (Mµ2 et
Mel270)
• Choiroid cells: choroid fibroblasts
• Time point:
– Day 0: cell viability after printing process
– Day 1: episcleral plaque will be added
– Day 4: episcleral plaque will be removed
56
1. Without printing 2. Printing a simple shape 3. Printing the model
57. Step 3: Cell viability assessment
• Live/dead kit test
– Green staining (calceine AM): live cells
– Red staining (ethidium homodimer-1): dead cells
• Images with epifluorescence microscope
57
Live cells image
Dead cells
image Merge image
58. Step 3: demonstration of cell viability
• Cell viability with and without printing
• Printing parameters do not affect significatively cell viability
58
Choroid fibroblasts
Cancer cell line Mel270 Cancer cell line Mµ2
0 1 4
0
20
40
60
80
100
Cell
Viability
(%)
Days
Mel270 without printing
Mel270 with printing
**
**
*
*p < 0.05
**p < 0.005
0 1 4
0
20
40
60
80
100
Cell
Viability
(%)
Days
Fibroblasts without printing
Fibroblasts with printing
*
**
**
0 1 4
0
20
40
60
80
100
Cell
Viability
(%)
Days
Mµ2 without printing
Mµ2 with printing
**
**
**
**
59. Conclusion: 3D-printed contrast-enhanced biogels
for eye cancer phantoms
• Print the complete in vitro cell-containing phantoms and
measure the cell viability at different time points
• In vitro cell-containing phantoms for testing radiotherapy
plaques
• The model could be used for a better adjustment of dose
calculation planning
59
Current
implant
1. Lesperance, M. et al., Medical Physics, 2014. 41(2): p. 12.
60. Outline and content
1. Introduction: contrast agents for T1-w MRI
2. MR-visible paramagnetic coatings for devices
3. Biocompatible ultra-small FeNPs “inks” for 3D
printing
4. 3D-printed contrast-enhanced biogels for eye
cancer phantoms
5. 3D-printed hydrogel implants for cervix
cancer therapy
60
61. Scientific objective: To develop and characterize a 3D-printed hybrid hydrogel-
nanoparticle formulation as a localized delivery system for cervical cancer therapy.
+ =
Pluronic F127
Alginate
AuNPs
(radiosensitizer)
A 3D-printed hybrid
delivery system
%
NPs
released
Time
Controlled release to the cancerous tissues
Elution/diffusion of gold nanoparticles from
hydrogels
62. Hydrogel implants for cervix cancer therapy
Hainfeld et al., Phys Med Biol. 2004, 49(18), 309-15
Beik et al., Coordination Chemistry Reviews 2019, 387, 299–324
Radiation
Nucleus
Tumor cell
e-
e-
e-
e-
e-
Photo/Auger electron
Radiosensitization effect
Stabilizing agent (e.g. PEG)
• Relative biocompatibility of Au
• High Z number element (Z = 79)
Gold nanoparticles as radiosensitizers
63. Hydrogel for Au NPs elution: PF127-alginate hydrogel
Ca2+ Ca2+
Pluronic F127 Alginate
• Thermosensitive (37 ºC)
• Poor mechanical properties
• Typical concentrations: 15% - 30% w/v
• Gelling agent for vaginal applications
• Cross-linking with divalent cations
• Improved mechanical stiffness and strength
• Typical concentrations: 1% - 5% w/v
Garg et al., Coordination Pharmaceutical Technolog 2001, 25(9), 14-24.
PEO-PPO-PEO
heating
cooling
Sol Gel
PEO PPO H2O
O
O
H
O
OH
99 67 99
64. Printability of the Pluronic F127-alginate ink
Pluronic F127 Alginate H2O
Before cross-linking with Ca2+
Low mechanical strength
37°C
1)
Extrusion-based CELLINK Bio X 3D-printer
ø 10 mm ø 3 mm, h = 3 mm
0.1 M CaCl2
Ca2+
Ca2+
Ca2+
Ca2+
After cross-linking with Ca2+
Improved mechanical strength
2)
65. In vitro degradation study of hydrogel for Au NP
release: scanning electron microscopy study
17
50 µm 50 µm 50 µm
SEM images: 3 kV, spot size 3, no coating, magnification 500 x
Day 1 Day 3 Day 5
(2.3 ± 1.0) µm (12.2 ± 3.4) µm (26.2 ± 7.5) µm
Pore size:
66. The tests were performed using a trypan blue exclusion method (n = 6)
Cytocompatibility of the PF127-alginate gel
HeLa cervical cancer cell line CRL-2616 normal vaginal cell line
> 93% viable
> 90% viable
Hydrogel implants for cervix cancer therapy
67. Biocompatibility of the PF127-alginate gel +/− AuNPs
Right flank:
gel alone/ gel + AuNPs
Left flank:
saline
Group 1,2
n = 6
• PF127 20% w/v, alginate 0.5% w/v
• AuNPs 0.1 mg/ml
• Cytokine test: IL-6, IL-10, MCP-1, IFN-γ,
TNF, IL-12p70
• Histology: H&E
• IHC: F4/80
• Balb/C mice
Day -3:
Blood sampling
12 mice
Day 0:
Administration of the
PF127-alginate gel +/−
AuNPs + MRI
12 mice
Day 3:
Blood sampling
+ MRI
12 mice
Day 10:
Blood sampling
+ MRI
12 mice
Day 14:
Blood sampling
+ MRI
+ histological
assessment
12 mice
68. MRI: in vivo gel degradation
Day 0 Day 3 Day 14
• T1-weighted 2D spin echo sequence (echo time/repetition time: 13.5/704.2 ms)
• 5 excitations
• PF127 20% w/v, alginate 0.5% w/v
69. In vivo degradation profile
**
*
• Group PF127-alginate: ~26% of initial volume
• Group PF127-alginate + AuNPs: ~20% of initial
volume
70. Immunohistochemistry: F4/80 antibody
• F4/80 is a general marker for macrophages (in green)
• Cell nuclei (in blue)
• 20 um thickness of the slide
PF127-alginate gel and surrounding skin Positive control, infected mice
• Microphages are seen on the periphery of the gel
• Mild inflammation response
Many thanks to Dr Dominique Mayrand (PhD, MBA) and Dr Julie Fradette (PhD, Professeur titulaire) for help in histological assessment
G
G
500 um 500 um
500 um
500 um
71. Printability of the Pluronic F127-alginate ink
ø 10 mm, h = 2 mm, 10 layers
ø 3 mm, h = 3 mm, 15 layers
72. 3D-printed hydrogel implants for cervix cancer
therapy
Lens-shaped gels:
T1-w. 2D SE: FOV: 40 mm; 28
slices; 0.9 mm thk; 0.1 mm gap;
dwell time 50 μs; matrix: 304 ×
304; fα 90°; echo asymmetry
50%; TE/TR: 90/3167.2 ms;
duration: 38 min). 3.5 cm
diam.coil.
Hollow tube-shaped gels: mouse
head coil.
T1-w. 2D SE: FOV: 30 mm; 30
slices; 0.6 mm slice thickness;
0.1 mm slice gap; dwell time 50
μs; matrix: 304 × 304; fα 90°;
echo asymmetry 50%; TE/TR:
85/3250.9 ms; 49 min 25 s).
(submitted)
73. Conclusion and perspectives
• Biocompatible polymers and hydrogels are often necessary in the design
of effective therapeutics
• Nanostructured materials for contrast enhancement in MRI are necessary
to design biomedical objects for diagnostic and therapeutic purposes
• Biocompatible materials with enhanced visibility in biomedical imaging
(MRI)
– Fundamentals of both imaging modalities and functional contrast agents
– Contrast agents must be used below toxicity thresholds
• Ultra-small iron oxide nanoparticles: at low concentration, as a functional
ink for 3D bioprinting (MRI visibility, geometrical conformity)
– Applications in medical physics, nanoparticle elution, etc
73
74. Research associates:
• Dr Jenny Roy
• Dr Pascale Chevallier
Students (PhD, MSc):
• Théophraste Lescot
• Mahmoud Omar
• Jean-François Sauvageau
• Mariia Kiseleva
• Sophie Lemay
• Cédric Garceau
• Lucille Samard
• Charlotte Valdenaire
• Samira Ravanbakhsh
• Zongyi Liu
Acknowledgments
Collaborators:
Dr Luc Beaulieu, Dr Claudine Bellerive, Dr Solange Landreville, Dr Julie Fradette, CHU de Québec
75. Announcement: Gold 2022 Conference in Quebec City
Chairs: MA Fortin and E.Boisselier, CR- CHU de Québec – U.Laval www.gold2022.org
Good afternoon everyone. First I would like to thank the organisers for this kind invitation to present the scientific work in our laboratory.
MRI is an imaging modality based on the detection of signal from water protons caused by nuclear magnetic resonance (NMR).
Think of a voxel of MRI as a little cube, typically 1 mm cube, filled with water molecules,
When hydrogen protons are submitted in a strong magnetic field, such as when the patient is inserted in the scanner, the spins align in the direction of the main magnetic field.
The sum of each one the dipolar magnetic moments in the cube, reveals the global magnetization vector for this precise voxel.
The magnetization vector ir directly linked with the total intensity of the signal dected in the voxel.
Then, once the spins have all aligned well along the main magnetic field, a radiofrequency pulse is send, precisely tuned to the excitation frequency of the water.
This results in the flipping of the Magnetization vector along the x-y plane of the scanner (z being the main axis of the scanner).
Once the radiofrequency is stopped, the spins are equalize between the high energy and low energy states. They are also in coherence, so they rotate aroung the z axis in a coherent manner – for a while.
Very rapidly, they loose coherence in the xp-y plane, and this cause the transverse relaxation time (T2).
In parallel with this phenomenon, the spins come back to their intial state between the high and low energy levels, and this cause the magnetization vector Z to come back to its initial state.
This phenomenon is associated to the longitudinal relaxation time T1.
These 2 phenomena are used to generate the contrast effects in MRI.
To generate positive contrast in images while preserving the intensity of the image, T1 relaxation effects must be exploited.
Positive contrast agents usually consist of Gadolinium chelated such as Gd DOTA, or Gd DTPA. These 2 compounds sequestrate the toxic gadolinium ion, and if they leak toward the blood, they are expelled by the kidneys in about 20 minutes.
The paramagnetic Gadolinium has several unpaired electrons in its outer shell and it interacts readily with water molecules thet bind to a complexation site.
This mechanism releases the energy of the hydrogen protons, with cascading effect on the signal intensity in the voxel.
By precisely tuning the echo time, the relaxation time and the concentration of Gd in one voxel, then one can increase the MRI signal.
One example of a medical object that must be carefully designed taking into account the physico-chemistry of nanomaterials, is biopsy needles.
Biopsies performed in MRI are very useful in certain types of cancers that are associated to the presence of nodes (e.g. breast cancer) or focal points (e.g. prostate cancer).
However, so-called MRI compatible needles are made of stainless steel and these needles produce image artifacts that extend far beyond the are of the needle itself. (typically 7 mm here for a 2 mm biopsy needle.
Back to the biopsy needle challenge.
To generate a signal-enhancing surface the number one condition it to preserve a large fraction of water into the coating.
In MRI, hydrogen is signal. If no water remains in the coating, then there will be no signal.
Therefore the surface must be ingineered in 3D, with a certain depth that correspond to the thickness of the image slices.
Also, the materials should not have a strong magnetic susceptibility, otherwise it will change the larmor frequency of the hydrogen protons. Stainless steel is not ideal: I prefer to work with titanium. It has much lower magnetic susceptibility.
Finally, a precise concentration of contrast agent must be sequestrated in the water-filled surface, in order to release the energy of water protons in the coating.
To generate paramagnetic coatings with just the right concentration of Gadolinium, we developed mesoporous suilica nanoparticles functionalised with Gadolinium.
MCM-48 Mesoporous silica nanoparticles have a total pore volume of 70%, so this material provide a highly hydrated scaffold onto which paramagnetic substances csn be grafted.
At a molar concentration of 0.5 mM, these colloids produce a strong signal enhancement in T1-weighted MRI.
And to solve the challenge we take titanium needles (low magnetic susceptibility material)
Polyethylene glycol chanis with phosphonate acrylate moleties are used to attach the hydrogel at the surface of titanium.
Paramagnetic silica nanoparticles are previously dispersed into the polymer.
Overall, the coating is highly hydrophilic.
The hydrogels were measured in MRI right after the preparation, and then up to 2 months in saline conditions.
The hydrogels were tested at different volumes. Here a MRI image of very small volumes of hydrogels.
And finally the titanium needles coated with the paramagnetic hydrogel were visualised in MRI and very clear contours without any sign of image artifact. Therefore, functional for biopsy practices at sub-millimetric precision.
The regulatory requirements for devices and transitory objects such as needles and catheters are less challenging than for biomedical implants.
For moving from devices and transitory objects, into the field of implants which are objects that permanently remain in the body, the requirements are stringents.
We need to to things differently.
One example of changes is the necessity to eliminate gadolinium. Gadolinium is toxic in its unchelated form.
It is not acceptable to use this element in permanent implants, and certainly not for biodegradable implants.
As an alternative to gadolinium contrast agents, we developed PEGylated ultra small iron oxide nanoparticles.
If they are small enough, they can generate psitive contrast in T1-weighted MRI,
In partnership with my collaborator John Oh from Concordia University in Montreal, we developed multidentate block-copolymer-stabilised iron oxide nanoparticles.
The multidentate molecules strongly attach at the surface of these very very small iron oxide nanoparticles and provide colloidal staibility.
The core of the particles in about 4.5 nm in size by TEM analysis, inferior to 20 nm once PEGylated and measured in DLS for hydrodynamic diameter.
The contrast enhancement properties of these colloids revealed a very strong positive contrast at very low iron oxide concentrations (inferior to 0.5 mM). This is about 100 – 1000 times below the cell toxicity thresholds of these products.
We tested the contrast enhancement properties of these colloids as blood pool contrast media in the mouse model. The paricles remain in the blood for several hours.
Then, how do we change a blood contrast media product into a contrast-enhanced hydrogel for regenerative medicine.
The US
USPIONs were dispersed in different formulations of alginate, a natural polymer that crosslinks in the presence of calcium ions.
At a concentration of 2% w alginate and 0.5 mM Fe, the hydrogel scaffolds provide a very strong MRI contrast enhancement.
The contrast was follow-ed in vitro for 30 days ,and we see a progressive elimination of the nanoparticles over time, which is a good thing for tranlational applications
Moving on into objects now.
Any soft biological tissue requires the presence of vasculature to bring nutrients and oxygen, and to take out the metabolic waste.
Therefore we developed an inverted template approach to fabricate pore networks in hydrogels.
Hydrogels were casted onto 3D printed sugar lattices that dissolve upon contact iwith water.
Then, the mixture of iron oxide and hydrogels are poured onto these lattices.
The alginate crosslinks in presence of calcium, and the sugar melts.
Then, the hydrogel networks are visualised in MRI: here without, and with iron oxide nanoparticles.
It is clear that the presence of even very litte concentration of iron oxide nanoparticles provide a very gret tool to visualise the contours of hydrogel implants in regenerative medicine.
S
However, there is no consideration for the radiosensitivity of the different types of cell in the tumor and uveal melanoma is known to be a type of cancer that shows a wide range of radiosensitivity Isodose: Courbe ou surface constituée de points qui reçoivent la même dose de rayonnement dans un milieu irradié.
Assuming the homogeneity of the area and the dose distribution
Development of an hydrogel formulation for optimal cell proliferation
Development of a 3D printing procedure for shaping hydrogel in the form of an eye ball
Demonstration of cell viability
Développer un modèle représentant l’œil humain
Sclère:Collagène I, III et V, élastine, protéoglycans et glycoprotéines
Fibroblastes et des myofibroblastes
Choroïde: Collagène I, III, IV, V et VI, fibres élastiques
Fibroblastes et mélanocytes
3D printing: Layer-by-layer production method allowing complex geometry printing
Balance between cellular viability and printability
The hydrogel is a combination of 3 polymers.
Collagen: Cross-link at 37°C, Cell proliferation, Weak mechanical properties , Improvement of mechanical properties when combined with other materials
However, this material has weak mechanical properties, but they can be improved when collagen is combined with other materials.
Alginate: Hydrogel from brown seaweed Cross-link with Ca2+ ions Biocompatible and non-toxic material
XG:Extracellular polysaccharides of bacteria X. campestris, High molecular weight, Biocompatible and non-toxic material
As a first result, different methods were tested to develop a support.
Resulting optimal combination: alginate 1.35% (w/v), XG 1.7% (w/v) and collagen 1 mg/ml
The hydrogel model will have a size close to that of a human eye. However, in the hydrogel, diffusion of oxygen and nutrients is limited to only on few milimeters. For this reason, a support will be used and it will allow a better oxygen and nutrients supply to the cells compared to a full hydrogel model.
1. Ratner, B.D., et al., Biomaterials Science: An Introduction to Materials in Medicine. 2012: Elsevier Science.
Epifluorescence microscopy,
Preliminary live/dead tests without printing and with a simple 3D printing shape
Plus radiosensible 92.1, moins Mel270
AuNPs will be used because of their therapeutic potential as radiosensitizers in radiotherapy.
AuNPs were chosen because of their therapeutic potential as radiosensitizers in radiotherapy, the modality that is often used for the treatment of cervical cancer. Their presence in tumors would enhance the radiation effect through secondary electron emission because of the ability to highly absorb radiation beam.
In 2004 the ability of AuNPs to enhance the effect of x-ray radiation was demonstrated for the first time. As a result, intravenous injection of 1.9 nm AuNPs along with radiation (up to 2.7 g Au/kg) greatly delayed tumor growth and improved the survival of mice bearing subcutaneous EMT-6 mammary carcinomas. 26 Gy of 250 kVp x-rays
One-year survival was 86% versus 20% with x-rays alone and 0% with gold alone
For this research project, Pluronic F127 (PF127) and alginate were chosen as two components for the hydrogel preparation. PF127 represents synthetic thermosensitive polymer that can rapidly jellify at the temperature close to 37°C by physical crosslinking. This phase behavior makes PF127 ideal for pattering structures in 3D-printing. Moreover, this polymer is listed in the US and European Pharmacopoeia as a gelling agent for vaginal formulations and is being extensively investigated as a potential therapeutics depot for the treatment of cervical cancer in in vitro and in vivo pre-clinical studies. However, purely physical mechanism of the crosslinking results in poor mechanical properties of PF127 gel, which results in rapid degradation of the printed networks upon cooling or immersion.
To achieve optimal mechanical properties of the 3D-printed scaffolds, alginate was added to the polymer composition as a second component. Alginate is a natural anionic polysaccharide that undergoes ionic gelation through chelation of Ca2+ ions by the carboxylic acid groups. Ionic crosslinking offers excellent structural fidelity and improved mechanical stiffness of the formed gel system. In this section, the methodology and preliminary results of characterization of the hydrogel system are discussed.
The printability of the bioink depends on the different parameters such as its viscosity, surface tension, mechanism of crosslinking and the properties of 3D-printing process itself (e.g. applied pressure). The other important desirable aspect for a bioink is high resolution during printing, which also depends on the inner diameter of the nozzle. Therefore, it is necessary to evaluate the processing abilities of the bioink formulation and to optimize parameters of 3D-printing process, such as applied pressure and extrusion speed. Apart from the strong requirements for the printing process, the final mechanical properties of the printed construct should also be sufficient for long-term shape fidelity, manipulation and easy handling. In other words, the resulted scaffolds should have the ability to self-retain the 3D-printed structure after printing. Printability of Pluronic F127-alginate hydrogel was evaluated using the CELLINK BIO X 3D Bioprinter by fabrication of the model scaffolds with lens-shape and rectilinear infill pattern. These structural templates were used for the facile assessment of the print quality and structural fidelity.
Hydrogel scaffolds were 3D-printed by a two-step procedure. Polymer solution was added at room temperature to the printhead, equipped with a plastic nozzle with inner diameter of 0.2 mm. The printhead was then heated up to 37 °C, which resulted in rapid jellification of the PF127 component and formation of the soft gel. Lens-shaped structures were printed at an extrusion rate 10 mm·s-1 with applied pressure 29 kPa on a Petri dish, which was fixed on a printbed preheated at 37 °C. After printing, the soft gel structures were stabilized via ionic crosslinking of alginate chains. For this, 3D-printed scaffolds were immersed in 0.1 mol/L aqueous solution of CaCl2 and after 10 min were rinsed with deionized water to remove the excess of Ca2+ ions.
Finally, cytocompatibility of the gel formulation was investigated using HeLa and CRL-2616 cell lines by incubation these cell lines with the gel formulation and its components separately for 1 and 2 days. All formulations demonstrated no detectable toxicity as cells remained more than 90% viable after 2 days of direct contact.
Now let’s move on to the methodology and results section. I will start with a first sub-objective which is to evaluate biocompatibility of the gel formulation with/without gold nanoparticles when injected subcutaneously. For this experiment, we had 2 groups of mice with 6 mice in each group, one of them was injected with 200 uL of the PF127-alginate polymer solution, and the second one – with the exact same formulation but containing gold nanoparticles. Right after the administration, MRI scan was performed in order to visualize formed implants. MRI was repeated at day 3, 10, and 14 post administration to monitor changes in the gel’s volume as it is being degraded. In parallel, at the same time points we collected blood samples to analyze them for presence of following cytokines. Samples collected 3 days before the injections were used as controls. At the last time point, mice were euthanized, the gels were extracted, and together with surrounding tissue were processed for detection of macrophages.
On this slide you can see MRI scans of the same mouse but at different time points. This mouse was injected with Pluronic-alginate hydrogel without gold nanoparticles. However, I want to note that AuNPs don’t bring anything to the signal in MRI because they are not a contrast agent. Although the gel was administrated without any contrast agent, we can clearly see it on the scans because it’s perfectly delineated by the adipose tissue. Right after injection, we can see that the bulge was formed both visually and on the MRI scan. What we also can notice from these scans is that the gels' volume has declined rapidly in the first three days and at a slower rate until the end of the experiment. There is only a small difference between them at day 3 and day 14.
If we look at the in vivo degradation profile for both groups, we can notice a sharp decrease in the gel’s volume from the injection day to day 3. However, after that, the gel degradation has become very gradual.
In previous in vitro experiments it was demonstrated that the gel disintegration in the first few days was governed by rapid dissolution of the PF127 component that has a very short life in aqueous media. When almost all Pluronic has been washed out, it’s alginate that is left and following degradation of the gel is led by diffusion of calcium ions that held alginate chains together out of the polymer structure.
Overall, ~26% of the initial gels' volume was left at 14-days after administration for the group injected with Pluronic-alginate, and ~20% for the group injected with the gel containing AuNPs. The difference between two groups doesn’t seem big but it’s statistically significant and can be explained by the fact that gold nanoparticles were diffusing out of the polymer network creating micropores and microchannels and exposing the interior of the gel more compared to the group injected with the gel alone. If we look at the in vitro degradation profile that I obtained earlier, we can notice the same tendency: after one day of incubation the gel’s mass more than by half, then they continued to degrade but with a much slower rate until the end of the experiment.
Now I will switch to the next sub-objective which is to evaluate biocompatibility of the administrated gels. This was done by studying both general and local inflammation responses in mice. The local inflammation response was investigated by extracting the gels with surrounding tissues and performing histological assessment on them. For that, together with our collaborators from LOEX we chose to use a general marker for macrophages that is being extensively used for this purpose in the mouse model. On the upcoming images, those macrophages are stained in green, and cell nuclei are stained in blue. On a microscope image of one of the samples, we can see the gel cavity, there are no cells or microphages inside the gel, and a few macrophages on the periphery of the gel. For comparison, here is a microscopy image of the tissue sample of the infected mouse used as a positive control. We can notice a huge number of macrophages, which tells out that a strong inflammation response was developed. This allows to tell us that mice injected with Pluronic-alginate formulation developed only mild to moderate inflammation response.
As a result, Pluronic F127-alginate hydrogel scaffolds were successfully printed in the desired lens-shape and with high resolution down to 0.2 mm. The geometry of the 3D-printed structures was highly reproducible (n>50). After the immersion in CaCl2 solution, obtained gel constructs were stable enough to be transported from the Petri dish and to self-retain the 3D-printed structure.Thus, the combination of thermosensitive PF127 and alginate components resulted in a bioink that can be extruded at high resolution and then effectively crosslinked to produce the gel constructs with sufficient structural fidelity
As a result, Pluronic F127-alginate hydrogel scaffolds were successfully printed in the desired lens-shape and with high resolution down to 0.2 mm. The geometry of the 3D-printed structures was highly reproducible (n>50). After the immersion in CaCl2 solution, obtained gel constructs were stable enough to be transported from the Petri dish and to self-retain the 3D-printed structure.Thus, the combination of thermosensitive PF127 and alginate components resulted in a bioink that can be extruded at high resolution and then effectively crosslinked to produce the gel constructs with sufficient structural fidelity
For the vast majority of the population, all imaging modalities look the same.
In fact, if you ask people around, including workers in the medical field, very few of us know the fundamental differences between MRI, CT, PET and so on.
Perhaps because many of the equipment all looks the same.
In fact, the basic mechanisms of each imaging modality appear to be very different.