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CDAC 2018 Dubini microfluidic technologies for single cell manipulation
1. Microfluidic Technologies
for Single Cell Manipulation
Como, 23 May 2018
Gabriele Dubini
Department of Chemistry, Materials and Chemical Engineering
‘Giulio Natta’
3. Microfluidics is the science of designing, manufacturing, and formulating devices
and processes that deal with volumes of fluid on the order of nanoliters or
picoliters.
What is microfluidics?
4. • Sample and medium - and waste handling - savings: e.g. nL of enzyme,
not mL
• Faster - and cheaper - analyses: can heat, cool small volumes quickly
• Integration: combine lots of steps onto a single device (including
parallelization)
• Automated processes
• Novel physics: diffusion, surface tension, and surface effects dominate
- This can actually lead to faster reactions!
• New functionalities, often impossible at the macroscopic level
Why use microfluidics?
5. van Duinen, Trietsch, Joore, Vulto, Hankemeier. Microfluidic 3D cell culture: from tools to tissue models.
Current Opinion in Biotechnology, 2015; 35: 118-126.
Why use microfluidics?
6. Several reasons make microfluidic devices and systems
interesting also for cell manipulation:
• The increasing interest for living cells
• The integration of several standard analytical
operations
• The possibility to manipulate large numbers of cells
simultaneously
• The possibility of manipulate single objects with cellular
dimension by micromechanics device
http://yoon.eecs.umich.edu/microfluidics.html
Motivation for microfluidics in cell biology
10. An early-concept for an integrated device with two liquid samples
and electrophoresis gel present
Burns et al., Science, 1998
Blue, liquid sample (ready for
metering)
Green, hydrophobic surfaces
Purple, polyacrylamide gel
11. Zhang and Nagrath. Microfluidics and Cancer: Are we there yet? Biomed. Microdevices 2013
13. Laminar and turbulent flow: the Reynolds number
water
ink
µ
ρ
= cLw
Re
x
y
z
wx
τy+dy
τy
dxdydz
x
w
wdxdydz
Dt
Dw x
x
∂
∂
ρ=ρ=forces(inertial)convective
( ) dxdydz
y
w
dxdzdy
y
w
y
dxdzdy
y
dxdz xx
ydyy 2
2
forcesviscous
∂
∂
µ=
∂
∂
µ
∂
∂
=
∂
τ∂
=τ−τ= +
carat
x
L
w
x
w
∝
∂
∂
22
2
caratt
x
L
w
y
w
∝
∂
∂
conduitsindiameterhydraulic
4
lengthsticcharacteri ==== h
t
c D
P
A
L
wwx ∝
16. 0=⋅∇ w
( ) gwww
w
ρ+∇µ+−∇=
∇⋅+
∂
∂
ρ 2
p
t
(mass conservation)
(momentum conservation)
Hypotheses: incompressible, homogeneous, Newtonian fluid
Incompressible, Newtonian fluids:
the Navier-Stokes equations
17. A particular case: 2-D Navier-Stokes equations for steady-state flow
𝜌
𝜕𝑤 𝑥
𝜕𝜕
+ 𝑤 𝑥
𝜕𝑤 𝑥
𝜕𝑥
+ 𝑤𝑧
𝜕𝑤 𝑥
𝜕𝑧
= −
𝜕𝜕
𝜕𝜕
+ 𝜇
𝜕2 𝑤 𝑥
𝜕𝑥2 +
𝜕2 𝑤 𝑥
𝜕𝑧2
𝜌
𝜕𝑤𝑧
𝜕𝜕
+ 𝑤 𝑥
𝜕𝑤𝑧
𝜕𝑥
+ 𝑤𝑧
𝜕𝑤𝑧
𝜕𝑧
= −
𝜕𝜕
𝜕𝜕
+ 𝜇
𝜕2
𝑤𝑧
𝜕𝑥2
+
𝜕2
𝑤𝑧
𝜕𝑧2
𝜕𝑤 𝑥
𝜕𝜕
+
𝜕𝑤𝑧
𝜕𝑧
= 0
𝜕𝜕
𝜕𝜕
= 𝜇
𝜕2
𝑤 𝑥
𝜕𝑧2
and, if the pressure gradient ∂P/∂x is constant and equal to ∆P/L:
𝑤 𝑥 𝑧 =
∆𝑃ℎ2
8𝜇𝜇
1 −
4𝑧2
ℎ2
= 𝑣 𝑚𝑚𝑚 1 −
4𝑧2
ℎ2
−
ℎ
2
≤ 𝑧 ≤ +
ℎ
2
for
x
y
z
L
w
h
h « L
h « w
𝑤 𝑥 =
1
𝐴 𝑡
� 𝑤 𝑥 𝑧 𝑑𝑑
+
ℎ
2
−
ℎ
2
=
2
3
∆𝑃ℎ2
8𝜇𝜇
18. Pressure (P) and shear stress (τ) are different:
• Pressure is the force per unit area acting in the normal direction to an (ideal)
surface within a fluid.
• Shear stress is the force per unit area acting in the tangential direction to an
(ideal) surface within a moving fluid.
Under steady-state conditions, force equilibrium in the longitudinal direction for
the yellow volume of fluid yields:
𝑃𝜋𝑟2
− 𝑃 − ∆𝑃 𝜋𝑟2
= 𝜏 2𝜋𝜋𝜋
∆𝑃
𝑙
=
2𝜏
𝑟
→ 𝜏 𝑟 =
∆𝑃
𝑙
∙
𝑟
2
Pressure and shear stress in a steadily moving fluid
19. Height of the channel (mm)
Pressure and shear stress in a steadily moving fluid
23. Comparison between volume densities of culture conditions in
traditional, macroscale culture in 6-well plates and in microscale,
microchannel culture (750 µm wide, 5 mm long, and 250 µm tall).
Paguirigan and Beebe, BioEssays, 2008
Scale effects
28. Effects of micro domain
– laminar flow
– surface tension
– surface effect
– electrowetting
– diffusion
The behavior of fluids at the microscale
29. Active flow mixers
Laminar flow
Cortelezzi, Ferrari and Dubini. A scalable active micro-
mixer for biomedical applications. Microfluidics and
Nanofluidics 2017; 21(3): article no. 31.
31. Cell responses on surface chemistry of channel walls:
1) surface hydrophobicity
2) protein adsorption
3) surface charge
4) surface roughness
5) surface softness and stiffness
Pinning fluid–fluid interfaces by chemically
inhomogeneous surfaces in static (c) and
flowing systems (d). Altering the wetting
properties using chemically homogeneous,
micro- and nanostructured surfaces: (e, f ).
(Gűnther and Jensen, Lab on a Chip, 2006)
Surface effects
32. Driving force for fluid
motion and the
channel
characteristics can
be chosen
independently
A flow driven by either a pressure
gradient, an electric field, or a
surface tension gradient.
A surface modified chemically in stripes. A surface modified with topography.
Stone et al. Annu. Rev. Fluid Mech., 2004
Surface effects
33. Electrical modulation of the solid-liquid interfacial tension
No Potential
A droplet on a hydrophobic
surface originally has a
large contact angle.
Applied Potential
The droplet’s surface
energy increases, which
results in a reduced contact
angle. The droplet now
wets the surface.
Electrowetting
34. Analyte D (m2/s) Pe
Na+ (100 pm) 10-9 10
Glucose 6×10-10 17
Albumine (BSA, 10 nm) 10-11 103
Viron (100 nm) 10-12 104
Bacterial Cell (1 µm) 10-13 105
Erythrocyte (10 µm) 10-14 106
Polystyrene Bead (100 µm) 10-15 107
Diffusivities and representative Péclet numbers for dilute analytes
in water at 25 °C (100 mm wide channel, 100 mm/s mean velocity)
Smith et al., Electrophoresis, 2012
Diffusion
35. Continuous-flow : Permanently etched microchannels, micropumps and
microvalves
Digital microfluidic : Manipulation of liquids as discrete droplets
Biosensors:
Optical: SPR, Fluorescence, etc.
Electrochemical: Amperometric,
Potentiometric, Impedence-based, etc.
Mixing: Static,
Diffusion Limited
Multiplexing
Microfluidic platforms
37. 𝐷𝐷𝐷𝐷𝐷𝐷𝐷𝐷𝐷𝐷𝐷 𝐷 =
𝑘 𝐵 𝑇
6𝜋𝜋𝜋
𝑃𝑃𝑃𝑃𝑃𝑃 𝑁𝑁𝑁𝑁𝑁𝑁 𝑃𝑃 =
𝑈𝐷ℎ
𝐷
𝑆ℎ𝑒𝑒𝑒𝑒𝑒𝑒 𝑁𝑁𝑁𝑁𝑁𝑁 𝑆ℎ =
ℎ𝐷ℎ
𝐷
Diffusivity characteristic time vs
convective characteristic time
Convective mass flux vs
diffusive mass flux
Parameters from ‘macroscopic’ transport phenomena - 2
38. (a)-(d) Contours of fluorescent light intensity (FLI), which indicate bacterial
concentration, plotted for RP437 E. coli at different time snapshots.
(e)-(h) Bacteria collect in the vortex pair as shown by FLI contours overlaid on the
flow streamlines (solid blue lines) (Yazdi and Ardekani, Biomicrofluidics, 2012).
Local fluid dynamics and cell adhesion
39. Smith et al., Electrophoresis, 2012
𝑆𝑆𝑆𝑆𝑆𝑆 𝑁𝑁𝑁𝑁𝑁𝑁 𝑆𝑆 =
𝜌 𝑝 𝐷 𝑝
2 𝑈
18𝜇𝐷ℎ
Particle time scale vs
flow time scale
PCTC: prostate circulating tumor cell
Local fluid dynamics and cell displacement
40. Smith et al., Electrophoresis, 2012
Local fluid dynamics and cell displacement
41. • rely on a diffusive process to cause cells to randomly move
transverse to streamlines,
• apply a body force (e.g., gravity or dielectrophoresis) to move the
cells transverse to streamlines,
• create geometries in the flow so that flow is accelerated,
streamlines are compressed and the cells are effectively brought in
proximity to the wall by motion along a streamline,
• make the wall permeable and allow the streamlines to cross the
interface.
Possible ways to bring cells in contact to a wall
42. 𝐶𝐶𝐶𝐶𝐶𝐶𝐶𝐶𝐶 𝑁𝑁𝑁𝑁𝑁𝑁 𝐶𝐶 =
𝜇𝑈 𝑑
𝜎
𝐵𝐵𝐵𝐵 𝑁𝑁𝑁𝑁𝑁𝑁 𝐵𝐵 =
∆𝜌 𝑔𝐷ℎ
2
𝜎
𝑊𝑊𝑊𝑊𝑊 𝑁𝑁𝑁𝑁𝑁𝑁 𝑊𝑊 =
𝜇𝑈 𝑑
2
𝐷ℎ
𝜎
Gravity vs interfacial forces
Viscous vs interfacial forces
Inertial vs interfacial forces
Presence of suspended cells multiphase flows
Parameters from ‘macroscopic’ transport phenomena - 3
43. Inertial, viscous and gravitational body forces, relative to interfacial forces,
as a function of the channel size and characteristic velocity in microfluidic
multiphase systems
Gűnther and Jensen, Lab on a Chip, 2006
Parameters from ‘macroscopic’ transport phenomena - 4
44. Strain rates can be large in the microflows.
In the simplest case, τ ≈ U/h, which can yield 103 - 104 s−1.
Such values are sufficiently large to cause non-Newtonian
rheological effects, if suspended deformable objects are
present.
𝐷𝐷𝐷𝐷𝐷𝐷ℎ 𝑁𝑁𝑁𝑁𝑁𝑁 𝐷𝐷 =
𝑡 𝑐
𝑡 𝑝
Material stress relaxation time vs
characteristic time scale
Presence of suspended cells non-Newtonian fluids
A well known effect - since 1929 - is the Fåhraeus effect for
blood flowing in small tubes (I.D. < 0,3 mm).
Parameters from ‘macroscopic’ transport phenomena – 5
45. Bianchi et al. Journal of Biomechanics, 2012
Example 1:
Shear-stress dependent leukocyte adhesion assays
46. mediators
Ronen Alon , Immunity ,2007
Blood flow
Particles interactions
(platelets –
erithrocytes)
τω
Fdragτm
Normal and shear
stresses on the
cell membrane
Normal and shear
stresses on the
endothelial wall
Multiple steps cascades controlled by
integrated chemoattractant-dependent
signals and adhesive events
Endothelial ligands involved in that second step
of firm adhesion are intercellular adhesion
molecules (ICAMs) and vascular cell
adhesion molecules (VCAMs).
inflammation
Leukocyte Shear dependent adhesion and
transmigration across vessel wall in
inflammation
Example 1:
Shear-stress dependent leukocyte adhesion assays
53. Material for the fabrication
of microfluidic channels
Silicon / Si compounds
Classical MEMS approach
Etching involved
Polymers / plastics
New methods
Easy fabrication
57. There are two types of photoresist:
• Positive: Exposure to UV light removes resist
• Negative: Exposure to UV light maintains resist
Mask
Positive Resist Negative Resist
Photolithography
60. Polymethyl methacrylate (PMMA)
• Often used as an alternative to glass
• Easily scratched
• Not malleable
• It can come in the form of a powder mixed
with liquid methyl methacrylate, which is an
irritant and possible carcinogen
64. • Access for colture medium (nutrients, GFs, etc.)
• Access for drug adminstration
• Compatible with robotic system access
• Compatible with micropipetting access
• Suitable for incubator use
• Pressurized vs. open wells
Design requirements
68. PDMS bonded on glass
many valves and tubings
280 wells - up to 600 cells/well
Provides nutrients through lateral
channels and sieves/valves
Up to 5 wells in series
Wells are not accessible with a
pipetting manual/robotic system
Unsuitable for incubator
70. 48 single-cell processing units
Fully automated, including:
• Cell selection and isolation
• Cell culture
• Imaging
• Exposure to drug
• Cell lysis and generation of
cDNA from mRNA
• PCR and cDNA harvesting
https://www.fluidigm.com/products/polaris#components