Some mathematical models of drug deliveryWhy do we need so many drug delivery systems? Some drug...
Transcript of Some mathematical models of drug deliveryWhy do we need so many drug delivery systems? Some drug...
Some mathematical models of drug delivery
Martin Meere, School of Mathematics, Statistics & AppliedMathematics, NUI, Galway.
November 11, 2009
Modelling drug release, 11/11/2009
Why do we need so many drug delivery systems?
Some drug delivery systems
◮ Oral - often used for small-molecule cheap drugs, such asaspirin, paracetomal or ibuprofen
◮ Injections - for example, into a vein, or into a muscle mass, orunder the skin. Often used for larger molecule drugs - insulin,for example
◮ Intravenous drip - allows precise control - often used forserious blood infections
◮ Transdermal patches - nicotine patches, or nitroglycerinpatches for treating agina
◮ Controlled release implants - allows long-term release -contraceptive devices, cancer therapy, delivering protein drugs
Modelling drug release, 11/11/2009
GLIADEL wafer placementA brain tumour cavity lined with polymer wafers loaded with thedrug carmustine. Polymer is poly(lactide-co-glycolide)(PLGA)
Modelling drug release, 11/11/2009
Classification system for diffusion controlled drug deliverysystems
[Siepmann & Siepmann, 2008.]
Modelling drug release, 11/11/2009
A simple barrier release model; drug concentration belowsolubility
c = c(t)
Barrier
= Dissolved drug
c(t)= t.
M(t) = t
V =
M(t) = V c(0)-c(t) .
concentration of drug in reservoir at time
cumulative amount of drug released by time .
Volume of reservoir.
Clearly ( )
The model assumes that
dM(t)
dt∝ c(t) ⇒ dM(t)
dt= α2c(t) = α2 (c(0) − M(t)/V )
⇒ M(t)
M(∞)= 1 − exp(−α2t/V ).
with α2 > 0 constant. First order kinetics.Modelling drug release, 11/11/2009
The barrier release model with drug concentration abovesolubility
Barrier
= Dissolved drug
= Undissolved drug
c=cS
While undissolved drug remains, we have
c(t) = cs , with cs a constant, the solubility.
Hence, for sufficiently short times t, we have
dM(t)
dt∝ cs ⇒ M(t) = α2cst.
Zeroth order kinetics.Modelling drug release, 11/11/2009
MicroparticlesPolymeric microparticles containing nifedipine (treats hypertension)[Hombreiro-Perez et al., 2003]
Modelling drug release, 11/11/2009
The classical diffusion model: Fick’s Law
In the absence of sources/sinks, we have conservation of drugmass:
∂c
∂t+ ∇.j = 0
where for many materials
j = −D∇c , (Fick’s Law.)
so that∂c
∂t= ∇. (D∇c)
Modelling drug release, 11/11/2009
Monolithic devices; drug concentration below solubility
Dissolved drug inpolymeric matrix
c=c(r,t)
r
Drug concentration, c(r , t), can now sometimes be adequatelymodelled by an IBVP for the heat equation:
∂c
∂t=
D
r2
∂
∂r
(
r2 ∂c
∂r
)
in 0 ≤ r < a, t > 0,
c = c0 at t = 0, 0 ≤ r < a,
c = 0 on r = a, t ≥ 0. (Assuming the surface is a perfect sink.)
Modelling drug release, 11/11/2009
The diffusivity, D, is constant here. The problem is linear and canbe solved using separation of variables:
c(r , t) =2ac0
π
∞∑
N=1
(−1)N+1
N
sin (Nπr/a)
rexp
(
−DN2π2t/a2)
which leads to
M(t)
M(∞)= 1 − 6c0
π2
∞∑
N=1
(−1)N+1
N2exp
(
−DN2π2t/a2)
.
Hombreiro-Perez et al., 2003 used this solution to successfullymodel drug release from non-degradable microparticles.
Other simple geometries such as thin films, rectangular blocks, orcylinders can be dealt with similarly.
Modelling drug release, 11/11/2009
Monolithic devices; drug concentration above solubilityThe modelling is more subtle now, and so we consider a simplergeometry.
Modelling drug release, 11/11/2009
The drug concentration c(x , t) in 0 < x < s(t) is governed by:
∂c
∂t= Dm
∂2c
∂x2in 0 < x < s(t), t > 0,
c = 0 on x = 0, t > 0,
c = cs , Dm
∂c
∂x=
ds
dt(c0 − cs) on x = s(t), t > 0.
Problem is self-similar in variable η = x/√
t ⇒ can write c = c(η)and s(t) = α
√t with α constant. The problem has solution:
c = cs
erf(
x
2√
Dmt
)
erf(
α
2√
Dm
) ,
with α determined from
αerf
(
α
2√
Dm
)
exp
(
α2
4Dm
)
= 2
√
Dm
π
cs
c0 − cs
with c0 > cs .
Modelling drug release, 11/11/2009
The Higuchi formula
Here
M(t) = c0s(t) −∫ s(t)
0cdx =
√t × (Complicated function of α)
For c0 ≫ cs , we have α ≪ 1 and
α ≈√
2Dmcs
c0 − cs
⇒ s(t) ≈√
2Dmcst
c0 − cs
Also
M(t) ≈
√
Dmcst(2c0 − cs)2
2(c0 − cs)
which is (essentially) the Higuchi formula. [Higuchi, 1961]
Modelling drug release, 11/11/2009
What is a stent?
A small metal scaffold that is typically placed in a diseasedcoronary artery to hold it open.
Modelling drug release, 11/11/2009
What is a drug eluting stent (DES)?
A stent that is coated with a drug; the drug diffuses into thesurrounding tissue to help prevent restenosis (re-blockage).
Modelling drug release, 11/11/2009
Modelling the behaviour of a DES in the body is typically avery formidable challenge
[Yang & Burt, 2006.]
Modelling drug release, 11/11/2009
Diffusion through the polymer
∂c
∂t= Dp
∂2c
∂x2in − Lp < x < 0,
∂c
∂x= 0 on x = −Lp, (Impenetrable reservoir wall)
c = c0 at t = 0,−Lp < x < 0 (Initial drug load in the polymer)
Convection-diffusion through the artery tissue
∂c
∂t+ v
∂c
∂x= D
∂2c
∂x2in 0 < x < Lw ,
c = 0 on x = Lw , (Boundary condition at outer artery wall)
c = 0 at t = 0, 0 < x < Lw
Boundary condition at polymer/artery interface
(
−Dp
∂c
∂x
)
x=0−=
(
−D∂c
∂x+ vc
)
x=0+
(Flux continuity)
Modelling drug release, 11/11/2009
φ = volume fraction of water.φw = maximum water fraction the polymer can absorb.φc = critical water fraction above which the polymer undergoespolymer chain relaxation.
∂φ
∂t=
∂
∂x
(
D(φ)∂φ
∂x
)
in sw (t) < x < sc(t), t > 0,
φ = φw , D∂φ
∂x=
dsw
dt(1 − φw ) on x = sw (t), t > 0,
φ = φc , D∂φ
∂x= −dsc
dtφc on x = sc(t), t > 0,
sw (0) = sc(0) = 0,
with
D(φ) = D0 exp (βφ) , β > 0. (Fujita-type dependence.)
The conditions for the speeds of the moving boundaries weredetermined using conservation laws.Modelling drug release, 11/11/2009
The problem for the drug concentration can now be posed
With φ(x , t), sw (t), sc(t) calculated, we can now pose the problemfor the drug concentration c(x , t). For example, if the initial drugload in the dry matrix has the constant value c0, and this is belowsolubility, then c(x , t) could satisfy:
∂c
∂t=
∂
∂x
(
D∗(φ)∂c
∂x
)
in sw (t) < x < sc(t), t > 0,
c = 0 on x = sw (t), t > 0,
c = c0 on x = sc(t), t > 0,
withD∗(φ) = D∗
0 exp (β∗φ) , β∗ > 0.
Modelling drug release, 11/11/2009
Thermoresponsive polymersPoly(N-isopropylacrylamide) (PNIPAm) is a smart polymer.
◮ In water, it is hydrophilic below 320C (the LCST).◮ Above 320C, it is hydrophobic.◮ These properties can be exploited to create an on/off switch
for drug release.
Modelling drug release, 11/11/2009
How to model this?One idea. Let TL be the critical temperature at which thetransition occurs. Write
φw (T ) =
{
φ−w for T < TL
0 for T > TL
with 0 < φ−w < 1, and,
φc(T ) =
{
φ−c for T < TL
1 for T > TL
with φ−w > φ−
c . With these conditions
dsw
dt< 0,
dsc
dt> 0 for T < TL (swelling)
anddsw
dt> 0,
dsc
dt< 0 for T > TL (collapsing)
Modelling drug release, 11/11/2009