# Nanomechanical Characterization of Amyloid Fibrils Using Single-Molecule Experiments and Computational Simulations

Authors: Bumjoon Choi; Taehee Kim; Sang Woo Lee; Kilho Eom
Journal: Journal of Nanomaterials
 (2016)

---

## Abstract

Amyloid fibrils have recently received much attention due to not only their important role in disease pathogenesis but also their excellent mechanical properties, which are comparable to those of mechanically strong protein materials such as spider silk. This indicates the necessity of understanding fundamental principles providing insight into how amyloid fibrils exhibit the excellent mechanical properties, which may allow for developing biomimetic materials whose material (e.g., mechanical) properties can be controlled. Here, we describe recent efforts to characterize the nanomechanical properties of amyloid fibrils using computational simulations (e.g., atomistic simulations) and single-molecule experiments (e.g., atomic force microscopy experiments). This paper summarizes theoretical models, which are useful in analyzing the mechanical properties of amyloid fibrils based on simulations and experiments, such as continuum elastic (beam) model, elastic network model, and polymer statistical model. In this paper, we suggest how the nanomechanical properties of amyloid fibrils can be characterized and determined using computational simulations and/or atomic force microscopy experiments coupled with the theoretical models.


---

## Body

## 1. Introduction

Amyloid fibrils, which are formed by self-assembly process (i.e., protein aggregation) [1–4], have recently received significant attention due to not only their important role in disease pathologies [5–9] but also their excellent nanomechanical properties [10]. In particular, amyloid materials have been found to be associated with various diseases such as neurodegenerative diseases [5–7] (e.g., Alzheimer’s disease and Parkinson’s disease), type II diabetes [8], and cardiovascular disease [11]. These amyloid materials exhibit multiscale structural feature [10] such that they are amyloid small aggregate (e.g., amyloid oligomer) at nanoscale, amyloid fibril at submicron scale, and amyloid plaques at micron scale. More remarkably, amyloid materials such as oligomers and fibrils are the ordered structures made of β-strands [1]. This ordered structure of amyloid materials is responsible for their insolubility in physiological condition and also for their remarkable (mechanical) properties. Specifically, β strand-rich protein structures (e.g., amyloid) are stable due to hydrogen bonds that sustain (and stabilize) β-sheet-rich structures [12, 13]. In addition, recent experimental studies [14, 15] report that the mechanical properties of amyloid fibril are determined from the content of β-sheets comprising the fibril in such a way that as the β-sheet content increases the mechanical properties (e.g., elastic modulus) of the fibril are improved.The nanomechanical properties of amyloid fibrils have recently been measured based on experimental and computational techniques. In particular, atomic force microscopy (AFM) or cryo-electron microscopy (EM) imaging techniques coupled with polymer chain statistics have allowed for estimating the bending property (i.e., persistent length) of amyloid fibrils [16, 17]. Specifically, the mechanical properties of protein fibrils are measured based on their fluctuation behavior, which can be obtained from AFM images or cryo-EM images. Recently, this imaging-based mechanical characterization has been implemented in FiberApp [18], which is an open software for analyzing the structures and mechanical properties of protein fibrils based on AFM images. Moreover, AFM nanoindentation technique has enabled the mechanical characterization of amyloid fibrils [19–21]. In addition, computational simulations based on atomistic and/or elastic network models have been extensively employed for characterizing the nanomechanical properties of amyloid fibrils [10, 22–24]. Based on experimental and computational techniques, the elastic modulus of amyloid fibrils is measured in the order of 1 to 10 GPa [10, 22–24], which is comparable to that of a spider silk protein [25], which is known as one of the mechanically strong proteins. Moreover, the toughness of amyloid small aggregates with their size of ~3 nm is measured as ~30 kcal·mol−1·nm−3 [23], which is very close to that of spider silk crystal with its size of ~2 nm. Recent experimental [26] and computational studies [22, 23] report an important role that the length scale of protein fibrils plays in their nanomechanical properties. This length scale effect in the nanomechanical properties of amyloid fibrils is attributed to the fact that the deformation mechanism of the fibrils depends on their length scale.The remarkable mechanical properties of amyloid fibrils have recently been found to play a pivotal role in their biological functions such as disease pathologies [36]. For instance, it has recently been reported that the mechanical disruption of cell membrane due to amyloid fibril [37] is ascribed to the fact that the elastic modulus of amyloid fibrils is in the order of 1 to 10 GPa [10], whereas the elastic modulus of cell membrane is in the order of 100 kPa [38]. This observation suggests an evidence that the nanomechanical properties of amyloid fibrils are highly correlated with their biological functions. Moreover, a recent study by Tanaka and coworkers [39] reports that prion infectivity is determined from the fracture toughness (brittleness) of prion fibrils such that the softer the fibril, the higher the prion infectivity. In addition, as described in our recent study [30], the size-dependent elastic properties of HET-s prion fibrils provide insight into their critical size related to prion infectivity. These observations highlight a role that the nanomechanical properties of amyloid fibrils play in their pathological functions.In this paper, we describe recent attempts to characterize the nanomechanical properties of amyloid fibrils by using experiments and simulations, as the mechanical characterization of the fibrils is of great importance for further understanding of their biological functions. This paper is organized as follows: Section2 summarizes theoretical models such as elastic network model, elastic beam model, and polymer chin model, which can be coupled with experiments or computational simulations in order to measure the mechanical properties of amyloid fibrils. In Section 3, we provide the recent efforts to characterize the nanomechanical properties of amyloid fibrils with using single-molecule experiments based on atomic force microscopy (AFM). Section 4 is dedicated to the review of computational efforts to measure the mechanical properties of amyloid fibrils as well as gain insight into their deformation mechanisms. In Section 5, we conclude this paper with providing remarks and further directions that can be considered for future works.


## 2. Theoretical Models

In this section, we summarize theoretical models that are useful in analyzing the experimental and simulation results to extract the nanomechanical properties of amyloid fibrils. Here, we note that the principles of computational simulations such as atomistic simulation and normal mode analysis are not included in this review, but the principles of these simulations including steered molecular dynamics (SMD) simulations are well described in [40–44]. In addition, though we describe recent experimental attempts to characterize the mechanical properties of amyloid fibrils, we skip the details of AFM experimental methods (e.g., AFM imaging and indentation), which are well summarized in [45]. In the following, we provide theoretical models such as polymer chain model, elastic network model, and continuum elastic beam model.


### 2.1. Polymer Chain Model: Polymer Chain Statistics

Polymer chain models have allowed for understanding the fluctuation behavior of one-dimensional polymer molecules [46]. Among polymer chain models, a wormlike chain (WLC) model [47] has been widely accepted for analyzing the fluctuation behavior of a biological molecule [48, 49] such as DNA chain [50, 51] and protein fibril, for example, microtubule [52]. The WLC model assumes that a biological fibril is composed of rigid subchains. The energy (V) required to bend an angle (θ) between two subchains located a distance ξ apart is given by(1)
V
=
E
B
I
2
ξ
θ
2
,where E
B and I are elastic modulus and cross-sectional moment of inertia for a biological fibril, respectively. A probability distribution function for an angle θ obeys Boltzmann’s distribution such as(2)
p
θ
=
E
B
I
2
ξ
k
B
T
exp
⁡
-
E
B
I
2
ξ
k
B
T
θ
2
,wherek
B and T are Boltzmann’s constant and absolute temperature, respectively. Here, it should be noted that the persistent length (L
P) of a biological fibril is defined as L
P
=
E
B
I
/
k
B
T. The ensemble averages for an angle θ and its cosine value are given by [49](3)
θ
2
=
ξ
L
P
,
(4)
cos
⁡
θ
=
exp
⁡
-
ξ
2
L
P
.The mean-squared value of the end-to-end distance (R) of a biological fibril in a two-dimensional space (i.e., on the surface) is represented in the form of [51](5)
R
2
L
2
=
4
L
L
P
1
-
2
L
P
L
1
-
e
x
p
-
L
2
L
P
,where L is a contour length of a biological fibril.


### 2.2. Elastic Network Model

Coarse-grained (CG) model enables not only the computationally efficient dynamic analysis of protein molecules [41, 53–56] but also the insight into a role that the structure of protein molecules plays in their dynamics and mechanics. The computational efficacy of CG model is due to the modeling strategy in that minimal degrees of freedom are used to model a protein structure with simplified interaction potential field.Among CG models, an elastic network model (ENM) [41, 57–64] is not only a most simple and computationally efficient model, but also a minimalist model which can provide an insight into the role of protein structure on the mechanics and dynamics of a protein molecule. The basic idea of ENM is to consider only the α-carbon atoms of a protein structure, while interaction between these α-carbon atoms is simplified as harmonic interaction. The potential field of ENM is given by(6)
V
=
γ
2
∑
i
,
j
r
→
i
-
r
→
j
-
r
→
i
0
-
r
→
j
0
2
·
H
R
c
-
r
→
i
0
-
r
→
j
0
,where γ is the force constant of a harmonic potential defined between two α-carbon atoms i and j, r
→
i is the position vector of the ith α-carbon atom, superscript 0 indicates the equilibrium state, R
c is a cut-off distance (that is typically defined as R
c = 10~14 Å), and H
(
x
) is a Heaviside unit step function defined as H
(
x
)
=
1 if x
>
0; otherwise, H
(
x
)
=
0. This ENM coupled with normal mode analysis is able to provide the elastic properties of amyloid fibrils, which is well described in [22, 27].


### 2.3. Continuum Model: Elastic Beam Model

Amyloid fibrils can be modeled as a one-dimensional beam model due to their structural feature in that their length is much larger than their thickness. Here, we consider the vibrational and deformation behaviors of the fibril based on Euler-Bernoulli beam theory. In addition, we present the Timoshenko beam theory useful for understanding the length-dependent mechanical properties of amyloid fibrils.


#### 2.3.1. Vibrational Behavior of Fibril Structure

Let us consider the vibrational (bending) motion of amyloid fibril. The equation of motion for a fibril modeled based on Euler-Bernoulli beam [65] is given by(7)
ρ
A
∂
t
2
w
x
,
t
+
∂
x
2
E
I
∂
x
2
w
x
,
t
=
0
,where ρ, A, E, and I represent the density, cross-sectional area, elastic modulus, and cross-sectional moment of inertia of the fibril, respectively, w
(
x
,
t
) is its transverse deflection, and a coordinate x is defined along the fibril axis. With assuming w
x
,
t
=
u
x
·
exp
⁡
[
j
ω
t
], the equation of motion given by (7) becomes an eigenvalue problem as follows:(8)
ω
2
ρ
A
u
=
E
I
∂
x
4
u
. Consequently, the frequency of the fibril is represented in the form of(9)
ω
=
λ
L
2
E
I
ρ
A
,where L is the length of an amyloid fibril and λ is a boundary condition-dependent constant. Equation (9) clearly demonstrates that it is straightforward to compute the elastic modulus (or equivalently, bending rigidity) of an amyloid fibril if its natural frequency was measured from computational simulations (e.g., atomistic simulations or ENM simulations) or experiments (based on 4D electron microscopy). In addition, the torsional shear modulus and axial elastic modulus of amyloid fibrils can be also characterized based on measuring their natural frequencies corresponding to torsional (twisting) and axial stretching deformation modes, respectively. The details of extracting these torsional shear modulus and axial elastic modulus based on the elastic beam model are well described in [22, 27].


#### 2.3.2. Mechanical (Bending) Deformation of Fibril

Let us take into account the force-driven (bending) deformation of an amyloid fibril. The governing equation for the bending deformation of a fibril due to a force is given by [66](10)
∂
x
2
E
I
∂
x
2
w
x
=
q
x
,where q
(
x
) is a distributed load acting on the fibril. In case of a force, F, acting on the specific location (x
=
x
0) of the fibril, the governing equation given by (11) becomes the following equation:(11)
∂
x
2
E
I
∂
x
2
w
x
=
F
·
δ
x
-
x
0
. Here, δ
(
x
) is a Dirac delta function. Consequently, the force-displacement relationship of deformed fibril is given by(12)
W
=
F
L
3
a
E
I
,where W is displacement at the location where a force is applied; that is, W
=
w
(
x
0
); a is a constant that depends on boundary condition and the location at which a force is applied. It is straightforward to extract the bending rigidity (or bending elastic modulus) of an amyloid fibril, if its force-displacement relationship (i.e., F versus W) is obtained from simulation or experiment.


#### 2.3.3. Timoshenko Beam Model: Length-Dependent Property

For understanding the effect of fibril length on the bending properties of protein fibril, recent studies [22, 23, 27, 30, 52, 67] have employed the Timoshenko beam theory [68], which assumes that the deformation of the fibril is attributed to both shear and bending deformations. The total deflection of the fibril is represented in the form of(13)
W
=
F
L
3
a
E
I
+
c
F
L
b
G
S
A
,where G
S and A represent the shear modulus and cross-sectional area of an amyloid fibril, respectively, b is a boundary condition-dependent constant, and c is a shear coefficient that depends on the cross-sectional shape of an amyloid fibril. From (13), the effective bending rigidity of an amyloid fibril is given by(14)
E
~
I
=
E
I
1
+
a
b
c
E
I
G
S
A
L
2
-
1
.The Timoshenko beam theory given by (14) provides the length-dependent bending rigidity of an amyloid fibril, which is ascribed to competition between shear and bending deformations.


## 2.1. Polymer Chain Model: Polymer Chain Statistics

Polymer chain models have allowed for understanding the fluctuation behavior of one-dimensional polymer molecules [46]. Among polymer chain models, a wormlike chain (WLC) model [47] has been widely accepted for analyzing the fluctuation behavior of a biological molecule [48, 49] such as DNA chain [50, 51] and protein fibril, for example, microtubule [52]. The WLC model assumes that a biological fibril is composed of rigid subchains. The energy (V) required to bend an angle (θ) between two subchains located a distance ξ apart is given by(1)
V
=
E
B
I
2
ξ
θ
2
,where E
B and I are elastic modulus and cross-sectional moment of inertia for a biological fibril, respectively. A probability distribution function for an angle θ obeys Boltzmann’s distribution such as(2)
p
θ
=
E
B
I
2
ξ
k
B
T
exp
⁡
-
E
B
I
2
ξ
k
B
T
θ
2
,wherek
B and T are Boltzmann’s constant and absolute temperature, respectively. Here, it should be noted that the persistent length (L
P) of a biological fibril is defined as L
P
=
E
B
I
/
k
B
T. The ensemble averages for an angle θ and its cosine value are given by [49](3)
θ
2
=
ξ
L
P
,
(4)
cos
⁡
θ
=
exp
⁡
-
ξ
2
L
P
.The mean-squared value of the end-to-end distance (R) of a biological fibril in a two-dimensional space (i.e., on the surface) is represented in the form of [51](5)
R
2
L
2
=
4
L
L
P
1
-
2
L
P
L
1
-
e
x
p
-
L
2
L
P
,where L is a contour length of a biological fibril.


## 2.2. Elastic Network Model

Coarse-grained (CG) model enables not only the computationally efficient dynamic analysis of protein molecules [41, 53–56] but also the insight into a role that the structure of protein molecules plays in their dynamics and mechanics. The computational efficacy of CG model is due to the modeling strategy in that minimal degrees of freedom are used to model a protein structure with simplified interaction potential field.Among CG models, an elastic network model (ENM) [41, 57–64] is not only a most simple and computationally efficient model, but also a minimalist model which can provide an insight into the role of protein structure on the mechanics and dynamics of a protein molecule. The basic idea of ENM is to consider only the α-carbon atoms of a protein structure, while interaction between these α-carbon atoms is simplified as harmonic interaction. The potential field of ENM is given by(6)
V
=
γ
2
∑
i
,
j
r
→
i
-
r
→
j
-
r
→
i
0
-
r
→
j
0
2
·
H
R
c
-
r
→
i
0
-
r
→
j
0
,where γ is the force constant of a harmonic potential defined between two α-carbon atoms i and j, r
→
i is the position vector of the ith α-carbon atom, superscript 0 indicates the equilibrium state, R
c is a cut-off distance (that is typically defined as R
c = 10~14 Å), and H
(
x
) is a Heaviside unit step function defined as H
(
x
)
=
1 if x
>
0; otherwise, H
(
x
)
=
0. This ENM coupled with normal mode analysis is able to provide the elastic properties of amyloid fibrils, which is well described in [22, 27].


## 2.3. Continuum Model: Elastic Beam Model

Amyloid fibrils can be modeled as a one-dimensional beam model due to their structural feature in that their length is much larger than their thickness. Here, we consider the vibrational and deformation behaviors of the fibril based on Euler-Bernoulli beam theory. In addition, we present the Timoshenko beam theory useful for understanding the length-dependent mechanical properties of amyloid fibrils.


### 2.3.1. Vibrational Behavior of Fibril Structure

Let us consider the vibrational (bending) motion of amyloid fibril. The equation of motion for a fibril modeled based on Euler-Bernoulli beam [65] is given by(7)
ρ
A
∂
t
2
w
x
,
t
+
∂
x
2
E
I
∂
x
2
w
x
,
t
=
0
,where ρ, A, E, and I represent the density, cross-sectional area, elastic modulus, and cross-sectional moment of inertia of the fibril, respectively, w
(
x
,
t
) is its transverse deflection, and a coordinate x is defined along the fibril axis. With assuming w
x
,
t
=
u
x
·
exp
⁡
[
j
ω
t
], the equation of motion given by (7) becomes an eigenvalue problem as follows:(8)
ω
2
ρ
A
u
=
E
I
∂
x
4
u
. Consequently, the frequency of the fibril is represented in the form of(9)
ω
=
λ
L
2
E
I
ρ
A
,where L is the length of an amyloid fibril and λ is a boundary condition-dependent constant. Equation (9) clearly demonstrates that it is straightforward to compute the elastic modulus (or equivalently, bending rigidity) of an amyloid fibril if its natural frequency was measured from computational simulations (e.g., atomistic simulations or ENM simulations) or experiments (based on 4D electron microscopy). In addition, the torsional shear modulus and axial elastic modulus of amyloid fibrils can be also characterized based on measuring their natural frequencies corresponding to torsional (twisting) and axial stretching deformation modes, respectively. The details of extracting these torsional shear modulus and axial elastic modulus based on the elastic beam model are well described in [22, 27].


### 2.3.2. Mechanical (Bending) Deformation of Fibril

Let us take into account the force-driven (bending) deformation of an amyloid fibril. The governing equation for the bending deformation of a fibril due to a force is given by [66](10)
∂
x
2
E
I
∂
x
2
w
x
=
q
x
,where q
(
x
) is a distributed load acting on the fibril. In case of a force, F, acting on the specific location (x
=
x
0) of the fibril, the governing equation given by (11) becomes the following equation:(11)
∂
x
2
E
I
∂
x
2
w
x
=
F
·
δ
x
-
x
0
. Here, δ
(
x
) is a Dirac delta function. Consequently, the force-displacement relationship of deformed fibril is given by(12)
W
=
F
L
3
a
E
I
,where W is displacement at the location where a force is applied; that is, W
=
w
(
x
0
); a is a constant that depends on boundary condition and the location at which a force is applied. It is straightforward to extract the bending rigidity (or bending elastic modulus) of an amyloid fibril, if its force-displacement relationship (i.e., F versus W) is obtained from simulation or experiment.


### 2.3.3. Timoshenko Beam Model: Length-Dependent Property

For understanding the effect of fibril length on the bending properties of protein fibril, recent studies [22, 23, 27, 30, 52, 67] have employed the Timoshenko beam theory [68], which assumes that the deformation of the fibril is attributed to both shear and bending deformations. The total deflection of the fibril is represented in the form of(13)
W
=
F
L
3
a
E
I
+
c
F
L
b
G
S
A
,where G
S and A represent the shear modulus and cross-sectional area of an amyloid fibril, respectively, b is a boundary condition-dependent constant, and c is a shear coefficient that depends on the cross-sectional shape of an amyloid fibril. From (13), the effective bending rigidity of an amyloid fibril is given by(14)
E
~
I
=
E
I
1
+
a
b
c
E
I
G
S
A
L
2
-
1
.The Timoshenko beam theory given by (14) provides the length-dependent bending rigidity of an amyloid fibril, which is ascribed to competition between shear and bending deformations.


## 2.3.1. Vibrational Behavior of Fibril Structure

Let us consider the vibrational (bending) motion of amyloid fibril. The equation of motion for a fibril modeled based on Euler-Bernoulli beam [65] is given by(7)
ρ
A
∂
t
2
w
x
,
t
+
∂
x
2
E
I
∂
x
2
w
x
,
t
=
0
,where ρ, A, E, and I represent the density, cross-sectional area, elastic modulus, and cross-sectional moment of inertia of the fibril, respectively, w
(
x
,
t
) is its transverse deflection, and a coordinate x is defined along the fibril axis. With assuming w
x
,
t
=
u
x
·
exp
⁡
[
j
ω
t
], the equation of motion given by (7) becomes an eigenvalue problem as follows:(8)
ω
2
ρ
A
u
=
E
I
∂
x
4
u
. Consequently, the frequency of the fibril is represented in the form of(9)
ω
=
λ
L
2
E
I
ρ
A
,where L is the length of an amyloid fibril and λ is a boundary condition-dependent constant. Equation (9) clearly demonstrates that it is straightforward to compute the elastic modulus (or equivalently, bending rigidity) of an amyloid fibril if its natural frequency was measured from computational simulations (e.g., atomistic simulations or ENM simulations) or experiments (based on 4D electron microscopy). In addition, the torsional shear modulus and axial elastic modulus of amyloid fibrils can be also characterized based on measuring their natural frequencies corresponding to torsional (twisting) and axial stretching deformation modes, respectively. The details of extracting these torsional shear modulus and axial elastic modulus based on the elastic beam model are well described in [22, 27].


## 2.3.2. Mechanical (Bending) Deformation of Fibril

Let us take into account the force-driven (bending) deformation of an amyloid fibril. The governing equation for the bending deformation of a fibril due to a force is given by [66](10)
∂
x
2
E
I
∂
x
2
w
x
=
q
x
,where q
(
x
) is a distributed load acting on the fibril. In case of a force, F, acting on the specific location (x
=
x
0) of the fibril, the governing equation given by (11) becomes the following equation:(11)
∂
x
2
E
I
∂
x
2
w
x
=
F
·
δ
x
-
x
0
. Here, δ
(
x
) is a Dirac delta function. Consequently, the force-displacement relationship of deformed fibril is given by(12)
W
=
F
L
3
a
E
I
,where W is displacement at the location where a force is applied; that is, W
=
w
(
x
0
); a is a constant that depends on boundary condition and the location at which a force is applied. It is straightforward to extract the bending rigidity (or bending elastic modulus) of an amyloid fibril, if its force-displacement relationship (i.e., F versus W) is obtained from simulation or experiment.


## 2.3.3. Timoshenko Beam Model: Length-Dependent Property

For understanding the effect of fibril length on the bending properties of protein fibril, recent studies [22, 23, 27, 30, 52, 67] have employed the Timoshenko beam theory [68], which assumes that the deformation of the fibril is attributed to both shear and bending deformations. The total deflection of the fibril is represented in the form of(13)
W
=
F
L
3
a
E
I
+
c
F
L
b
G
S
A
,where G
S and A represent the shear modulus and cross-sectional area of an amyloid fibril, respectively, b is a boundary condition-dependent constant, and c is a shear coefficient that depends on the cross-sectional shape of an amyloid fibril. From (13), the effective bending rigidity of an amyloid fibril is given by(14)
E
~
I
=
E
I
1
+
a
b
c
E
I
G
S
A
L
2
-
1
.The Timoshenko beam theory given by (14) provides the length-dependent bending rigidity of an amyloid fibril, which is ascribed to competition between shear and bending deformations.


## 3. Single-Molecule Force Spectroscopy-Based Mechanical Characterization of Amyloid Fibrils

Single-molecule force spectroscopy based on optical tweezer or AFM is a useful experimental toolkit that allows for mechanical characterization of protein materials at molecular scale [69–72]. For a recent decade, single-molecule force spectroscopy has been utilized to probe the mechanical properties of amyloid fibrils [10, 45]. Here, we briefly provide the recent key efforts to experimentally characterize the nanomechanical properties of amyloid fibrils using force spectroscopy based on AFM.In recent years, Knowles and coworkers [32] have reported the nanomechanical properties of amyloid fibrils using AFM imaging experiments coupled with polymer chain statistics that is described in Section 2.1. In particular, they measured the fluctuation of angle between two tangent vectors, which results in the extraction of mechanical properties such as persistent length—for example, see (3)—from the AFM images of amyloid fibrils. The nanomechanical properties of several amyloid fibrils such as α-lactalbumin fibril, insulin β-chain fibril, β-lactoglobulin fibril, insulin fibril, and TTR (105–115) fibril were measured using AFM imaging experiments coupled with polymer chain statistics. The bending elastic modulus of these fibrils is measured in a range of 1 to 10 GPa (Figure 1). They found that, based on AFM experiments and simulations such as atomistic simulations and ENM, the excellent mechanical properties of these fibrils are attributed to intermolecular forces that act between β-sheet layers (Figure 1). In addition, they reported that the elastic modulus of amyloid fibril is close to that of mechanically strong spider silk protein and that the fracture property of amyloid fibril is related to the growth mechanisms of amyloid fibrils [26].Figure 1
Nanomechanical properties of amyloid fibrils and the role of intermolecular forces in the nanomechanical properties. The elastic modulus of amyloid fibrils is measured in a range of 1 to 10 GPa (blue region in the graph), and this elastic modulus is comparable to that of dragline silk. The nanomechanical properties of amyloid fibrils are measured based on AFM-based single-molecule experiments and simulations such as full-atomistic simulations, backbone-based atomistic simulations, and elastic network model (as shown in figures from lower left panel to lower right panel, resp.). Figures are adopted with permission from [32].Recently, Adamcik and colleagues have reported the nanomechanical properties of multistranded amyloid fibrils using AFM imaging experiments together with polymer chain statistics [16] (Figure 2). They reported that amyloid fibrils can be formed as a multistranded fibril that is composed of single to five filaments. They found that the helical structure of a multistranded amyloid fibril is determined by interaction between filaments comprising the fibril. In addition, the persistent length of amyloid fibril is critically dependent on the number of filaments comprising the fibril such that the persistent length of the fibril increases with respect to the number of filaments. This has been elucidated based on helical ribbon model, which suggests that the increase of persistent length with respect to the number of filaments is attributed to the fact that the cross-sectional moment of inertia of the fibril increases with respect to the number of filaments. Furthermore, Usov and Mezzenga elaborated the theoretical model based on continuum elastic (beam) theory in order to understand the nanomechanical properties of amyloid fibrils with respect to their various conformations based on AFM experiments of the fibrils [73].Figure 2
Nanomechanical properties of multistranded amyloid fibrils. (a) Schematic illustration of measuring the angle between two tangent vectors to extract the mechanical properties of the fibril using polymer chain statistics. (b) The ensemble averages of correlation functions (defined as cosine values of angles) for a multistranded fibril made of single (blue), two (red), and three (yellow) filaments, respectively, are measured from AFM experiments. The measured experimental results (indicated by blue, red, and yellow dots) are well fitted to theoretical predictions from polymer chain statistics (indicated by blue, red, and yellow lines). (c) Persistent length and helical pitch for amyloid fibrils composed of single, two, and three filaments, respectively. (d) The distribution of the difference between maximum and minimum AFM heights (thicknesses) of amyloid fibrils. (e) AFM images (shown in lower panel) and corresponding coarse-grained models (shown in upper panel) provide the left-handed multistranded amyloid fibrils made of one to five filaments, respectively. Figures are adopted with permission from [16].
(a)
(b)
(c)
(d)
(e)In addition to AFM imaging experiment, AFM-based nanoindentation has been considered to characterize the mechanical properties of amyloid fibrils. Adamcik and colleagues employed an AFM-based peak force QNM (quantitative nanomechanical mapping) technique to characterize the nanomechanical properties ofβ-lactoglobulin amyloid fibrils [19]. They found that the elastic modulus of β-lactoglobulin fibril is estimated as 3.3 GPa. A recent study by Sweers and coworkers [20] has suggested that the elastic modulus of α-synuclein fibril was measured as 1.3~2.1 GPa from AFM-based peak force QNM experiments (Figure 3). A previous study by Guo and Akhremitchev [21] reports the elastic modulus of insulin fibrils using AFM indentation experiments. Their study provides that the elastic modulus of insulin fibril is measured in a range of 5 to 50 MPa. In recent years, Gsponer and colleagues [28] utilized the AFM experiments (based on amplitude modulation-frequency modulation imaging, referred to as AM-FM imaging) to measure the mechanical properties of prion amyloid fibrils. They found that the radial elastic modulus of prion fibrils is measured in a range of 0.5 to 1.3 GPa and that this radial elastic property critically depends on their thickness in such a way that the radial elastic modulus of the fibrils decreases as their thickness increases.Figure 3
AFM peak force QNM- (quantitative nanomechanical mapping-) based experiments ofα-synuclein amyloid fibrils. (a) and (c) show the AFM topographic images of the fibrils, while (b) and (d) present the AFM peak force QNM images of the fibrils. Here, (a) and (b) are obtained from AFM QNM experiments of the fibrils in liquid environment, while (c) and (d) are acquired based on AFM QNM imaging of the fibrils in ambient condition. Figures are adopted from [20] under Creative Commons Attribution (CCA).
(a)
(b)
(c)
(d)


## 4. Computational Simulation-Based Mechanical Characterization of Amyloid Fibrils

### 4.1. Nanomechanical Characterization Based on the Vibration of Amyloid Fibrils

A recent study by Xu and coworkers [27] considers ENM simulations to measure the vibrational characteristics of Aβ fibrils and their elastic properties. They found that the low-frequency dynamic modes of these fibrils correspond to twisting, bending, or axial stretching deformation modes (Figure 4) and that the elastic moduli of amyloid fibrils are dependent on their length scales. In addition, they report that the twisting (or helical) conformation of amyloid fibrils results in their isotropic bending property when the fibril length is >150 nm. Recently, our previous study [22] reports the nanomechanical properties of human islet amyloid polypeptide (hIAPP) fibrils, which are formed based on four different types of steric zipper patterns, based on ENM simulations. We found that as the fibril length increases, the torsional and axial stretching deformation modes of the fibril become the high-frequency dynamic modes, while the bending deformation mode corresponds to the low-frequency mode independent of fibril length (Figure 5(a)). This indicates that the thermal fluctuation behavior of an amyloid fibril is mostly contributed by the bending deformation mode, that is, a low-frequency mode. In addition, we have shown that the dependence of the bending rigidity (or persistent length) of amyloid fibrils on their length scales is well fitted to Timoshenko beam model (Figure 5(b)), which suggests that the bending property of the fibrils is attributed to competition between shear and bending deformation modes. Moreover, we have also studied the nanomechanical properties of prion amyloid fibrils based on ENM [30]. It is found that the mechanical properties of prion fibrils significantly depend on their β-helical structures and that the length-dependent mechanical properties of prion fibrils provide an insight into their critical size, at which prion infectivity is maximized.Figure 4
Vibrational characteristics of Aβ amyloid fibrils computed from elastic network model. Four low-frequency vibrational modes correspond to the twisting, two bending, and axial stretching modes, respectively. Here, low-frequency vibrational modes are shown for three different types of Aβ amyloid fibrils with their length of 9.64, 19.28, and 28.92 nm, respectively. Figures are adopted with permission from [27].Figure 5
Length-dependent vibrational and nanomechanical properties of human islet amyloid polypeptide (hIAPP) fibrils computed from the elastic network model. (a) The mode index for three dominant deformation modes such as bending, torsional, and axial stretching deformation modes, respectively, is shown as a function of fibril length. As the fibril length increases, the torsional and axial deformation modes become the high-frequency vibrational modes, while the bending deformation modes are the low-frequency vibrational modes without any dependence on the fibril length. (b) The bending rigidity of hIAPP amyloid fibrils is shown as a function of their length scales based on ENM simulations. Figures are adopted with permission from [22].
(a)
(b)In recent years, we have studied the vibrational characteristics of hIAPP (20–29) fibrils, which are formed based on the eight possible conformations of the fibrils as suggested in [33, 74] (Figure 6(a)), based on atomistic molecular dynamics (MD) simulations together with continuum elastic beam model [24]. We have shown that the fibril structure becomes stable when the fibril is formed based on antiparallel stacking of β-sheets (Figure 6(b)) and that the frequencies of the fibrils for their bending deformation modes are measured in the order of 0.2 THz, which is much larger than the frequencies measured by 4D electron microscopy experiments [36]. The discrepancy between frequencies measured from MD simulations and 4D electron microscopy experiments is attributed to the fact that the fibril length considered for MD simulation is less by a few orders of magnitude than that for 4D electron microscopy experiment. In addition, we have shown that the bending rigidity of hIAPP fibril becomes optimized when the fibril is formed based on the antiparallel stacking and that the mutation of phenylalanine to leucine in hIAPP (20–29) leads to the decrease of not only the structural stability but also the bending rigidity of hIAPP (20–29) fibril. Moreover, a recent study by Chang et al. [75] reports the effect of aromatic residue (i.e., phenylalanine) on the vibrational characteristics and mechanical properties of Aβ amyloid fibrils using MD simulations coupled with continuum elastic beam model. They found that aromatic residue such as phenylalanine plays a key role in stabilizing the structure of amyloid fibrils and in optimizing their mechanical properties.Figure 6
(a) Structural models of amyloid fibrils. These structural models are theoretically provided based onβ-sheet stacking patterns such as parallel or antiparallel stacking. Figures are adopted with permission from [33]. (b) Atomistic molecular dynamics simulations provide the equilibrium structures of hIAPP amyloid fibrils based on the structural models. Figures are adopted from [24] under Creative Commons Attribution (CCA).
(a)
(b)Our recent study [34] reports the structure and vibrational (or equivalently mechanical) properties of a multistranded amyloid fibril by using atomistic MD simulations coupled with ENM. Specifically, MD simulation was used to understand the structure of a multistranded β
2-microglobulin fibril, whereas ENM was utilized to characterize their vibrational and mechanical properties (Figure 7(a)). Our previous study found that the dependence of the helical structure of β
2-microglobulin fibril on the number of filaments comprising the fibril is attributed to the nonbonded interactions between filaments, which is consistent with AFM-based experimental study of β-lactoglobulin fibril [16]. In particular, MM-PBSA calculations suggest that as the number of filaments comprising the β
2-microglobulin fibril increases, the molecular mechanics energy of the fibril is decreased and it is mostly contributed by nonbonded energy such as electrostatic and van der Waals interaction energies [34]. Moreover, our previous study suggests the persistent length of amyloid fibrils as a function of the number of filaments comprising the fibril with using ENM simulation coupled with continuum beam model. The dependence of the persistent length on the number of filaments is well fitted to a scaling law of L
P
∝
n
q
2
-
sin
2
⁡
n
q
1
/
2 for a helical fibril model [73] (Figure 7(b)).Figure 7
Nanomechanical properties ofβ
2-microglobulin fibrils made of one to five filaments, respectively. (a) The length-dependent effective bending rigidity of β
2-microglobulin fibrils composed of one to five filaments, respectively. (b) The intrinsic bending rigidity of β
2-microglobulin fibrils made of two to five filaments, respectively, is shown as a function of the number of filaments comprising the fibrils. The dots indicate the results of ENM simulations, while solid line presents the theoretical prediction from continuum helical fibril model. Figures are adopted with permission from [34].
(a)
(b)


### 4.2. Mechanical Deformation Mechanisms of Amyloid Fibrils

Mechanical characterization of amyloid fibrils based on measuring their vibrational characteristics is insufficient to gain insight into the mechanical behaviors and properties of amyloid fibrils, as the vibrational properties of the fibrils are correlated with only their elastic moduli [76]. In particular, the vibrational characteristics of amyloid fibrils cannot provide the quantitative insight into the fracture behaviors and properties of amyloid fibrils. Here, we take a look at the mechanical deformation mechanisms and properties of amyloid fibrils based on two types of deformation modes such as (i) axial deformation and (ii) bending-like deformation.First, we consider recent attempts to characterize the axial deformation behavior of amyloid fibrils. A recent study by Dong et al. [35] reports the axial extension of prion fibrils using optical tweezer force spectroscopy. In their experiment [35], it is found that the prion fibrils can resist force up to 250 pN and that discontinuities in the force-extension curve (before the fibril is ruptured) are observed possibly due to the partial unfolding of prion proteins comprising the fibril (Figure 8). SMD simulation-based study by Lee et al. [77] provides that the mechanical behavior of polymorphic amyloid fibrils is critically dependent on their molecular structures. In particular, an amyloid fibril formed based on antiparallel stacking of β-sheets can sustain a force even up to ~1500 pN. This value of the force is larger than a force that other fibrils, which are formed based on other stacking patterns, can resist. In recent years, Solar and Buehler [29] report the tensile deformation and failure of amyloid fibrils using SMD simulations. They considered three types of amyloid fibrils based on their structural features (Figure 9): (a) a fibril formed based on stacking of β-sheets, (b) a fibril constructed based on β-helix, and (c) a fibril established based on mixed structure, that is, stacking of β-helices. The mechanical strength of an amyloid fibril can be maximized (i.e., up to 1000 MPa) when it is formed based on a mixed structure. By contrast, the strength is estimated as 200~400 MPa for a fibril formed by stacking of β-sheets, and it is measured as ~600 MPa for the fibril constructed based on β-helix.Figure 8
Optical tweezer-based stretching experiment of prion fibrils. (a) Three representative force curves for prion fibril when it is extended with a constant pulling speed. Arrows indicate discontinuities in a force-extension curve due to partial unfolding of prion proteins. (b) Fracture mechanism of amyloid fibril made ofβ-helices due to partial unfolding. (c) Fracture mechanism of amyloid fibril made of β-sheets due to partial unfolding. Figures are adopted with permission from [35].
(a)
(b)
(c)Figure 9
Three different structural types of amyloid fibrils. Amyloid fibrils can be formed based on (a) stackedβ-sheets, (b) β-helices, or (c) stacked β-helices. Figures are redrawn using VMD package for these three types of structures, whose information is provided in the protein data bank (PDB) with PDB codes of 2LNQ, 1P9H, and 2KJ3, respectively.Now, we take into account recent efforts to characterize the bending deformation of an amyloid fibril. A previous study by Smith et al. [26] reports the three-point bending-like deformation of an amyloid fibril using atomic force microscopy (AFM) experiment. It is found that the insulin amyloid fibril exhibits the elastic modulus of ~3.3 GPa, mechanical strength of ~600 MPa, and bending rigidity of ~9.1 × 10−26 N·m2, respectively. Our previous study [23] considers the bending deformation mechanisms of amyloid fibrils using SMD simulations. In our previous study, it was found that the deformation mechanism of amyloid fibrils is significantly dependent on their length scales (Figure 10(a)). In particular, when a short fibril is deformed, it undergoes shear-like deformation. By contrast, the bending deformation occurs when a long fibril is deformed. Furthermore, it was shown that Timoshenko beam model is able to capture the length-dependent stiffness of amyloid fibrils (Figure 10(b)) and that their length-dependent fracture behavior (Figure 10(c)) is attributed to the length-dependent mechanisms of hydrogen bond ruptures [23]. In addition, our recent study [78] has shown the effect of boundary conditions in the fracture behavior of amyloid fibrils. Moreover, a recent study by Kim et al. [79] provides the anisotropic bending deformation mechanisms of hIAPP amyloid fibrils using atomistic SMD simulations. Their study has shown that the fracture property (e.g., rupture force) of amyloid fibril is critically dependent on bending direction, which highlights the important role of loading mode in the fracture properties of amyloid fibrils.Figure 10
(a) Length-dependent mechanical deformation mechanisms of amyloid fibrils. The upper panel shows the shear-like deformation of a short fibril, while the lower panel provides the bending deformation of a long fibril. (b) Length-dependent elastic stiffness of amyloid fibrils (black) and spider silk crystals (red). (c) Length-dependent rupture forces of amyloid fibrils (black) and spider silk crystals (red). Figures are adopted with permission from [23].
(a)
(b)
(c)


## 4.1. Nanomechanical Characterization Based on the Vibration of Amyloid Fibrils

A recent study by Xu and coworkers [27] considers ENM simulations to measure the vibrational characteristics of Aβ fibrils and their elastic properties. They found that the low-frequency dynamic modes of these fibrils correspond to twisting, bending, or axial stretching deformation modes (Figure 4) and that the elastic moduli of amyloid fibrils are dependent on their length scales. In addition, they report that the twisting (or helical) conformation of amyloid fibrils results in their isotropic bending property when the fibril length is >150 nm. Recently, our previous study [22] reports the nanomechanical properties of human islet amyloid polypeptide (hIAPP) fibrils, which are formed based on four different types of steric zipper patterns, based on ENM simulations. We found that as the fibril length increases, the torsional and axial stretching deformation modes of the fibril become the high-frequency dynamic modes, while the bending deformation mode corresponds to the low-frequency mode independent of fibril length (Figure 5(a)). This indicates that the thermal fluctuation behavior of an amyloid fibril is mostly contributed by the bending deformation mode, that is, a low-frequency mode. In addition, we have shown that the dependence of the bending rigidity (or persistent length) of amyloid fibrils on their length scales is well fitted to Timoshenko beam model (Figure 5(b)), which suggests that the bending property of the fibrils is attributed to competition between shear and bending deformation modes. Moreover, we have also studied the nanomechanical properties of prion amyloid fibrils based on ENM [30]. It is found that the mechanical properties of prion fibrils significantly depend on their β-helical structures and that the length-dependent mechanical properties of prion fibrils provide an insight into their critical size, at which prion infectivity is maximized.Figure 4
Vibrational characteristics of Aβ amyloid fibrils computed from elastic network model. Four low-frequency vibrational modes correspond to the twisting, two bending, and axial stretching modes, respectively. Here, low-frequency vibrational modes are shown for three different types of Aβ amyloid fibrils with their length of 9.64, 19.28, and 28.92 nm, respectively. Figures are adopted with permission from [27].Figure 5
Length-dependent vibrational and nanomechanical properties of human islet amyloid polypeptide (hIAPP) fibrils computed from the elastic network model. (a) The mode index for three dominant deformation modes such as bending, torsional, and axial stretching deformation modes, respectively, is shown as a function of fibril length. As the fibril length increases, the torsional and axial deformation modes become the high-frequency vibrational modes, while the bending deformation modes are the low-frequency vibrational modes without any dependence on the fibril length. (b) The bending rigidity of hIAPP amyloid fibrils is shown as a function of their length scales based on ENM simulations. Figures are adopted with permission from [22].
(a)
(b)In recent years, we have studied the vibrational characteristics of hIAPP (20–29) fibrils, which are formed based on the eight possible conformations of the fibrils as suggested in [33, 74] (Figure 6(a)), based on atomistic molecular dynamics (MD) simulations together with continuum elastic beam model [24]. We have shown that the fibril structure becomes stable when the fibril is formed based on antiparallel stacking of β-sheets (Figure 6(b)) and that the frequencies of the fibrils for their bending deformation modes are measured in the order of 0.2 THz, which is much larger than the frequencies measured by 4D electron microscopy experiments [36]. The discrepancy between frequencies measured from MD simulations and 4D electron microscopy experiments is attributed to the fact that the fibril length considered for MD simulation is less by a few orders of magnitude than that for 4D electron microscopy experiment. In addition, we have shown that the bending rigidity of hIAPP fibril becomes optimized when the fibril is formed based on the antiparallel stacking and that the mutation of phenylalanine to leucine in hIAPP (20–29) leads to the decrease of not only the structural stability but also the bending rigidity of hIAPP (20–29) fibril. Moreover, a recent study by Chang et al. [75] reports the effect of aromatic residue (i.e., phenylalanine) on the vibrational characteristics and mechanical properties of Aβ amyloid fibrils using MD simulations coupled with continuum elastic beam model. They found that aromatic residue such as phenylalanine plays a key role in stabilizing the structure of amyloid fibrils and in optimizing their mechanical properties.Figure 6
(a) Structural models of amyloid fibrils. These structural models are theoretically provided based onβ-sheet stacking patterns such as parallel or antiparallel stacking. Figures are adopted with permission from [33]. (b) Atomistic molecular dynamics simulations provide the equilibrium structures of hIAPP amyloid fibrils based on the structural models. Figures are adopted from [24] under Creative Commons Attribution (CCA).
(a)
(b)Our recent study [34] reports the structure and vibrational (or equivalently mechanical) properties of a multistranded amyloid fibril by using atomistic MD simulations coupled with ENM. Specifically, MD simulation was used to understand the structure of a multistranded β
2-microglobulin fibril, whereas ENM was utilized to characterize their vibrational and mechanical properties (Figure 7(a)). Our previous study found that the dependence of the helical structure of β
2-microglobulin fibril on the number of filaments comprising the fibril is attributed to the nonbonded interactions between filaments, which is consistent with AFM-based experimental study of β-lactoglobulin fibril [16]. In particular, MM-PBSA calculations suggest that as the number of filaments comprising the β
2-microglobulin fibril increases, the molecular mechanics energy of the fibril is decreased and it is mostly contributed by nonbonded energy such as electrostatic and van der Waals interaction energies [34]. Moreover, our previous study suggests the persistent length of amyloid fibrils as a function of the number of filaments comprising the fibril with using ENM simulation coupled with continuum beam model. The dependence of the persistent length on the number of filaments is well fitted to a scaling law of L
P
∝
n
q
2
-
sin
2
⁡
n
q
1
/
2 for a helical fibril model [73] (Figure 7(b)).Figure 7
Nanomechanical properties ofβ
2-microglobulin fibrils made of one to five filaments, respectively. (a) The length-dependent effective bending rigidity of β
2-microglobulin fibrils composed of one to five filaments, respectively. (b) The intrinsic bending rigidity of β
2-microglobulin fibrils made of two to five filaments, respectively, is shown as a function of the number of filaments comprising the fibrils. The dots indicate the results of ENM simulations, while solid line presents the theoretical prediction from continuum helical fibril model. Figures are adopted with permission from [34].
(a)
(b)


## 4.2. Mechanical Deformation Mechanisms of Amyloid Fibrils

Mechanical characterization of amyloid fibrils based on measuring their vibrational characteristics is insufficient to gain insight into the mechanical behaviors and properties of amyloid fibrils, as the vibrational properties of the fibrils are correlated with only their elastic moduli [76]. In particular, the vibrational characteristics of amyloid fibrils cannot provide the quantitative insight into the fracture behaviors and properties of amyloid fibrils. Here, we take a look at the mechanical deformation mechanisms and properties of amyloid fibrils based on two types of deformation modes such as (i) axial deformation and (ii) bending-like deformation.First, we consider recent attempts to characterize the axial deformation behavior of amyloid fibrils. A recent study by Dong et al. [35] reports the axial extension of prion fibrils using optical tweezer force spectroscopy. In their experiment [35], it is found that the prion fibrils can resist force up to 250 pN and that discontinuities in the force-extension curve (before the fibril is ruptured) are observed possibly due to the partial unfolding of prion proteins comprising the fibril (Figure 8). SMD simulation-based study by Lee et al. [77] provides that the mechanical behavior of polymorphic amyloid fibrils is critically dependent on their molecular structures. In particular, an amyloid fibril formed based on antiparallel stacking of β-sheets can sustain a force even up to ~1500 pN. This value of the force is larger than a force that other fibrils, which are formed based on other stacking patterns, can resist. In recent years, Solar and Buehler [29] report the tensile deformation and failure of amyloid fibrils using SMD simulations. They considered three types of amyloid fibrils based on their structural features (Figure 9): (a) a fibril formed based on stacking of β-sheets, (b) a fibril constructed based on β-helix, and (c) a fibril established based on mixed structure, that is, stacking of β-helices. The mechanical strength of an amyloid fibril can be maximized (i.e., up to 1000 MPa) when it is formed based on a mixed structure. By contrast, the strength is estimated as 200~400 MPa for a fibril formed by stacking of β-sheets, and it is measured as ~600 MPa for the fibril constructed based on β-helix.Figure 8
Optical tweezer-based stretching experiment of prion fibrils. (a) Three representative force curves for prion fibril when it is extended with a constant pulling speed. Arrows indicate discontinuities in a force-extension curve due to partial unfolding of prion proteins. (b) Fracture mechanism of amyloid fibril made ofβ-helices due to partial unfolding. (c) Fracture mechanism of amyloid fibril made of β-sheets due to partial unfolding. Figures are adopted with permission from [35].
(a)
(b)
(c)Figure 9
Three different structural types of amyloid fibrils. Amyloid fibrils can be formed based on (a) stackedβ-sheets, (b) β-helices, or (c) stacked β-helices. Figures are redrawn using VMD package for these three types of structures, whose information is provided in the protein data bank (PDB) with PDB codes of 2LNQ, 1P9H, and 2KJ3, respectively.Now, we take into account recent efforts to characterize the bending deformation of an amyloid fibril. A previous study by Smith et al. [26] reports the three-point bending-like deformation of an amyloid fibril using atomic force microscopy (AFM) experiment. It is found that the insulin amyloid fibril exhibits the elastic modulus of ~3.3 GPa, mechanical strength of ~600 MPa, and bending rigidity of ~9.1 × 10−26 N·m2, respectively. Our previous study [23] considers the bending deformation mechanisms of amyloid fibrils using SMD simulations. In our previous study, it was found that the deformation mechanism of amyloid fibrils is significantly dependent on their length scales (Figure 10(a)). In particular, when a short fibril is deformed, it undergoes shear-like deformation. By contrast, the bending deformation occurs when a long fibril is deformed. Furthermore, it was shown that Timoshenko beam model is able to capture the length-dependent stiffness of amyloid fibrils (Figure 10(b)) and that their length-dependent fracture behavior (Figure 10(c)) is attributed to the length-dependent mechanisms of hydrogen bond ruptures [23]. In addition, our recent study [78] has shown the effect of boundary conditions in the fracture behavior of amyloid fibrils. Moreover, a recent study by Kim et al. [79] provides the anisotropic bending deformation mechanisms of hIAPP amyloid fibrils using atomistic SMD simulations. Their study has shown that the fracture property (e.g., rupture force) of amyloid fibril is critically dependent on bending direction, which highlights the important role of loading mode in the fracture properties of amyloid fibrils.Figure 10
(a) Length-dependent mechanical deformation mechanisms of amyloid fibrils. The upper panel shows the shear-like deformation of a short fibril, while the lower panel provides the bending deformation of a long fibril. (b) Length-dependent elastic stiffness of amyloid fibrils (black) and spider silk crystals (red). (c) Length-dependent rupture forces of amyloid fibrils (black) and spider silk crystals (red). Figures are adopted with permission from [23].
(a)
(b)
(c)


## 5. Discussion

In this review article, we address recent attempts to characterize the nanomechanical properties of amyloid fibrils measured from computational simulations and/or AFM experiments together with theoretical models. The nanomechanical properties of amyloid fibrils are summarized in Table1, which shows that the elastic modulus of amyloid fibrils is evaluated in the order of 1 to 10 GPa and that their mechanical strength is measured in the order of 1 GPa. It should be noted that though both amyloid fibril and spider silk crystal are made of stacked β-sheets, the mechanical strength of amyloid fibril is less than that of a spider silk crystal, which is attributed to the different orientation of stacked β-sheets with respect to the fibril axis [31].Table 1
Nanomechanical properties of amyloid fibrils measured from simulations and experiments.
Material
Measurement method
Length (nm)
Bending rigidity (×10−26 N⋅m2)
Young’s modulus (GPa)
Shear modulus (GPa)
Strength (GPa)
Ref.
h
I
A
P
P
20
–
29 fibril
Steered molecular dynamics (simulation)
3.41–17.5
7.73–37.7
5.97–6.71
4–8
[23]
h
I
A
P
P
20
–
29 fibril
Elastic network model (simulation)
10–300
~8
12–14
1.1
[22]
h
I
A
P
P
20
–
29 fibril
Molecular dynamics (simulation)
10
0.01–0.04
0.4–0.6
[24]
A
β
1
–
40 fibril
Cryoelectron microscopy (experiment)
500–1000
~13
0.0127
[17]
A
β
1
–
40 fibril
Elastic network model (simulation)
~30
21–63
4.3–5.6
[27]
β-lactoglobulin fibril
AFM imaging experiment
500–15,000
0.4–1.6
~4
[16]
β-lactoglobulin fibril
AFM indentation experiment (peak force QNM)
500–15,000
3.3
[19]
Mouse prion fibril
AFM experiments (AM-FM imaging)
>1000
0.5–1.36
[28]
α-synuclein fibril
AFM indentation (peak force QNM)
>1000
1.2
±
0.2
[20]
Insulin fibril
AFM bending experiment
>~1500
~9.1
~0.28
[26]
Insulin fibril
AFM imaging experiment
>~2000
~17
~0.13
[26]
HET-s prion fibril
Steered molecular dynamics (simulation)
5.38
9.8
0.917
[29]
HET-s prion fibril
Elastic network model (simulation)
8.93
0.115
1.5
[30]
Spider silk crystal
Steered molecular dynamics (simulation)
2–7
~2.8
4.6
[12]
Spider silk crystal
Steered molecular dynamics (simulation)
30–70
[31]Here, we note that most of recent works reviewed in this work do not consider the effect of physiological conditions in the nanomechanical properties of amyloid fibrils. It has recently been found that physiological conditions play a crucial role in the formation and structure of amyloid proteins. For instance, a recent study by Lee et al. [80] reports a critical role that the physiological condition such as the pH of a solvent plays in the morphology of amyloid fibrils. In addition, Mizuno and coworkers [81] found the dependence of HET-s prion amyloid fibril structure on the pH of a solvent. Moreover, it has been debated whether metal ion promotes the formation of amyloid oligomers or fibrils, as previous studies [82–84] report that the high concentration of metal ions was found for patients suffering from neurodegenerative diseases. In addition, recent studies [85, 86] have shown the important role of metal ion in the formation and structure of amyloid fibrils. Despite these recent studies showing the role of physiological condition in the formation and structure of amyloid proteins, how physiological condition may make an impact on the nanomechanical properties of amyloid fibrils has remained elusive. Future studies may be directed towards understanding how physiological conditions affect the nanomechanical properties of amyloid fibrils.In conclusion, this review article summarizes the excellent nanomechanical properties of amyloid fibrils, which are measured with using experiments (based on AFM) and computational simulations (based on atomistic simulations or ENM). The nanomechanical characterization of amyloid fibrils may allow for further insight into not only the mechanics-driven biological functions of the fibrils but also the design principles showing how the properties of protein materials can be determined or controlled.



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*Source: 5873695-2016-06-26.xml*