ISSN: 0970-938X (Print) | 0976-1683 (Electronic)

An International Journal of Medical Sciences

Research Article - Biomedical Research (2017) Volume 28, Issue 19

**Xiao Chen ^{1,2*}, Qianyi Ji^{1} and Chang Xu^{1}**

^{1}School of Electronic and Information Engineering, Nanjing University of Information Science and Technology, Nanjing, PR China

^{2}Jiangsu Key Laboratory of Meteorological observation and Information Processing, Nanjing University of Information Science and Technology, Nanjing, PR China

- *Corresponding Author:
- Xiao Chen

School of Electronic and Information Engineering

Nanjing University of Information Science and Technology, PR China

**Accepted on** December 21, 2017

It is difficult to detect muscle tension *in vivo*. *In vitro* experiments, the young's modulus of human muscle changes with the tension and the shear wave speed is affected by young’s modulus. The tension can be qualified by using the shear wave elastography method. In this paper, the hyperelasticity model for muscles was established. The shear wave speeds in the muscle tissues under tension were studied by applying different statistic loads in the axial direction, and the effect of loads on the shear wave speeds was obtained. The results show that the shear wave speeds increases from 6.1 m/s to 13.1 m/s as the load increases from 0 to 50 kpa, and the speed is linearly related to the load. The shear wave elastography method could be used as a potential non-invasive method to measure the tension in tissues.

Hyperelasticity, Shear wave elastography, Shear wave speed, Muscle.

Shear wave elastography (SWE) is a promising method of medical imaging. It is a new method of obtaining quantitative tissue elasticity data and is a developing variation of ultrasound imaging. As a supplement to traditional ultrasonic imaging methods [1], shear wave elastography is based on acoustic radiation force. Compared with other elastic imaging methods, SWE is quantifiable, repeatable and noninvasive. It is found that the hardness, i.e., the Young’s modulus, of diseased tissues is different from the normal tissue. And the shear wave speed is greatly affected by Young's modulus [2]. Therefore, tissue lesions can be diagnosed by measuring the shear wave speed [2-4].

For organs, the load can usually be ignored. But the muscle is
always in a state of stress in order to maintain physiological
activities. Clinical and *in vitro* experiments show that the
relative position of thick and thin filaments is different when
the muscle is in the state of relaxation and contraction [5-7].
What’s more, detection data also show that the Young's
modulus varies greatly under different load [5]. However,
facing the difficulties *in vivo* detection, the specific distribution
of force in muscle is not clear [6,7], and the theoretical model
for muscle under load is imperfect. The emergence of shear
wave elastic imaging technology can control the detection
range flexibly by focus position. According to the relationship
between the load and shear wave speed, the distribution of
force in muscles can be obtained by measuring the shear wave
speed. SWE has become a promising way of studying the
distribution of force in muscles.

This article will discuss the establishment of a reasonable muscle model. Through the variation of shear wave speed caused by different loads, this paper provides the theoretical basis for studying the force distribution in vivo by using shear wave elastography.

The principle of traditional elastic imaging is squeeze version of the device or addition low-frequency vibration, generating displacement. The Young's Modulus of the tissue can be obtained by comparing the strain before and after the deformation assuming that the muscle is linear elastic. σ=Eε, where σ is the stress, E is Young's modulus, and ε is strain [8]. But these methods need to be exposed to the surface of the tissue. They are not applicable to non-surface organs. With the development of technology, the introduction of acoustic radiation force enables the detection by controlling the focusing position, generating displacement and radiation shear wave [9] near the focus position. For linear elastic materials, the shear wave speed in the material can be expressed as

(1)

Where c is linear elastic shear wave speed, ρ is the tissue density, v is Poisson's ratio, and μ is shear modulus.

It is shown that the linear elastic material model cannot meet the requirement of clinical trials, and there are obvious limitations. Therefore, a nonlinear model, such as viscoelasticity and hyperelasticity, is proposed for the muscle tissue.

The Ogden’s strain energy function model, one of the hyperelastic models, is better than other hyperelastic models, which is more suitable for fitting the stress hardening characteristics of nonlinear materials. The Ogden strain energy function is

(2)

Where W is a strain energy, and J is the compression ratio. is the Partial elongation ratio

λp is the main elongation of three directions. For incompressible materials, J can be defined as

As shown in **Table 1**, the shear wave speeds for the uniaxial
tensile test data of isolated fox eye muscles [10] are compared
with those calculated by using the Ogden model. To
characterize the parameters in the Ogden model, the particle
swarm optimization algorithm [11-13] was used. The Ogden
strain energy equation of the N order can be written as

Elongation | Experimental data of stress | Simulation data of stress |
---|---|---|

1.06 | 1.20 | 1.19 |

1.15 | 8.31 | 8.56 |

1.24 | 18.09 | 23.01 |

1.33 | 31.18 | 35.15 |

1.42 | 47.71 | 54.77 |

**Table 1.** Uniaxial stretching experimental data and the Ogden model
simulation data.

(4)

The Ogden model includes two parameters, the shear modulus
μ and the stress hardening coefficient α, which respond to the
properties of the muscle tissue under the external stress. At the
same elongation ratio, when the strain is small, the
experimental data in vitro are close to the simulation results,
and the experimental results are slightly lower than the
simulation results as the strain increase. **Table 2** shows the
shear wave speeds under different loads. The result of the
fitting of the applied stress and the corresponding speed is

Load (Kpa) | Speed (m/s) |
---|---|

0 | 6.1233 |

1 | 6.3892 |

10 | 8.2336 |

20 | 9.6332 |

30 | 10.9157 |

40 | 11.9934 |

50 | 13.1172 |

**Table 2.** Shear wave speeds under different loads.

y=0.1391x+6.487 → (5)

Beside the shape of the muscle model and the material parameters are set, the load and the constraint conditions of the model should be determined as well. The load is applied with two steps. The first step is the exertion of the external tension, the axial load is applied on the right section, and the load is gradually increased from 0 to 50 Kpa. The second step is to apply a sinusoidal excitation on a certain node in the middle of the model to generate the shear wave.

As the distance between the two nodes is small, the speed between the two adjacent nodes is simplified to a uniform motion when the speed of the shear wave is calculated. The farther the distance from the excitation node, the later the vibration appears, and the amplitude of the vibration decreases with the increase of distance. With the increase of the applied stress, the earlier the time of the wave peak of the displacement envelope of the same node shows that the shear wave speed increases with the increase of stress.

The time of flight (TOF) algorithm is used to calculate the shear wave speed. While there is no external load, the shear wave speed is about 6.1 m/s, and the speed increases with the increase of load. In the case of 50 kPa load, the speed reaches 13.1 m/s, and the specific speed change is shown in Table 2. There is a certain correlation between the tensile load and the shear wave speed, that is, the shear wave speed in the muscle tissue increases with the increase of the applied stress. The fitting result in Eq. (5) implies that the relationship between the applied load and the shear wave speed is basically linear.

In this paper, the hyperelasticity model is established and the
linear relationship between the shear wave speed and the load
is obtained by analyzing the shear wave spped in the muscle
tissue. The results also show that shear wave elastography is
feasible for detecting muscle force distribution in different
states, which provides a basis for determining the distribution
of force *in vivo*.

The cross sectional area, volume and hardness of the muscle tissue are affected by the individual conditions, such as sex, age, etc. The measured images maybe have noises and need denoise [14,15]. In addition, the model in this paper only considers the hyperelasticity of tissue. In fact, the muscle tissue is obviously viscoelastic. In the next stage, it is necessary to further optimize the muscle model and establish a more reasonable model.

This work was supported in part by project grants from the six talent peaks project in Jiangsu Province (DZXX-006), in part by 333 high level personnel training project Jiangsu Province of China, in part by the Natural Science Foundation of Jiangsu Province of China (BK20161536), and in part by the Priority Academic Program Development of Jiangsu Higher Education Institutions.

- Sandrin L, Fourquet B, Hasquenoph JM. Transient elastography: a new noninvasive method for assessment of hepatic fibrosis. Ultrasound Med Biol 2003; 29: 1705-1713.
- Thiele M, Detlefsen S, Møller LS. Transient and 2-dimensional shear-wave elastography provide comparable assessment of alcoholic liver fibrosis and cirrhosis. Gastroenterology 2016; 150: 123-133.
- Song J, Zhou Q, Jiang J. Real-time quantitative shear-wave elastography Young's modulus in the detection of systematic Hashimoto's Thyroiditis. J Chinese Pract Diag Ther 2017; 31: 65-67.
- Lam ACL, Pang SWA, Ahuja AT. The influence of precompression on elasticity of thyroid nodules estimated by ultrasound shear wave elastography. Euro Radiol 2016; 26: 2845-2852.
- Wen C, Fan C, Xi J. Quantitative measurement of the elastic modulus of the biceps brachii during muscle relaxation and tension by shear-wave elasto-sonography. China J Med 2011; 8: 61-63.
- Zivkovic MZ, Djuric S, Cuk I. A simple method for assessment of muscle force, velocity, and power producing capacities from functional movement tasks. J Sports Sci 2017; 35: 1287-1293.
- Bogey RA, Barnes LA. An EMG-to-force processing approach for estimating in vivo hip muscle forces in normal human walking. IEEE Transact Neural Syst Rehab Eng 2016.
- Ophir J, Cespedes I, Ponnekanti H. Elastography: a quantitative method for imaging the elasticity of biological tissues. Ultrasonic Imaging 1991; 13: 111-134.
- Nightingale K. Acoustic radiation force impulse (ARFI) imaging: a review. Curr Med Imag Rev 2011; 7: 328-339.
- Guo H, Gao Z, Chen W. Hyperelastic analysis for the passive behavior of fox extraocular muscles in vitro. J Med Biomech 2017; 32: 27-31.
- Chen X, Zou S. Improved wi-fi indoor positioning based on particle swarm optimization. IEEE Sensors J 2017; 17: 7143-7148.
- Chen X, Zhang B. 3D DV-hop localisation scheme based on particle swarm optimisation in wireless sensor networks. Int J Sensor Networks 2014; 16: 100-105.
- Chen X, Zhang B. Improved DV-hop node localization algorithm in wireless sensor networks. Int J Distribut Sensor Networks 2012; 2012: 213980.
- Chen X, Hu C. Medical image encryption based on multiple chaotic mapping and wavelet transform. Biomed Res India 2017; 28: 8576-8579.
- Chen X, Hu C. Adaptive medical image encryption algorithm based on multiple chaotic mapping. Saudi J Biol Sci 2017.