Abstract
Establishment of three-dimensional finite-element model of the whole auditory system includes external ear, middle ear, and inner ear. The sound-solid-liquid coupling frequency response analysis of the model was carried out. The correctness of the FE model was verified by comparing the vibration modes of tympanic membrane and stapes footplate with the experimental data. According to calculation results of the model, we make use of the least squares method to fit out the distribution of sound pressure of external auditory canal and obtain the sound pressure function on the tympanic membrane which varies with frequency. Using the sound pressure function, the pressure distribution on the tympanic membrane can be directly derived from the sound pressure at the external auditory canal opening. The sound pressure function can make the boundary conditions of the middle ear structure more accurate in the mechanical research and improve the previous boundary treatment which only applied uniform pressure acting to the tympanic membrane.
1. Introduction
With the development of interdiscipline, the research that explores issues of life sciences with principles of mechanics has become a new frontier. The study of ear biological mechanics has a relatively brief history which trace back to the end of last century and the beginning of this century. Scholars mainly adopt two methods to study ear problems with mechanics: the first one is theoretical research methods, such as the use of analytical solution to eardrum vibration problem deduced by mechanical theory and analytical method of artificial ossicle detection [1, 2]; the other is numerical modeling methods, the most popular of which is finite element method. For example, Voss and Peake [3] studied the relationship between sound transmission and perforation using the finite element method. Bance et al. [4] studied the impact of size of incus prosthesis head on Tympanic membrane vibration. Dai et al. [5] studied the combined effects of fluid and air in middle ear cavity. Vard and Kelly [6] studied how the design of ventilation tubes influence on vibration. Tange and Grolman [7] studied the impact of connector shape of stapes replacement prosthesis on hearing conduction. Tenney et al. [8] studied the restoration of hearing of stapes prosthesis in the short term and the impact of angle of implantation on hearing. Gan et al. [9–11] simulated the tympanic membrane perforation, inner ear impedance, and other middle ear diseases using the finite element method. Wenjuan Yao and coworkers used finite element methods to analyse the material of the stapes replacement prosthesis and the connection between prosthesis and incus long legs [12–14]. The above studies have promoted the development of ear-biomechanics.
However, these preliminary studies all simplified the boundary conditions, in which the sound incentive on the tympanic membrane surface was defined as uniformly distributed loads. The external load on the tympanic membrane, however, is not really uniform, because sound waves have reached external auditory canal before they reach tympanic membrane, and gas-solid coupling occurs in external auditory canal then reach tympanic membrane, and fluid-solid coupling will happen between tympanic membrane and air in the external auditory canal. After sound-solid-liquid three-phase fluid-solid coupling occurs, the pressure distribution on the tympanic membrane is shown in Figure 1.
2. Model and Method
2.1. Data Sources and Establishment of Middle Ear Model
Based on the CT scan images from Zhongshan Hospital of Fudan University on the normal human middle ear (GE lights peed VCT 64 Slice spiral CT machine, Scanning parameters: collimation 0.625 mm, tube rotation time 0.4 s, reconstruction thickness 0.625 mm, interval 0.5 ~ 0.625 mm.) by further processing the image, using self-compiled program to Numerical Value the CT scans and import it into FE software Patran to reconstruct three-dimensional finite element model of ear structure, then divide into grid, we can define the boundary conditions and the material parameters, as shown in Figures 2 and 3. The model adopts interface element to simulate interosseous membrane among ossicles in order that transfer behavior among ossicles (malleus, incus, and stapes) is simulated perfectly.
This paper combined the numerical analysis and theoretical analysis to study the load distribution on the eardrum deeply.
External auditory canal gas unit is divided into 7200 eight-node hexahedron (Hex8) units. The number of nodes is 7460. Tympanic membrane is divided into 330 four-node quadrilateral (Quad4) and 30 triangle (Tri3) surface units, the number of nodes is 373. Ossicular chain is divided into 21,438 four-node tetrahedral elements (Tet4), nodes 6065, Figures 2 and 3.
Cochlea mesh: the fluid domain near stapes within vestibular is divided into Tet4 units, and other fluid domain are divided into Hex8 units, The fluid unit attributes are defined as FLUID units, the number of units produced is 4391 in total, 6817 nodes; oval window is divided into Tria3 surface units, oval window unit is defined as two-dimensional membrane structure, and the number of units is 56 in total, 37 nodes; and round window is divided into Quad4 surface units, and round window membrane unit is defined as two-dimensional structure (membrane) total 16 units, 25 nodes. Mesh is shown in Figure 3.
2.2. Governing Equations
The structural dynamics equation of the acoustic structural coupled system of air in external canal and tympanic membrane, stapes footplate, and perilymphatic fluid in inner ear where is structural mass matrix; is coupling interface mass matrix; is air mass matrix; is structural damping matrix; ] is air damping matrix; is fluid stiffness matrix; is the displacement vector; is the sound pressure matrix.
2.3. Interface Fundamental Equations
The assumption that elements are in no thickness where is tangential stiffness; is normal stiffness; , , and are two coordinates directions and element normal direction in the actual contact surface; , , and are relative displacements of upper wall and bottom wall of contact face in tangential and normal direction where Element stiffness matrix is
2.4. Material Properties
Material properties and acoustic properties of various parts of numerical models in this paper refer to experimental data in [9, 11, 15], the relevant parameter values of them are shown in Tables 1 and 2, and Poisson’s ratio was taken as 0.3. Hearing system damping coefficient was taken as 0.5 by spreadsheet simulation.
2.5. Boundary Conditions
Because of the sensitivity of displacement of microstructure to the dynamical response of ear structure, the connection between soft tissue and temporal bone was regarded as fixed constraint, which is to say its displacement in all three orthogonal directions is zero. The defined boundary condition is listed below.(1)90 dB SPL (0.632 Pa, from 200 Hz to 8000 Hz) was set on the opening surface of external auditory canal.(2)The displacement of connection between soft tissues and temporal bone was defined to be zero in three orthogonal directions.(3)The displacement of outer edge of tympanic membrane annular ligament was defined to be zero in three orthogonal directions.(4)The displacement of outer edge of stapes annular ligament was defined to be zero in three orthogonal directions.(5)The displacement of outer edge of oval window and round window was defined to be zero in three orthogonal directions.(6)The displacement of external auditory canal wall and the inner ear bony labyrinth wall was defined to be zero in three orthogonal directions.(7)Eardrum and Oval window are fluid-structure coupling interface.
3. Results
3.1. The Reliability of Numerical Simulations
Figures 4 and 5 shows the FE model-derived frequency response curve of the TM displacement and stapes footplate displacement in comparison with the corresponding curves obtained from 10 temporal bones at the same input sound pressure level of 90 dB applied on the TM in the ear canal by Gan et al. [15]. These figures show that the FE model predicted TM and stapes footplate curves fall into the range of the 10 temporal bone experimental curves and the tendency is similar across the frequency range of 200–8000 Hz.
Aibara et al. [16] obtained the stapes velocity transfer function (SVTF) curve from 11 fresh temporal bones with Doppler Vibration Instrument, characterizing the middle ear sound transfer function. Stapes velocity transfer function is defined as where is stapes footplate speed of stapes and is pressure near the eardrum. Figure 6 shows the SVTF curve calculated by the FE model comparisons with the experimental results.
The displacement of soft tissue in the boundary condition and the elastic modulus of Table 1 are most sensitive and important for the results in Figures 4–6. But the displacement of tympanic membrane umbo and stapes footplate was derived from inversion.
The simulation results show that SVTF reaches the average maximum when the frequency is 1 KHz, gets 0.33 mm s−1/Pa, has a slope of about 7 dB/octave in the range of 100–1000 Hz frequency, and has a slope of about −7 dB/octave above 1000 HZ. Figure 6 shows the SVTF calculation results by finite element model and Aibara et al. measured SVTF through the 11 cases of fresh temporal bone. The comparisons of results show that in the paper, the frequency response curves obtained by computational results and experiments are in very good agreement not only in tendency but also in amplitude, therefore, further proving that the model is correct and, thus the present model is a good starting point to predict the dynamical properties of ear structure.
3.2. Distribution of External Ear Canal Sound Pressure
This paper makes use of finite element model to impose sound incentive on external auditory canal, and results are compared with those of sound pressure imposed on tympanic membrane in the vicinity, the comparison shows that when the range of frequency is between 3 and 4 kHz, the effect that impose sound incentive on external auditory canal is higher than that of Eardrum with an increase of 10 dB. The increase reaches the maximum when the frequency is 3700 Hz; see Figure 7. This result can be explained by the physical principle that inflatable pipe closed at one end can generate resonant interaction with the acoustic whose wavelength is 4 times tube length. The external auditory canal belongs to this type tube (one end opening, the other end terminated at the tympanic membrane), and its length is about 2.5–3.5 cm; therefore, external auditory canal plays a role of amplification in signals among the range of 3000–4000 Hz frequency.
Figure 8 shows the distribution of acoustic pressure in external auditory canal at different frequency; the distance of 0 is external auditory canal mouth, and the distance of 30 mm is convex part of eardrum. As can be seen from the figure, in the low frequency (500 Hz, 1000 Hz), the sound pressure in the external auditory canal at different location has no obvious difference, and the sound pressure gain is quite small. Under the frequency of 2000 Hz, the increase of sound pressure at different location also has no obvious difference, but sound pressure has expanded, the biggest sound pressure gain is about 3 dB. When the sound frequency is 4000 Hz, the sound pressure gain is big, and the effect of increment varies with location: with the location being closer to the tympanic membrane, the larger of increment of sound pressure is (about 10 dB), while the gain is quite small (0.5 dB) near external auditory canal mouth. At the higher frequency, there was a decrease in the sound pressure at the central location of external auditory canal. When the frequency is about 8000 Hz, there is the largest decline at the location 17.5 mm away from the external auditory canal mouth (−10 dB), and the sound pressure still has small increase at the location near external auditory canal and tympanic membrane; the sound pressure gain is in the range of 2 dB.
Figure 9 shows the acoustic pressure at different location of external auditory canal from 200 Hz to 8000 Hz. As can be seen from the figure, in the rang of low frequency (200–1000 Hz), the variation of sound pressure of external auditory canal at different location is quite small, within 1.5 dB. Among the range of intermediate frequency (1000 Hz–4000 Hz), sound pressure at different position all have increased; the closer the location to the tympanic membrane, the larger the sound pressure gain, and the increasing values vary with the increment of the frequency. The increase reaches the maximum when the frequency is 4000 Hz (In this paper, only mapping the frequency points of integer multiple of 1000 in the high frequency, the actual maximum appears in the about 3700 Hz.) In the higher-frequency range (4000 Hz–8000 Hz), gain variations of sound pressure of external auditory canal at different positions are not uniform. The basic trend is declining firstly then rise slightly. But change of the magnitude is different, the reductions are all quite obvious at the location 5 mm–25 mm away from the external auditory canal, the increments of sound pressure are negative above the frequency of 4000 Hz. the increments at the location 5 mm and 10 mm are positive when the frequency is 4000 Hz. The declines of sound pressure near tympanic membrane are quite obvious, but the sound pressure still maintain above 90 dB (input sound incentive on the external acoustic foramen), the increments of sound pressure are positive.
Figure 10 shows the changing of acoustic pressure at six different locations near tympanic membrane surface varying with frequency. The figure shows that in the frequency range of 200 Hz–4500 Hz, the distributions of different points of sound pressure are basically the same, but between the range of 4500 Hz–8000 Hz, the difference in sound pressure appears near tympanic membrane. This phenomenon can prove that when sound pressure reaches eardrum, the tympanic membrane is equivalently incited by uniformly distributed pressure in the low-frequency range. However, when sound pressure above 4500 Hz frequency, different points of tympanic membrane are incited by different sound pressure, and the pressure that influences the surface of tympanic membrane is no longer uniform sound pressure.
According to calculation results, piecewise function of sound pressure which varies with frequency in different points of the surface of tympanic membrane was fitted using least-square method where is sound pressure (MPa), is frequency (Hz), and is distance between different points and the umbo (mm).
4. Conclusion
The paper achieves the following conclusions by numerical simulation and theoretical analysis. (1)The finite element model containing external auditory canal, middle ear, and inner ear hearing system was established, made use of this model to do the frequency response analysis containing gas external auditory canal, middle ear structure, and inner ear fluid coupling, and get the response curves of tympanic membrane and stapes footplate. In the paper, the curves obtained by calculation results using this model and experiment data of was in very good agreement, and prove that the model is correct. (2)In consideration of the sound transmission role of external auditory canal, middle ear structures occurs resonance at the frequency 3000 Hz–4000 Hz, and close to the conclusions of medical science [17], further proving that the correctness of the model. (3)The calculation results showed that in the low frequency (<4500 Hz), the sound pressure that transmits uniform sound pressure of external acoustic foramen into the surface of tympanic membrane by external auditory canal mainly varies with frequency, the effects of changes in distance can be ignored, in the high frequency (>4500), the situation is different; the sound pressure of the surface of tympanic membrane does not only vary with frequency, but also relates to distance. Thus, according to simulation results, functional formula of sound pressure of the surface of tympanic membrane was fitted using least-square (3.2).(4)Previous studies usually defined a constant sound pressure in simplified model of tympanic membrane, taking no consideration of the influence of external auditory canal. Since (3.2) provide a new distribution function of sound pressure, it can be used to calculate the sound pressure at any point and further provide more accurate boundary conditions for the middle ear structure. It could provide additional information and insight for researchers to better understand the mechanism of sound transmission in human ear.
Acknowledgments
The authors gratefully acknowledge national natural science foundation of China (11072143) and foundation research key project of shanghai science committee (08jc1404700).