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34
UNCONFINED COMPRESSION OF THE PERIODONTAL LIGAMENT,
INTERVERTEBRAL DISC, ARTICULAR CARTILAGE AND OTHER PERMEABLE DEFORMABLE TISSUES: A POROELASTIC ANALYSIS
M.Y. Nyashin
Department of Theoretical Mechanics, Perm State Technical University, 29a, Komsomolsky Prospect, 614600, Perm, Russia
Abstract: In this paper, behavior of the porous tissues such as the periodontal ligament, intervertebral disc, articular cartilage was investigated. They are generally subjected to compressive loads, which are transmitted through the surrounding hard tissues (tooth, bones). To a first approximation, such porous tissues saturated by free fluid may be viewed as poroelastic. The porous medium was considered to be sandwiched between two approached parallel rigid impervious plates. The approximate analytical solution of the problem on stationary flow of the interstitial fluid completely saturating the incompressible porous medium was found. The fields of displacements, strains, stresses of the porous medium and fields of fluid pressure and fluid flow were obtained. The determined solution has qualitatively described the processes proceeding in such porous tissues, in particular, of interstitial fluid movement.
Key words: permeable deformable tissues, poroelastic analysis, unconfined compression, periodontal ligament, periodontal fluid, intervertebral disc, articular cartilage, interstitial fluid
Introduction
In this paper, the behavior of the interstitial fluid that saturates and flows through a deformable porous matrix is considered for the case of unconfined compression of such a porous medium.
The periodontal ligament is a dense connective tissue that surrounds the root of the tooth and attaches it to the alveolar bone. The periodontal ligament behavior is very diverse and depends heavily on the kind of mechanical load acting on the tooth. It was experimentally shown that under a short-term load the periodontal ligament may be considered as a porous material saturated by free fluid with a permeability coefficient k of the order of 10"8 m2/(Pa-sec) [18, 20]. Such a load may lead to the different tooth traumas, their kind being mainly determined by the degree of periodontal ligament fluid redistribution [19]. Under a long-term load the periodontal ligament may be viewed as an elastic material [5, 9, 12, 17, 21, 22].
This paper presents the study of such a case of a short-term load, which leads to the translational movement of the tooth. The human periodontal ligament width ranges from 0.1 to 0.3 mm [16, 26]. These values are far less than the tooth root length (the order of 15 mm) [28]. Because of this, the deformation of the porous medium located within a narrow long gap between two approached parallel rigid impervious plates is investigated. The purpose is to determine stresses, strains and displacements of the periodontal ligament solid matrix as well as fluid pressure and fluid velocities.
It should be emphasized that other porous tissues (intervertebral disc, articular cartilage) were viewed as deformable porous solid materials that are saturated by mobile fluid [1, 4, 6-8, 13-15, 23, 24] and the unconfined compression was theoretically investigated in a
number of papers [1, 10, 11]. The solution presented in this paper is analytical and describes some processes occurring in the periodontal ligament as well as in articular cartilage, intervertebral disc and other permeable deformable solids.
The problem formulation
It is supposed that the plate size in z-direction is infinite and thus all investigated parameters are independent on z. Then in the stationary process the equations describing the poroelastic behavior of completely saturated porous medium are [2, 3, 20]
1 dp
G dx
1 dp
-—— +
d 2 Ux
dx 2
d2 u
+
d 2 Ux
dy 2 d2 u
+
1 de
1 - 2 v dx
1 de
= 0,
+
+
G y x2 y2 1 - 2v y
= 0,
d2p d2p + —f = 0,
x 2 y
2
(1) (2) (3)
where ux (x,y) is the x-component of the displacement of the porous medium; uy (x,y) is the y-
component of the displacement of the porous medium; p(xy) is the fluid pressure; G and v are the shear modulus and Poisson ratio for the completely saturated porous medium, respectively;
ux u
e=
+
is the volume strain of the porous medium.
(4)
dx dy
In this paper, the unconfined compression of two parallel rigid impervious plates is investigated, the points of plates satisfying the conditions -l<x<l; y=±h (Fig. 1). The porous medium is assumed to be located between these plates compressed so that the y-displacement
of each plate equals the preassigned magnitude (M U ). Thus, the required solutions of equations (1)-(3) are considered to meet the following boundary conditions
Ux h)=0 Ux C^ -h)=0
uy (x, h)= - U uy (x, -h)= U
p(±l, y)=o i U
B T
at -l<x<l; at -l<x<l; at -l<x<l; at -l<x<l;
at -h<y<h.
y
(5)
(6)
U
-l
h
C
U
-h
A
O
x
U
D
Fig. 1. Unconfined compression of the porous medium (periodontal ligament, articular cartilage,
intervertebral disc and others).
l
It should be noted that the conditions (5) mean the adhesion of solid matrix to the plates and the condition (6) does that the free boundaries (x=±I) do not inhibit the horizontal fluid exudation.
Determination of the porous medium displacements and fluid pressure
To solve this problem the method in which an approximate analytical solution is built with the help of polynomials is used [27]. One can readily see that the following second-degree polynomial satisfies equation (3)
P(x,y) = A{y2 "x2) + A2, (7)
where A1 and A2 are some constants. In this problem, the first-degree terms cannot enter into the polynomial equation because the pressure is independent of the signs of both x and y. Further, the equations for porous medium displacements will be sought in the form
ux (xy^iyX (8)
Uy (x^)=a(y). (9)
Then using (8) and (9) expression (4) may be written as
e=b(y)+a'(y). (10)
Substituting (7), (8) and (10) into (1) yields
--1 {- 4x) + b"{y)x = 0. (11)
Hence
4
b"{y) = - G (12)
and
b{y) = - G y + c1y + C2, (13)
where C1 and C2 are some constants.
Then the x-component of the porous medium displacement may be found by combining equations (8) and (13)
i \ ( A y2 1
Ux {x, y)= + C1y + C2 x . (14)
v G 2 y
The boundary conditions (5) demand
A h2
G 2
^T^^T+Ch+C2 = 0,
A, h2
- - Ch + C2 = 0,
(15)
and thus
C1 = 0,
h2 (16)
C2 = G 2 . Then expression (14) takes the following form
Ux {x, y) = 2G x{h 2 - y 2 ) . (17)
Let us determine now uy (x,y).
Substituting (7), (9), (10), (13), (16) into (2) we derive
- -14 y + a" ( y) + Y^^" G y + a" ( y)) = 0
then
a
'( y )
A
G
y ■
and therefore
A1 y
a1 V, = ~G~6 + D1y + D2,
(y)
where D1 and D2 are some constants.
Thus (9) can be written, in view of equation (20), as
uy\x
( x y)
A
G 6
+ D1 y + D2.
(19)
(20)
(21)
The boundary conditions (5) demand
A1 h3 ~
+ Dxh + D2 = -U,
A1 h3 ~
- - Dh+D2 = u,
(22)
whence it follows that
D2 = 0,
D1 =--1 h
U +
A1h ~6G
3^
(23)
and then
uy\x
( x, y)
A1 y3 6G
A1h
v^7+"A6G
y.
(24)
To determine A2 we assume that the boundary condition on the fluid pressure (6) is satisfied aty=±h, i.e. at the points A, B, C, D (Fig. 1), thenp(±l, ±h)=0 and equation (7) yields
A 2
Combining equations (7) and (25) we obtain
A2 =- (h2 -12 ).
p(x, y) = A (y2 - h2 +12 - x2 ).
2
(25)
(26)
The analysis of (26) shows that the boundary condition (6) is not exactly met. However the error which arises due to approximate problem solving vanishes when h<<l. In fact, for the case of x=±l the maximum error appearing by using equation (26), i.e. the maximum difference by absolute value between the fluid pressure obtained using equation (26) and the boundary condition (6), is equal to p(±l,0)=Aih2/2. It follows from equation (26) that the maximum pressure proves to equal p(0,±h)= A1l2/2. Since the relative error is determined by division of these values, then the lower is the ratio h/l, the lower is the relative error.
It is pertinent to note that relations (17), (24) and (26) identically comply with the input equations (1)-(6).
To determine the coefficient A1 an additional condition is required.
For this purpose let us substitute (17) and (24) into (4), then
e = A(A2 + + , (27)
2GV * ' 2G h \ 6G J' v 7
and hence the volume strain e of the porous medium is constant with both x and y
e = - h =const(x,y). (28)
Further the porous medium is considered to be incompressible, i.e.
e=0. (29) The incompressibility condition (29) demands
„ 3UG
Ai (30)
and then equations (17), (24) and (26) are rewritten in the finished form
r(x, y) = ^ x{„2 - y2), (31)
UAX, y =-7 x\
2h3
u„ I x,y ) =
( x, y ) = y(y2 - 3h2 ), (32)
p(x,y) = 3G(y2 - h2 + /2 - x2 ). (33)
Determination of the fluid velocity vectors and filtered fluid streamlines
To find out the fluid velocity vectors v the Darcy's law is used [2, 20, 25]
v = - kVp, (34)
where k is the permeability coefficient.
In the two-dimensional problem, the components vx and vy of the vector v (equation (34)) have the form
cPp
Vx = - k — , (35)
ox
dp
V=- V <36)
Then with the help of (33) we find
3UGk
Vx = , 3 x , (37) h3
3UGk (38)
vy y. (38)
h
Let us draw now the fluid streamlines. It is known that the streamlines are coincident with the trajectories in the stationary process [29]. In this paper, it is the stationary process which is considered, therefore equations (37) and (38) may be written as
dx 3UGk dt ~ h3 dy 3UGk
The solutions of (39) and (40) are
dt h
3UGk x = Xo e h3
x, (39)
3 y . (40)
t (41)
Fig. 3. The vectors of the fluid velocity.
3UGk
y=y *" t, (42)
where t is time; X0, Ya are coordinates of some point at t=0. Elimination of t from (41) and (42) yields
y = ^. (43)
x
Figures 2 and 3 show streamlines of the filtered fluid and vectors of the fluid velocity, respectively (h=10; ¿=100).
It should be emphasized that a streamline is determined only by the directions of vectors (their magnitudes are of no significance) [29]. That is why if the fluid pressure is known to comply with (7), then relation (43) can be immediately obtained by using (7) instead of (33).
Determination of the strains and stresses of the porous medium
The total stress components of the completely saturated incompressible porous medium are written as [20]
xx = 2G^x - p, (44)
xy = 2Gey - p, (45)
X xy = G xy , (46)
where the components of the porous medium strains are
^x duy àutoy
e =- e =- y =-+--(4/)
x cx ' y dy ' ixy dy dx V 1
Combining equations (31)-(33) and (47) we obtain
ex (x, y) = 2h3 (h2 - y 2 ),
ey( x, y) = ^ (y2 - h 2 ),
(49)
3U
(50)
Then the total stress components of the porous medium are
3U7G r , , -,
1 I,
(51)
(52)
(53)
An additional point to emphasize is that the magnitude F of the force applied to each plate is readily determined as follow
In this paper, behavior of the porous tissues such as the periodontal ligament, intervertebral disc, articular cartilage was investigated. They are generally subjected to compressive loads, which are transmitted through the surrounding hard tissues (tooth, bones).To a first approximation, such porous tissues saturated by free fluid may be viewed as poroelastic. The porous medium was considered to be sandwiched between two approached parallel rigid impervious plates. The approximate analytical solution of the problem on stationary flow of the interstitial fluid completely saturating the incompressible porous medium was found. The fields of displacements, strains, stresses of the porous medium and fields of fluid pressure and fluid flow were obtained. The determined solution has qualitatively described some processes proceeding in such porous tissues, in particular, of interstitial fluid movement.
1. ARMSTRONG C.G., LAI W.M., MOW V.C. An analysis of the unconfined compression of articular cartilage. Journal of Biomechanical Engineering, 106: 165-173, 1984.
2. BIOT M.A. General theory of three-dimensional consolidation. Journal of Applied Physics, 12: 155-164, 1941.
3. BIOT M.A. Mechanics of deformation and acoustic propagation in porous media. Journal of Applied Physics, 33: 1482-1498, 1962.
4. HENDRY N.G.C. The hydration of the nucleus pulposus and its relation to intervertebral disc derangement. Journal of Bone and Joint Surgery, 40B: 132-144, 1958.
(54)
Conclusions
Acknowledgements
This work was supported in part by a grant from the INTAS, ?97-32158.
References
5. JONES M.L., MIDDLETON J., HICKMAN J., VOLP C., KNOX J. The development of a validated model of orthodontic movement of the maxillary central incisor in the human subject. Russian Journal of Biomechanics, 2(1-2): 36-44, 1998.
6. LAI W.M., MOW V.C. Drag induced compression of articular cartilage during a permeation experiment. Biorheology, 17: 111-123, 1980.
7. LAIBLE J.P., PFLASTER D.S., KRAG M.H., SIMON B.R., HAUGH L.D. A poroelastic-swelling finite element model with application to the intervertebral disc. Spine, 18(5): 659-670, 1993.
8. LAIBLE J.P., PFLASTER D., SIMON B.R., KRAG M.H., POPE M., HAUGH L.D. A dynamic material parameter estimation procedure for soft tissue using a poroelastic finite element model. Journal of Biomechanical Engineering, 116: 19-29, 1994.
9. KATONA T.R., PAYDAR N.H., AKAY H.U., ROBERTS W.E. Stress analysis of bone modelling response to rat molar orthodontics. Journal of Biomechanics, 28(1): 27-38, 1995.
10. KENYON D.E. Consolidation in transversely isotropic solids. Journal of Applied Mechanics, 46: 65-70, 1979.
11. MAK A.F. Unconfined compression of hydrated viscoelastic tissues: A biphasic poroviscoelastic analysis. Biorheology, 23: 371-383, 1986.
12. McGUINNESS N.J.P., WILSON A.N., JONES M.L., MIDDLETON J. A stress analysis of the periodontal ligament under various orthodontic loadings. European Journal of Orthodontics, 13: 231-242,1991.
13. MOW V.C., KUEI S.C., LAI W.M., ARMSTRONG C.G. Biphasic creep and stress relaxation of articular cartilage in compression: theory and experiments. Journal of Biomechanical Engineering, 102: 73-84, 1980.
14. MOW V.C., LAI W.M. Recent developments in synovial joint biomechanics. SIAM Review, 22: 275-317, 1980.
15. MOW V.C., ATESHIAN G.A., SPILKER R.J. Biomechanics of diarthrodial joints: a review of twenty years of progress. Journal of Biomechanical Engineering, 115: 460-467, 1993.
16. MUHLEMAN H.R. Tooth mobility: A review of clinical aspects and research findings. Journal of Periodontology, 38: 686-773, 1967.
17. NYASHIN M.Y., PECHENOV V.S., RAMMERSTORFER F.G. Determination of optimal orthodontic forces. Russian Journal of Biomechanics, 1(1-2): 84-96, 1997.
18. NYASHIN M.Y., OSIPOV A.P., BOLOTOVA M.Ph., NYASHIN Y.I., SIMANOVSKAYA E.Y. Periodontal ligament may be viewed as a porous material filled by free fluid: experimental proof. Russian Journal of Biomechanics, 3(1): 89-95, 1999.
19. NYASHIN M.Y., BAGAUTDINOVA I.V., SIMANOVSKAYA E.Y., CHERNOPAZOV S.A. Biomechanical investigation of a trauma of the upper central incisor. Russian Journal of Biomechanics, 3(1): 96-100, 1999.
20. NYASHIN MY. Mathematical model of the periodontal ligament. Ph.D. Thesis, Perm State Technical University, 1999 [ НЯШИН М.Ю. Математическая модель периодонта. Дисс. ... канд. физико-математических наук. Пермь, 1999 ] (in Russian).
21. OSIPENKO M.A., NYASHIN M.Y., NYASHIN Y.I. Center of resistance and center of rotation of a tooth: the definitions, conditions of existence, properties. Russian Journal of Biomechanics, 3(1): 5-15, 1999.
22. TANNE K., SAKUDA M., BURSTONE C.J. Three-dimensional finite elements analysis for stress in the periodontal tissue by orthodontic forces. American Journal of Orthodontic and Dentofacial Orthopaedics, 92: 499-505, 1987.
23. SPILKER R.L., SUH J.-K., MOW V.C. A finite element analysis of the indentation stress-relaxation response of linear biphasic articular cartilage. Journal of Biomechanical Engineering, 114: 191201,1992.
24. URBAN J.P.G., MAROUDAS A. Swelling of the intervertebral disc: Influence of proteoglycan and collagen contents. Biorheology, 22: 145-157, 1985.
25. БАРЕНБЛАТТ Г.И., ЕНТОВ В.М., РЫЖИК В.М. Теория нестационарной фильтрации жидкости и газа. Москва, Недра, 1972 (in Russian).
26. ГАВРИЛОВ Е.И., ОКСМАН И.М. Ортопедическая стоматология. Москва, Медицина, 1978 (in Russian).
27. ЕГЕР Дж.К. Упругость, прочность и текучесть. Москва, Машгиз, 1961 (in Russian).
28. КУРЛЯНДСКИЙ В.Ю. Зубное протезирование. Атлас. Том 1. Москва, Медицина, 1963 (in Russian).
29. СЕДОВ Л.И. Механика сплошной среды. Т.1. Москва, Наука, 1970 (in Russian).
ДЕФОРМИРОВАНИЕ ПЕРИОДОНТА, МЕЖПОЗВОНКОВОГО ДИСКА, СУСТАВНОГО ХРЯЩА И ДРУГИХ ПРОНИЦАЕМЫХ ДЕФОРМИРУЕМЫХ
ТКАНЕЙ: ПОРОУПРУГИЙ АНАЛИЗ
М.Ю. Няшин (Пермь, Россия)
Ранее было показано (Nyashin M.Y. с соавт., Russian Journal of Biomechanics, 3(1): 89-95, 1999), что периодонт при кратковременном нагружении ведет себя как пористый материал, насыщенный способной перемещаться в нем периодонтальной жидкостью. В настоящей статье приведено решение тестовой задачи, в которой моделировалось движение жидкости в периодонте при поступательном перемещении зуба. Для этого рассматривалась плоская задача о стационарной медленной фильтрации вязкой жидкости, полностью насыщающей деформируемую несжимаемую пористую среду, которая располагается в узкой длинной щели между двумя сближающимися параллельными пластинами. Задача решалась методом полиномов, с помощью которого удалось получить приближенное аналитическое решение задачи. Были определены поля скоростей и линии тока фильтрующейся жидкости, а также получены аналитические выражения для определения всех компонент вектора перемещений точек пористой среды, тензора полных напряжений и тензора малых деформаций пористой среды. Найденное решение качественно совпадает с представлениями о течении периодонтальной жидкости. В статье также отмечается, что предложенная постановка и решение пригодны для исследования поведения некоторых других тканей, которые можно рассматривать как пористые среды. В частности, полученное решение частично описывает сжатие межпозвонкового диска и суставного хряща. Библ. 29.
Ключевые слова: проницаемые деформируемые ткани, пороупругий анализ, периодонт, периодонтальная жидкость, межпозвонковый диск, суставной хрящ, интерстициальная жидкость
Received 11 October 1999
