the invention will now be described in details with reference to various preferred and optional embodiments to make the invention clear . the present invention describes a method for solving the navier - stocks equations of the blood dynamic as a non - newtonian fluid in the left ventricle for modeling of the myocardial motion in an elastic membrane . in an embodiment the invention provides modelling of the blood flow curves inside the left ventricle by studying the flow of the blood curves near echocardiography samples i . e . the basal , mid and apical anterior and the basal , mid and apical inferior and the basal , mid and apical lateral and the basal , mid and apical septum . these samples as the material elastic points in the myocardium of the left ventricle induce mechanical parameters to the viscosity of blood . invention describes method of formulating and calculating the mechanical parameters of blood , numerically , and then applying navier - stocks equations to model the blood flow curve regionally and globally inside the left ventricle . the method is summarized as below b . calculating the myofiber curve for echocardiography samples of step ( a ); c . studying “ quadratic form ” for the curve of step ( b ) for each echocardiography samples ; d . determining the blood flow curve for step ( c ) for each echocardiography samples and e . integrating the blood flow curves of step ( d ) for determining blood flow curve for left ventricle globally . in an embodiment of invention , fig2 illustrates a flowchart giving mathematical signs of the basal anterior and the mid of anterior and the apical anterior in their corresponded regions to obtain good formulizations of the induced mechanical parameters of the blood . referring to fig3 , invention further describes geometrical modeling of the basal , mid and apical anterior using mathlab software as described below . let ε rr , p ba , ε ll , p ba and ε cc , p ba be strain components of the basal anterior , p ba we set γ p ba ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p ba × ε ll , p ba and ε rr , x × ε ll , x × ε cc , x = ε rr , p ba × ε ll , p ba × ε cc , p ba } and similarly for the mid of anterior and the apical anterior would have the following sets ; γ p ma ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p ma × ε ll , p ma and ε rr , x × ε ll , x × ε cc , x = ε rr , p ma × ε ll , p ma × ε cc , p ma } γ p aa ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p aa × ε ll , p aa and ε rr , x × ε ll , x × ε cc , x = ε rr , p aa × ε ll , p aa × ε cc , p aa } in fact , γ p ba ′ γ p ma and γ p aa are those myofiber bands in the myocardium where have been called at fig2 . in a preferred embodiment q &# 39 ; s at fig3 have the following algebraic equations : where , p k and p l are points belonging to γ p ba ∩ o p ba and if p ba =( y 1 , ba , y 2 , ba , y 3 , ba ) as cartesian coordinate . by a similar argument we have the algebraic equations in cartesian coordinate of q &# 39 ; s for the mid of anterior and the apical anterior : where , p k and p l are points belonging to γ p ma ∩ o p ma and if p ma =( y 1 , ma , y 2 , ma , y 3 , ma ) as cartesian coordinate . where , p k and p l are points belonging to γ p aa ∩ o p aa and if p aa =( y 1 , aa , y 2 , aa , y 3 , aa ) as cartesian coordinate . in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p ma of the apical inferior . fig5 shows a rendering of these solutions in the mathlab software . fig4 shows the mechanical parameters of blood which were induced by q p ma in region o p ma related to apical inferior . the surface is ; in the region o p ba , let φ 1 , p ba ( t ), φ 2 , p ba ( t ) and φ 3 , p ba ( t ) are parameterized forms of the projections of the surface f p ba on xy - axis and yz - axis : ⁢ κ 1 , p ba ⁡ ( t ) · n 1 , p ba ⁡ ( t ) = ⅆ t 1 , p ba ⅆ s ; κ 1 , p ba ⁡ ( t ) = ( ( ( d p ba - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p ba ′ 3 ; a 1 , p ba ( t )= s 1 , p ba ″· t 1 , p ba ( t )+ κ 1 , p ba ( t )· n 1 , p ba ( t ) ⁢ κ 2 , p ba ⁡ ( t ) · n 2 , p ba ⁡ ( t ) = ⅆ t 2 , p ba ⅆ s ; κ 2 , p ba ⁡ ( t ) = ( ( ( d p ba - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p ba ′ 3 ; a 2 , p ba ( t )= s 2 , p ba ″· t 2 , p ba ( t )+ κ 2 , p ba ( t )· n 2 , p ba ( t ) ⁢ κ 3 , p ba ⁡ ( t ) · n 3 , p ba ⁡ ( t ) = ⅆ t 2 , p ba ⅆ s ; κ 3 , p ba ⁡ ( t ) = ( ( ( d p ba - ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p ba ′ 3 ; a 3 , p ba ( t )= s 3 , p ba · t 3 , p ba ( t )+ κ 3 , p ba ( t )· n 3 , p ba ( t ) if ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p ba of the basal anterior and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p ba , c 2 , p ba and c 3 , p ba are the graphs of φ 1 , p ba ( t ), φ 2 , p ba ( t ) and φ 3 , p ba ( t ) respectively then the mechanical parameters of the red blood cells in the region o p ba are realized by the following formulas : v 1 , p ba ⁡ ( t ) = ∫ c 1 , p ba ⁢ t 1 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t ; n 1 , p ba ⁡ ( t ) = ∫ c 1 , p ba ⁢ n 1 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t ; a 1 , p ba rbc ⁡ ( t ) = ∫ c 1 , p ba ⁢ a 1 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t v 2 , p ba ⁡ ( t ) = ∫ c 2 , p ba ⁢ t 2 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t ; n 2 , p ba ⁡ ( t ) = ∫ c 2 , p ba ⁢ n 2 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t ; a 2 , p ba rbc ⁡ ( t ) = ∫ c 2 , p ba ⁢ a 2 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t v 3 , p ba ⁡ ( t ) = ∫ c 3 , p ba ⁢ t 3 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t ; n 3 , p ba ⁡ ( t ) = ∫ c 3 , p ba ⁢ n 3 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t ; a 3 , p ba rbc ⁡ ( t ) = ∫ c 3 , p ba ⁢ a 3 , p ba ⁡ ( t ) ⊗ δ ⁡ ( x 1 , x 2 , x 3 , t ) ⁢ ⅆ t the formulas as mentioned hereinabove give analytical solution of the navier - stocks equations in the region o p ba of the basal anterior . the invention provides , with reference to fig5 , provides a rendering of this solution in the mathlab software . in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p ma of the apical inferior . fig7 shows a rendering of these solutions in the mathlab software . fig6 shows the mechanical parameters of blood which were induced by q p ma in region o p ma related to apical inferior . the surface is ; in the region o p ma , let φ 1 , p ma ( t ), φ 2 , p ma ( t ) and φ 3 , p ma ( t ) are parameterized forms of the projections of the surface f p ma on xy - axis and yz - axis : ⁢ κ 1 , p ma ⁡ ( t ) · n 1 , p ma ⁡ ( t ) = ⅆ t 1 , p ma ⅆ s ; κ 1 , p ma ⁡ ( t ) = ( ( ( d p ma - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p ma ′ 3 ; a 1 , p ma ( t )= s 1 , p ma ″· t 1 , p ma ( t )+ κ 1 , p ma ( t )· n 1 , p ma ( t ) ⁢ κ 2 , p ma ⁡ ( t ) · n 2 , p ma ⁡ ( t ) = ⅆ t 2 , p ma ⅆ s ; κ 2 , p ma ⁡ ( t ) = ( ( ( d p ma - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p ma ′ 3 ; a 2 , p ma ( t )= s 2 , p ma ″· t 2 , p ma ( t )+ κ 2 , p ma ( t )· n 2 , p ma ( t ) ⁢ κ 3 , p ma ⁡ ( t ) · n 3 , p ma ⁡ ( t ) = ⅆ t 2 , p ma ⅆ s ; κ 3 , p ma ⁡ ( t ) = ( ( ( d p ma - ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p ma ′ 3 ; a 3 , p ma ( t )= s 3 , p ma · t 3 , p ma ( t )+ κ 3 , p ma ( t )· n 3 , p ma ( t ) if ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p ma of the basal anterior and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p ma , c 2 , p ma and c 3 , p ma are the graphs of φ 1 , p ma ( t ), φ 2 , p ma ( t ) and φ 3 , p ma ( t ) respectively then the mechanical parameters of the red blood cells in the region o p ma are realized by the following formulas : in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p aa of the apical inferior . fig9 shows a rendering of these solutions in the mathlab software . fig8 shows the mechanical parameters of blood which were induced by q p aa in region o p aa related to apical inferior . the surface is ; in the region o p aa , let φ 1 , p aa ( t ), φ 2 , p aa ( t ) and φ 3 , p aa ( t ) are parameterized forms of the projections of the surface f p aa on xy - axis and yz - axis : ⁢ κ 1 , p aa ⁡ ( t ) · n 1 , p aa ⁡ ( t ) = ⅆ t 1 , p aa ⅆ s ; κ 1 , p aa ⁡ ( t ) = ( ( ( d p aa - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p aa ′ 3 ; a 1 , p aa ( t )= s 1 , p aa ″· t 1 , p aa ( t )+ κ 1 , p aa ( t )· n 1 , p aa ( t ) ⁢ κ 2 , p aa ⁡ ( t ) · n 2 , p aa ⁡ ( t ) = ⅆ t 2 , p aa ⅆ s ; κ 2 , p aa ⁡ ( t ) = ( ( ( d p aa - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p aa ′ ⁢ 3 ; a 2 , p aa ( t )= s 2 , p aa ″· t 2 , p aa ( t )+ κ 2 , p aa ( t )· n 2 , p aa ( t ) ⁢ κ 3 , p aa ⁡ ( t ) · n 3 , p aa ⁡ ( t ) = ⅆ t 2 , p aa ⅆ s ; κ 3 , p aa ⁡ ( t ) = ( ( ( d p aa - ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p aa ′ ⁢ 3 ; a 3 , p aa ( t )= s 3 , p aa · t 3 , p aa ( t )+ κ 3 , p aa ( t )· n 3 , p aa ( t ) if ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p ma of the basal anterior and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p aa , c 2 , p aa and c 3 , p aa are the graphs of φ 1 , p aa ( t ), φ 2 , p aa ( t ) and φ 3 , p aa ( t ) respectively then the mechanical parameters of the red blood cells in the region o p ma are realized by the following formulas : in an embodiment the invention provides mathematical signs of the basal inferior and the mid of inferior and the apical inferior in their corresponded regions to gain good formulizations of the induced mechanical parameters of the blood , as shown in fig1 . accordingly , let ε rr , p bl , ε ll , p bl and ε cc , p bl be the strain components of the basal inferior p bl , then γ p bl ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p bl × ε ll , p bl and ε rr , x × ε ll , x × ε cc , x = ε rr , p bl × ε ll , p bl × ε cc , p bl } γ p ml ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p ml × ε ll , p ml and ε rr , x × ε ll , x × ε cc , x = ε rr , p ml × ε ll , p ml × ε cc , p ml } γ p al ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p al × ε ll , p al and ε rr , x × ε ll , x × ε cc , x = ε rr , p al × ε ll , p al × ε cc , p al } γ p bl , γ p ml and γ p al are the myofiber bands illustrated in fig2 . the q &# 39 ; s have following values where , p k and p l are points belonging to γ p bl ∩ o p bl and if p bl =( y 1 , bl , y 2 , bl , y 3 , bl ) as cartesian coordinate similarly , the cartesian coordinates for q &# 39 ; s for mid and apical inferiors are as follows ; q p m ⁢ ⁢ l : d p m ⁢ ⁢ l = ( ∑ k , l ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 2 + ( ∑ k , l ⁢ ɛ ll ⁢ ⁢ p k , p l ⁢ ⅆ t ) · y 2 2 + ( ∑ k , l ⁢ ɛ cc ⁢ ⁢ p k , p l ⁢ ⅆ t ) · y 3 2 d p m ⁢ ⁢ l = ( ∑ k , l ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 , m ⁢ ⁢ l 2 + ( ∑ k , l ⁢ ɛ ll ⁢ ⁢ p k , p l ⁢ ⅆ t ) · y 2 , m ⁢ ⁢ l 2 + ( ∑ k , l ⁢ ɛ cc ⁢ ⁢ p k , p l ⁢ ⅆ t ) · y 3 , m ⁢ ⁢ l 2 where , p k and p l are points belonging to γ p ml ∩ o p ml and if p ml =( y 1 , ml , y 2 , ml , y 3 , ml ) as cartesian coordinate . q p al : d p al = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 2 d p al = ( ∑ k . , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 , al 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 , al 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 , al 2 where , p k and p l are points belonging to γ p al ∩ o p al and if p al =( y 1 , al , y 2 , al , y 3 , al ) as cartesian coordinate . in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p al of the apical inferior . fig1 shows a rendering of these solutions in the mathlab software . fig1 shows the mechanical parameters of blood which were induced by q p al in region o p al related to apical inferior . the surface is ; in the region o p al , let φ 1 , p al ( t ), φ 2 , p al ( t ) and φ 3 , p al ( t ) are parameterized forms of the projections of the surface f p al on xy - axis and yz - axis : ⁢ κ 1 , p al ⁡ ( t ) · n 1 , p al ⁡ ( t ) = ⅆ t 1 , p al ⅆ s ; κ 1 , p al ⁡ ( t ) = ( ( ( d p al - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p al ′ ⁢ 3 ; a 1 , p al ( t )= s 1 , p al ″· t 1 , p al ( t )+ κ 1 , p al ( t )· n 1 , p al ( t ) ⁢ κ 2 , p al ⁡ ( t ) · n 2 , p al ⁡ ( t ) = ⅆ t 2 , p al ⅆ s ; κ 2 , p al ⁡ ( t ) = ( ( ( d p al - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p al ′ ⁢ 3 ; a 2 , p al ( t )= s 2 , p al ″· t 2 , p al ( t )+ κ 2 , p al ( t )· n 2 , p al ( t ) ⁢ κ 3 , p al ⁡ ( t ) · n 3 , p al ⁡ ( t ) = ⅆ t 2 , p al ⅆ s ; κ 3 , p al ⁡ ( t ) = ( ( ( d p al - ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p al ′ ⁢ 3 ; a 3 , p al ( t )= s 3 , p al · t 3 , p al ( t )+ κ 3 , p al ( t )· n 3 , p al ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p al of the apical inferior and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p al , c 2 , p al and c 3 , p al are the graphs of φ 1 , p al ( t ), φ 2 , p al ( t ) and φ 3 , p al ( t ) respectively then the mechanical parameters of the red blood cells in the region o p al are calculated by the following formulae : in another preferred embodiment the invention provides an analytical solution of the navier - stocks equations in the region o p ml of the mid inferior . fig1 shows a rendering of these solutions in the mathlab software . fig1 shows the mechanical parameters of blood which were induced by q p ml in region o p ml related to apical inferior . the surface is ; in the region o p ml , let φ 1 , p ml ( t ), φ 2 , p ml ( t ) and φ 3 , p ml ( t ) are parameterized forms of the projections of the surface f p ml on xy - axis and yz - axis : ⁢ κ 1 , p ml ⁡ ( t ) · n 1 , p ml ⁡ ( t ) = ⅆ t 1 , p ml ⅆ s ; κ 1 , p ml ⁡ ( t ) = ( ( ( d p ml - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p ml ′ ⁢ 3 ; a 1 , p ml ( t )= s 1 , p ml ″· t 1 , p ml ( t )+ κ 1 , p ml ( t )· n 1 , p ml ( t ) ⁢ κ 2 , p ml ⁡ ( t ) · n 2 , p ml ⁡ ( t ) = ⅆ t 2 , p ml ⅆ s ; κ 2 , p ml ⁡ ( t ) = ( ( ( d p ml - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p ml ′ ⁢ 3 ; a 2 , p ml ( t )= s 2 , p ml ″· t 2 , p ml ( t )+ κ 2 , p ml ( t )· n 2 , p ml ( t ) ⁢ κ 3 , p ml ⁡ ( t ) · n 3 , p ml ⁡ ( t ) = ⅆ t 2 , p ml ⅆ s ; κ 3 , p ml ⁡ ( t ) = ( ( ( d p ml - ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p ml ′ ⁢ 3 ; a 3 , p ml ( t )= s 3 , p ml · t 3 , p ml ( t )+ κ 3 , p ml ( t )· n 3 , p ml ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p ml of the mid inferior and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p ml , c 2 , p ml and c 3 , p ml are the graphs of φ 1 , p ml ( t ), φ 2 , p ml ( t ) and φ 3 , p ml ( t ) respectively then the mechanical parameters of the red blood cells in the region o p ml are calculated by the following formulae : in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p bl of the basal inferior . fig1 shows a rendering of these solutions in the mathlab software . fig1 shows the mechanical parameters of blood which were induced by q p bl in region o p bl related to apical inferior . the surface is ; in the region o p bl , let φ 1 , p bl ( t ), φ 2 , p bl ( t ) and φ 3 , p bl ( t ) are parameterized forms of the projections of the surface f p bl on xy - axis and yz - axis : ⁢ κ 1 , p b ⁢ l ⁡ ( t ) · n 1 , p b ⁢ l ⁡ ( t ) = ⅆ t 1 , p b ⁢ l ⅆ s ; κ 1 , p b ⁢ l ⁡ ( t ) = ( ( ( d p b ⁢ l - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p b ⁢ l ′ ⁢ 3 ; a 1 , p bl ( t )= s 1 , p bl ″· t 1 , p bl ( t )+ κ 1 , p bl ( t )· n 1 , p bl ( t ) ⁢ κ 2 , p b ⁢ l ⁡ ( t ) · n 2 , p b ⁢ l ⁡ ( t ) = ⅆ t 2 , p b ⁢ l ⅆ s ; κ 2 , p b ⁢ l ⁡ ( t ) = ( ( ( d p b ⁢ l - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p b ⁢ l ′ ⁢ 3 ; a 2 , p bl ( t )= s 2 , p bl ″· t 2 , p bl ( t )+ κ 2 , p bl ( t )· n 2 , p bl ( t ) ⁢ κ 3 , p b ⁢ l ⁡ ( t ) · n 3 , p b ⁢ l ⁡ ( t ) = ⅆ t 2 , p b ⁢ l ⅆ s ; κ 3 , p b ⁢ l ⁡ ( t ) = ( ( ( d p b ⁢ l - ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p b ⁢ l ′ ⁢ 3 ; a 3 , p bl ( t )= s 3 , p bl · t 3 , p bl ( t )+ κ 3 , p bl ( t )· n 3 , p bl ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p bl of the basal inferior and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p ml , c 2 , p ml and c 3 , p ml are the graphs of φ 1 , p bl ( t ), φ 2 , p bl ( t ) and φ 3 , p bl ( t ) respectively then the mechanical parameters of the red blood cells in the region o p bl are calculated by the following formulae : in an embodiment , as illustrated in fig1 , the invention provides mathematical signs of basal lateral , mid lateral and apical lateral to obtain good formulizations of the induced mathematical parameters of the blood . the invention further provides geometrical modelling of the basal , mid and apical lateral as described below ; let ε rr , p bl , ε ll , p bl and ε cc , p bl be the strain components of the basal inferior p bl , then γ p bl ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p bl × ε ll , p bl and ε rr , x × ε ll , x × ε cc , x = ε rr , p bl × ε ll , p bl × ε cc , p bl } γ p ml ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p ml × ε ll , p ml and ε rr , x × ε ll , x × ε cc , x = ε rr , p ml × ε ll , p ml × ε cc , p ml } γ p al ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p al × ε ll , p al and ε rr , x × ε ll , x × ε cc , x = ε rr , p al × ε ll , p al × ε cc , p al } γ p bl , γ p ml and γ p al are the myofiber bands illustrated in fig2 . the q &# 39 ; s have following values where , p k and p l are points belonging to γ p bl ∩ o p bl and if p bl =( y 1 , bl , y 2 , bl , y 3 , bl ) as cartesian coordinate similarly , the cartesian coordinates for q &# 39 ; s for mid and apical inferiors are as follows ; q p ml : d p bl = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 2 d p ml = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 , ml 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 , ml 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 , ml 2 where , p k and p l are points belonging to γ p ml ∩ o p ml and if p ml =( y 1 , ml , y 2 , ml , y 3 , ml ) as cartesian coordinate : q p a ⁢ l : d p al = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 2 d p a ⁢ l = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 , a ⁢ l 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 , a ⁢ l 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 , a ⁢ l 2 where , p k and p l are points belonging to γ p al ∩ o p al and if p al =( y 1 , al , y 2 , al , y 3 , al ) as cartesian coordinate . in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p al of the apical inferior . fig2 shows a rendering of these solutions in the mathlab software . fig2 , illustrates mechanical parameters of blood induced by q p al in the region o p al related to apical lateral . the surface parameters are as follows in the region o p al , let φ 1 , p al ( t ), φ 2 , p al ( t ) and φ 3 , p al ( t ) are parameterized forms of the projections of the surface f p al on xy - axis and yz - axis : ⁢ κ 1 , p al ⁡ ( t ) · n 1 , p al ⁡ ( t ) = ⅆ t 1 , p al ⅆ s ; κ 1 , p al ⁡ ( t ) = ( ( ( d p al - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p al ′ 3 ; a 1 , p al ( t )= s 1 , p al ″· t 1 , p al ( t )+ κ 1 , p al ( t )· n 1 , p al ( t ) ⁢ κ 2 , p al ⁡ ( t ) · n 2 , p al ⁡ ( t ) = ⅆ t 2 , p al ⅆ s ; κ 2 , p al ⁡ ( t ) = ( ( ( d p al - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p al ′ 3 ; a 2 , p al ( t )= s 2 , p al ″· t 2 , p al ( t )+ κ 2 , p al ( t )· n 2 , p al ( t ) ⁢ κ 3 , p al ⁡ ( t ) · n 3 , p al ⁡ ( t ) = ⅆ t 2 , p al ⅆ s ; κ 3 , p al ⁡ ( t ) = ( ( ( d p al - ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p al ′ 3 ; a 3 , p al ( t )= s 3 , p al · t 3 , p al ( t )+ κ 3 , p al ( t )· n 3 , p al ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p al of the apical lateral and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p al , c 2 , p al and c 3 , p al are the graphs of φ 1 , p al ( t ), φ 2 , p al ( t ) and φ 3 , p al ( t ) respectively then the mechanical parameters of the red blood cells in the region o p al are calculated by the following formulae : in another preferred embodiment the invention provides an analytical solution of the navier - stocks equations in the region o p ml of the mid lateral . fig2 shows a rendering of these solutions in the mathlab software . fig2 shows the mechanical parameters of blood which were induced by q p ml in region o p ml related to apical inferior . the surface is ; in the region o p ml , let φ 1 , p ml ( t ), φ 2 , p ml ( t ) and φ 3 , p ml ( t ) are parameterized forms of the projections of the surface f p ml on xy - axis , xz - axis and yz - axis : ⁢ κ 1 , p ml ⁡ ( t ) · n 1 , p ml ⁡ ( t ) = ⅆ t 1 , p ml ⅆ s ; κ 1 , p ml ⁡ ( t ) = ( ( ( d p ml - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p ml ′ 3 ; a 1 , p ml ( t )= s 1 , p ml ″· t 1 , p ml ( t )+ κ 1 , p ml ( t )· n 1 , p ml ( t ) ⁢ κ 2 , p ml ⁡ ( t ) · n 2 , p ml ⁡ ( t ) = ⅆ t 2 , p ml ⅆ s ; κ 2 , p ml ⁡ ( t ) = ( ( ( d p ml - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p ml ′ 3 ; a 2 , p ml ( t )= s 2 , p ml ″· t 2 , p ml ( t )+ κ 2 , p ml ( t )· n 2 , p ml ( t ) ⁢ κ 3 , p ml ⁡ ( t ) · n 3 , p ml ⁡ ( t ) = ⅆ t 2 , p ml ⅆ s ; κ 3 , p ml ⁡ ( t ) = ( ( ( d p ml - ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p ml ′ 3 ; a 3 , p ml ( t )= s 3 , p ml · t 3 , p ml ( t )+ κ 3 , p ml ( t )· n 3 , p ml ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p ml of the mid lateral and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p ml , c 2 , p ml and c 3 , p ml are the graphs of φ 1 , p ml ( t ), φ 2 , p ml ( t ) and φ 3 , p ml ( t ) respectively then the mechanical parameters of the red blood cells in the region o p ml are calculated by the following formulae : in another preferred embodiment the invention provides an analytical solution of the navier - stocks equations in the region o p bl of the basal lateral . fig2 shows a rendering of these solutions in the mathlab software . fig2 shows the mechanical parameters of blood which were induced by q p bl in region o p bl related to apical inferior . the surface is ; in the region o p bl , let φ 1 , p bl ( t ), φ 2 , p bl ( t ) and φ 3 , p bl ( t ) are parameterized forms of the projections of the surface f p bl on xy - axis , xz - axis and yz - axis : ⁢ κ 1 , p bl ⁡ ( t ) · n 1 , p bl ⁡ ( t ) = ⅆ t 1 , p bl ⅆ s ; κ 1 , p bl ⁡ ( t ) = ( ( ( d p bl - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p bl ′ 3 ; a 1 , p bl ( t )= s 1 , p bl ″· t 1 , p bl ( t )+ κ 1 , p bl ( t )· n 1 , p bl ( t ) ⁢ κ 2 , p bl ⁡ ( t ) · n 2 , p bl ⁡ ( t ) = ⅆ t 2 , p bl ⅆ s ; κ 2 , p bl ⁡ ( t ) = ( ( ( d p bl - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p bl ′ 3 ; a 2 , p bl ( t )= s 2 , p bl ″· t 2 , p bl ( t )+ κ 2 , p bl ( t )· n 2 , p bl ( t ) ⁢ κ 3 , p bl ⁡ ( t ) · n 3 , p bl ⁡ ( t ) = ⅆ t 2 , p bl ⅆ s ; κ 3 , p bl ⁡ ( t ) = ( ( ( d p bl - ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p bl ′ 3 ; a 3 , p bl ( t )= s 3 , p bl · t 3 , p bl ( t )+ κ 3 , p bl ( t )· n 3 , p bl ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p bl of the basal lateral and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p bl , c 2 , p bl and c 3 , p bl are the graphs of φ 1 , p bl ( t ), φ 2 , p bl ( t ) and φ 3 , p bl ( t ) respectively then the mechanical parameters of the red blood cells in the region o p bl are calculated by the following formulae : in an embodiment , as illustrated in fig2 , the invention provides mathematical signs of basal septum , mid septum and apical septum to obtain good formulizations of the induced mathematical parameters of the blood . the invention further provides geometrical modelling of the basal , mid and apical septum as described below ; let ε rr , p bs , ε p bs and ε cc , p bs be the strain components of the basal inferior p bs , then γ p bs ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p bs × ε ll , p bs and ε rr , x × ε ll , x × ε cc , x = ε rr , p bs × ε ll , p bs × ε cc , p bs } γ p ms ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p ms × ε ll , p ms and ε rr , x × ε ll , x × ε cc , x = ε rr , p ms × ε ll , p ms × ε cc , p ms } γ p as ={ each mayocardial sample x that ε rr , x × ε ll , x = ε rr , p as × ε ll , p as and ε rr , x × ε ll , x × ε cc , x = ε rr , p as × ε ll , p as × ε cc , p as } γ p bs , γ p ms and γ p as are the myofiber bands illustrated in fig2 . the q &# 39 ; s have following values where , p k and p l are points belonging to γ p bs ∩ o p bs and if p bs =( y 1 , bs , y 2 , bs , y 3 , bs ) as cartesian coordinate similarly , the cartesian coordinates for q &# 39 ; s for mid and apical inferiors are as follows ; q p ms ∷ d p ms = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 2 d p ms = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 , ms 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 , ms 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 , ms 2 ⁢ where , p k and p l are points belonging to γ p ms ∩ o p ms and if p ms =( y 1 , ms , y 2 , ms , y 3 , ms ) as cartesian coordinate . q p as ∷ d p as = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 2 d p as = ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ⁢ ⅆ t ) · y 1 , as 2 + ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ⁢ ⅆ t ) · y 2 , as 2 + ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ⁢ ⅆ t ) · y 3 , as 2 where , p k and p l are points belonging to γ p as ∩ o p as and if p as =( y 1 , as , y 2 , as , y 3 , as ) as cartesian coordinate . in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p as of the apical septum . fig3 shows a rendering of these solutions in the mathlab software . fig2 , illustrates mechanical parameters of blood induced by q p as in the region o p as related to apical lateral . the surface parameters are as follows in the region o p as , let φ 1 , p as ( t ), φ 2 , p as ( t ) and φ 3 , p as ( t ) are parameterized forms of the projections of the surface f p as on xy - axis , xz - axis and yz - axis : ⁢ κ 1 , p as ⁡ ( t ) · n 1 , p as ⁡ ( t ) = ⅆ t 1 , p as ⅆ s ; κ 1 , p as ⁡ ( t ) = ( ( ( d p as - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p as ′ 3 ; a 1 , p as ( t )= s 1 , p as ″· t 1 , p as ( t )+ κ 1 , p as ( t )· n 1 , p as ( t ) ⁢ κ 2 , p as ⁡ ( t ) · n 2 , p as ⁡ ( t ) = ⅆ t 2 , p as ⅆ s ; κ 2 , p as ⁡ ( t ) = ( ( ( d p as - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p as ′ 3 ; a 2 , p as ( t )= s 2 , p as ″· t 2 , p as ( t )+ κ 2 , p as ( t )· n 2 , p as ( t ) ⁢ κ 3 , p as ⁡ ( t ) · n 3 , p as ⁡ ( t ) = ⅆ t 2 , p as ⅆ s ; κ 3 , p as ⁡ ( t ) = ( ( ( d p as - ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p as ′ 3 ; a 3 , p as ( t )= s 3 , p as · t 3 , p as ( t )+ κ 3 , p as ( t )· n 3 , p as ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p as of the apical septum and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p as , c 2 , p as and c 3 , p as are the graphs of φ 1 , p as ( t ), φ 2 , p as ( t ) and φ 3 , p as ( t ) respectively then the mechanical parameters of the red blood cells in the region o p as are calculated by the following formulae : in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p ms of the mid septum . fig3 shows a rendering of these solutions in the mathlab software . fig3 , illustrates mechanical parameters of blood induced by q p ms in the region o p ms related to mid lateral . the surface parameters are as follows in the region o p ms , let φ 1 , p ms ( t ), φ 2 , p ms ( t ) and φ 3 , p ms ( t ) are parameterized forms of the projections of the surface f p ms on xy - axis , xz - axis and yz - axis : ⁢ κ 1 , p ms ⁡ ( t ) · n 1 , p ms ⁡ ( t ) = ⅆ t 1 , p ms ⅆ s ; κ 2 , p ms ⁡ ( t ) = ( ( ( d p ms - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p ms ′ ⁢ ⁢ 3 ; a 1 , p ms ( t )= s 1 , p ms ″· t 1 , p ms ( t )+ κ 1 , p ms ( t )· n 1 , p ms ( t ) ⁢ κ 2 , p ms ⁡ ( t ) · n 2 , p ms ⁡ ( t ) = ⅆ t 2 , p ms ⅆ s ; κ 2 , p ms ⁡ ( t ) = ( ( ( d p ms - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p ms ′ ⁢ ⁢ 3 ; a 2 , p ms ( t )= s 2 , p ms ″· t 2 , p ms ( t )+ κ 2 , p ms ( t )· n 2 , p ms ( t ) ⁢ κ 3 , p ms ⁡ ( t ) · n 3 , p ms ⁡ ( t ) = ⅆ t 2 , p ms ⅆ s ; κ 3 , p ms ⁡ ( t ) = ( ( ( d p ms - ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p ms ′ ⁢ ⁢ 3 ; a 3 , p ms ( t )= s 3 , p ms · t 3 , p ms ( t )+ κ 3 , p ms ( t )· n 3 , p ms ( t ) ⁢ κ 1 , p ms ⁡ ( t ) · n 1 , p ms ⁡ ( t ) = ⅆ t 1 , p ms ⅆ s ; κ 1 , p ms ⁢ ( t ) = ( ( ( d p ms - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p ms ′ ⁢ ⁢ 3 ; a 1 , p ms ( t )= s 1 , p ms ″· t 1 , p ms ( t )+ κ 1 , p ms ( t )· n 1 , p ms ( t ) ⁢ κ 2 , p ms ⁡ ( t ) · n 2 , p ms ⁡ ( t ) = ⅆ t 2 , p ms ⅆ s ; κ 2 , p ms ⁡ ( t ) = ( ( ( d p ms - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p ms ′ ⁢ ⁢ 3 ; a 2 , p ms ( t )= s 2 , p ms ″· t 2 , p ms ( t )+ κ 2 , p ms ( t )· n 2 , p ms ( t ) ⁢ κ 3 , p ms ⁡ ( t ) · n 3 , p ms ⁡ ( t ) = ⅆ t 2 , p ms ⅆ s ; κ 3 , p ms ⁢ ( t ) = ( ( ( d p ms - ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p ms ′ ⁢ ⁢ 3 ; a 3 , p ms ( t )= s 3 , p ms · t 3 , p ms ( t )+ κ 3 , p ms ( t )· n 3 , p ms ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p ms of the apical septum and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p ms , c 2 , p ms and c 3 , p ms are the graphs of φ 1 , p ms ( t ), φ 2 , p ms ( t ) and φ 3 , p ms ( t ) respectively then the mechanical parameters of the red blood cells in the region o p ms are calculated by the following formulae : in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p as of the apical septum . fig3 shows a rendering of these solutions in the mathlab software . fig2 , illustrates mechanical parameters of blood induced by q p as in the region o p as related to apical lateral . the surface parameters are as follows in the region o p as , let φ 1 , p as ( t ), φ 2 , p as ( t ) and φ 3 , p as ( t ) are parameterized forms of the projections of the surface f p as on xy - axis , xz - axis and yz - axis : ⁢ κ 1 , p as ⁡ ( t ) · n 1 , p as ⁡ ( t ) = ⅆ t 1 , p as ⅆ s ; κ 1 , p as ⁢ ( t ) = ( ( ( d p as - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p as ′ ⁢ ⁢ 3 ; a 1 , p as ( t )= s 1 , p as · t 1 , p as ( t )+ κ 1 , p as ( t )· n 1 , p as ( t ) ⁢ κ 2 , p as ⁡ ( t ) · n 2 , p as ⁡ ( t ) = ⅆ t 2 , p as ⅆ s ; κ 2 , p as ⁡ ( t ) = ( ( ( d p as - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p as ′ ⁢ ⁢ 3 ; a 2 , p as ( t )= s 2 , p as ″· t 2 , p as ( t )+ κ 2 , p as ( t )· n 2 , p as ( t ) ⁢ κ 3 , p as ⁡ ( t ) · n 3 , p as ⁡ ( t ) = ⅆ t 2 , p as ⅆ s ; κ 3 , p as ⁢ ( t ) = ( ( ( d p as - ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p as ′ ⁢ ⁢ 3 ; a 3 , p as ( t )= s 3 , p as · t 3 , p as ( t )+ κ 3 , p as ( t )· n 3 , p as ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p as of the apical septum and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p as , c 2 , p as and c 3 , p as are the graphs of φ 1 , p as ( t ), φ 2 , p as ( t ) and φ 3 , p as ( t ) respectively then the mechanical parameters of the red blood cells in the region o p as are calculated by the following formulae : in a preferred embodiment , the invention provides an analytical solution of the navier - stocks equations in the region o p bs of the base septum . fig3 shows a rendering of these solutions in the mathlab software . fig3 , illustrates mechanical parameters of blood induced by q p bs in the region o p bs related to mid lateral . the surface parameters are as follows in the region o p bs , let φ 1 , p bs ( t ), φ 2 , p bs ( t ) and φ 3 , p bs ( t ) are parameterized forms of the projections of the surface f p bs on xy - axis , xz - axis and yz - axis : ⁢ κ 1 , p bs ⁡ ( t ) · n 1 , p bs ⁡ ( t ) = ⅆ t 1 , p bs ⅆ s ; κ 1 , p bs ⁢ ( t ) = ( ( ( d p bs - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p bs ′ ⁢ ⁢ 3 ; a 1 , p bs ( t )= s 1 , p bs ″· t 1 , p bs ( t )+ κ 1 , p bs ( t )· n 1 , p bs ( t ) ⁢ κ 2 , p bs ⁡ ( t ) · n 2 , p bs ⁡ ( t ) = ⅆ t 2 , p bs ⅆ s ; κ 2 , p bs ⁡ ( t ) = ( ( ( d p bs - ( ∑ k , l ⁢ ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p bs ′ ⁢ ⁢ 3 ; a 2 , p bs ( t )= s 2 , p bs ″· t 2 , p bs ( t )+ κ 2 , p bs ( t )· n 2 , p bs ( t ) ⁢ κ 3 , p bs ⁡ ( t ) · n 3 , p bs ⁡ ( t ) = ⅆ t 2 , p bs ⅆ s ; κ 3 , p bs ⁢ ( t ) = ( ( ( d p bs - ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p bs ′ ⁢ ⁢ 3 ; a 3 , p bs ( t )= s 3 , p bs · t 3 , p bs ( t )+ κ 3 , p bs ( t )· n 3 , p bs ( t ) ⁢ κ 1 , p bs ⁡ ( t ) · n 1 , p bs ⁡ ( t ) = ⅆ t 1 , p bs ⅆ s ; κ 1 , p bs ⁡ ( t ) = ( ( ( d p bs - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 1 , p bs ′ ⁢ 3 ; a 1 , p bs ( t )= s 1 , p bs ″· t 1 , p bs ( t )+ κ 1 , p bs ( t )· n 1 , p bs ( t ) ⁢ κ 2 , p bs ⁡ ( t ) · n 2 , p bs ⁡ ( t ) = ⅆ t 2 , p bs ⅆ s ; κ 2 , p bs ⁡ ( t ) = ( ( ( d p bs - ( ∑ k , l ⁢ ɛ rr p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ cc p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 2 , p bs ′ ⁢ 3 ; a 2 , p bs ( t )= s 2 , p bs ″· t 2 , p bs ( t )+ κ 2 , p bs ( t )· n 2 , p bs ( t ) ⁢ κ 3 , p bs ⁡ ( t ) · n 3 , p bs ⁡ ( t ) = ⅆ t 2 , p bs ⅆ s ; κ 3 , p bs ⁡ ( t ) = ( ( ( d p bs - ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ⁢ t 2 ) / ( ∑ k , l ⁢ ɛ ll p k , p l ′ ⁢ ⅆ t ) ) 1 2 ) - 0 / s 3 , p bs ′ ⁢ 3 ; a 3 , p bs ( t )= s 3 , p bs · t 3 , p bs ( t )+ κ 3 , p bs ( t )· n 3 , p bs ( t ) ( x 1 , x 2 , x 3 , t ) is the coordinate system of the red blood cell in a neighbourhood o p bs of the basal septum and δ ( x 1 , x 2 , x 3 , t )= δ *( x 1 , t )· δ *( x 2 , t )· δ *( x 3 , t ) where δ * is the dirac function and c 1 , p bs , c 2 , p bs and c 3 , p bs are the graphs of φ 1 , p bs ( t ), φ 2 , p bs ( t ) and φ 3 , p bs ( t ) respectively then the mechanical parameters of the red blood cells in the region o p bs are calculated by the following formulae : in an embodiment , the invention provides method for regionally making blood flow curve as described below ; setting v p aa ( t )=( v 1 , p aa ( t ), v 2 , p aa ( t ), v 3 , p aa ( t )) as field velocity vectors of the blood in region o p aa , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p aa is called as bfc p aa (( x 1 , x 2 , x 3 , t )) then setting v p ma ( t )=( v 1 , p ma ( t ), v 2 , p ma ( t ), v 3 , p ma ( t )) as field velocity vectors of the blood in region o p ma , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p ma is called as bfc p ma (( x 1 , x 2 , x 3 , t )) then setting v p ba ( t )=( v 1 , p ba ( t ), v 2 , p ba ( t ), v 3 , p ba ( t )) as field velocity vectors of the blood in region o p ba , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p ba is called as bfc p ba (( x 1 , x 2 , x 3 , t )) then setting v p al ( t )=( v 1 , p al ( t ), v 2 , p al ( t ), v 3 , p al ( t )) as field velocity vectors of the blood in region o p al , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p al is called as bfc p al (( x 1 , x 2 , x 3 , t )) then setting v p ml ( t )=( v 1 , p ml ( t ), v 2 , p ml ( t ), v 3 , p ml ( t )) as field velocity vectors of the blood in region o p ml , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p ml is called as bfc p ml (( x 1 , x 2 , x 3 , t )) then setting v p bl ( t )=( v 1 , p bl ( t ), v 2 , p bl ( t ), v 3 , p bl ( t )) as field velocity vectors of the blood in region o p bl , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p bl is called as bfc p bl (( x 1 , x 2 , x 3 , t )) then setting v p al ( t )=( v 1 , p al ( t ), v 2 , p al ( t ), v 3 , p al ( t )) as field velocity vectors of the blood in region o p al , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p al is called as bfc p al (( x 1 , x 2 , x 3 , t )) then setting v p ml ( t )=( v 1 , p ml ( t ), v 2 , p ml ( t ), v 3 , p ml ( t )) as field velocity vectors of the blood in region o p ml , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p ml is called as bfc p ml (( x 1 , x 2 , x 3 , t )) then setting v p bl ( t )=( v 1 , p bl ( t ), v 2 , p bl ( t ), v 3 , p bl ( t )) as field velocity vectors of the blood in region o p bl , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p bl is called as bfc p bl (( x 1 , x 2 , x 3 , t )) then setting v p as ( t )=( v 1 , p as ( t ), v 2 , p as ( t ), v 3 , p as ( t )) as field velocity vectors of the blood in region o p as , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p as is called as bfc p as (( x 1 , x 2 , x 3 , t )) then setting v p ms ( t )=( v 1 , p ms ( t ), v 2 , p ms ( t ), v 3 , p ms ( t )) as field velocity vectors of the blood in region o p ms , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p ms is called as bfc p ms (( x 1 , x 2 , x 3 , t )) then setting v p bs ( t )=( v 1 , p bs ( t ), v 2 , p bs ( t ), v 3 , p bs ( t )) as field velocity vectors of the blood in region o p bs , field of displacements in the real time at the same region is obtained by : if , algebraic form of r p bs is called as bfc p bs (( x 1 , x 2 , x 3 , t )) then x blood flow in lv = x p aa ∪ x p ma ∪ x p ba ∪ x p al ∪ x p ml ∪ x p bl ∪ x p al ∪ x p ml ∪ x p bl ∪ x p as ∪ x p ms ∪ x p bs .
the present invention discloses a method for solving the navier - stokes equation of blood dynamics as a non - newtonian fluid in the left ventricle . the method seeks to provide a model of the model of myocardial motion as an elastic membrane . this invention provides a new method to study the blood flow inside a biological membrane , estimated using quadratic equations .