# Modeling of the aorta artery aneurysms and renal artery stenosis using cardiovascular electronic system

- Kamran Hassani
^{1}Email author, - Mahdi Navidbakhsh†
^{2}and - Mostafa Rostami†
^{3}

**6**:22

https://doi.org/10.1186/1475-925X-6-22

© Hassani et al; licensee BioMed Central Ltd. 2007

**Received: **21 January 2007

**Accepted: **09 June 2007

**Published: **09 June 2007

## Abstract

### Background

The aortic aneurysm is a dilatation of the aortic wall which occurs in the saccular and fusiform types. The aortic aneurysms can rupture, if left untreated. The renal stenosis occurs when the flow of blood from the arteries leading to the kidneys is constricted by atherosclerotic plaque. This narrowing may lead to the renal failure. Previous works have shown that, modelling is a useful tool for understanding of cardiovascular system functioning and pathophysiology of the system. The present study is concerned with the modelling of aortic aneurysms and renal artery stenosis using the cardiovascular electronic system.

### Methods

The geometrical models of the aortic aneurysms and renal artery stenosis, with different rates, were constructed based on the original anatomical data. The pressure drop of each section due to the aneurysms or stenosis was computed by means of computational fluid dynamics method. The compliance of each section with the aneurysms or stenosis is also calculated using the mathematical method. An electrical system representing the cardiovascular circulation was used to study the effects of these pressure drops and the compliance variations on this system.

### Results

The results showed the decreasing of pressure along the aorta and renal arteries lengths, due to the aneurysms and stenosis, at the peak systole. The mathematical method demonstrated that compliances of the aorta sections and renal increased with the expansion rate of the aneurysms and stenosis. The results of the modelling, such as electrical pressure graphs, exhibited the features of the pathologies such as hypertension and were compared with the relevant experimental data.

### Conclusion

We conclude from the study that the aortic aneurysms as well as renal artery stenosis may be the most important determinant of the arteries rupture and failure. Furthermore, these pathologies play important rules in increase of the cardiovascular pulse pressure which leads to the hypertension.

## Background

The aortic aneurysm is a disease, which is defined as focal or diffuse dilatation of the aorta. Most of the aorta aneurysms are fusiform (concentric radial dilatation) but infrequently may be saccular (eccentric radial dilatation). The abdominal aorta aneurysm is the most common form of the aneurismal disease. Less commonly patients may present with the thoracic aorta aneurysms. The aorta aneurysms have primarily been studied by Long [1] and Morris [2] who investigated the compliance of aortic aneurysms and observed the effects of the pathology. More recent studies have used the clinical data to investigate the aortic aneurysms [3–5].

- 1)
A brief review of the electronic cardiovascular system which has been previously described in detail [10].

- 2)
The computational fluid dynamics method which has been used to compute the pressure drops due to the pathologies.

- 3)
The mathematical method which has been used to calculate the variations of the compliance due to the pathologies.

- 4)
The study of the effects of the pathologies using the electronic cardiovascular system and investigating the cases.

The obtained results have been compared with the relevant clinical data to determine whether our modelling method has been able to present the effects of the pathologies appropriately.

## Methods

### The electronic cardiovascular system review

^{2}/ml). The electrical model consists of forty two elements which represent the left and right ventricles, systemic arteries and veins, and pulmonary arteries and veins. Each element consists of a conduit for viscous blood flow, which is characterized by a linear resistance and a volume storage element, which is characterized by a linear capacitor. The inertance of each element is characterized by a linear inducer. The reference pressure is atmosphere pressure (or ground) for the circuit. The energy of systolic contraction is modeled by superposition of three voltage suppliers and two ideal diodes. The voltage suppliers vary periodically over time and are responsible for driving the flow of blood in both left and right ventricles. The four ideal diodes represent the ventricular inflow and outflow valves and ensure unidirectional blood flow; furthermore the model works at the frequency of 1 Hz. We have demonstrated [10] that this model behaves reasonably in terms of pulsatile waveforms and properties of the systemic circulation.

The electrical specifications of each element. The electrical characteristics of the elements of the system with reference to the block diagram of Figure 1.

ITEM | DESCRIPTION | R(kΩ) | L(μH) | C(μF) |
---|---|---|---|---|

1 | Left Atrium | 0.5 | 0.1 | 101 |

2 | Left Ventricle | 0.5 | 0.1 | 25 |

3 | Ascending Aorta | 7.6 | 0.133 | 0.918 |

4 | Aortic Arch 1 | 0.011 | 0.144 | 0.262 |

5 | Aortic Arch 2 | 0.0265 | 0.245 | 0.489 |

6 | Right Subclavin II | 14.118 | 18.61 | 0.489 |

7 | Right Carotid | 8.14 | 9.3 | 0.167 |

8 | Right int Carotid | 159.8 | 40.4 | 0.01277 |

9 | Right ext Carotid | 160.7 | 40.6 | 0.0137 |

10 | Left Subclavin II | 14.118 | 18.61 | 0.489 |

11 | Left Carotid | 9.89 | 10.93 | 0.197 |

A | Left int Carotid | 159.8 | 40.4 | 0.01277 |

B | Left ext Carotid | 160.72 | 40.6 | 0.0137 |

12 | Thoracic Aorta 1 | 0.046 | 0.374 | 0.556 |

13 | Thoracic Aorta 2 | 0.446 | 1.642 | 0.376 |

14 | Abdominal Aorta 1 | 0.419 | 0.749 | 0.1933 |

15 | Abdominal Aorta 2 | 0.882 | 2.439 | 0.353 |

16 | Abdominal Aorta 3 | 0.1218 | 0.2661 | 0.0254 |

17 | Left Common Iliac | 2.867 | 3.135 | 0.0557 |

18 | Left External Iliac | 12.23 | 10.1 | 0.0524 |

19 | Left Femoral | 87.74 | 47.533 | 0.0906 |

20 | Right Common Iliac | 2.867 | 3.135 | 0.0577 |

21 | Right External Iliac | 12.23 | 10.1 | 0.0524 |

22 | Right Femoral | 87.74 | 47.533 | 0.0906 |

23 | Hepatic | 25.11 | 9.815 | 0.0168 |

24 | Oastric | 60.28 | 15.77 | 0.0108 |

25 | Splenic | 9.817 | 5.996 | 0.0285 |

26 | Left Renal | 6.24 | 3.4072 | 0.0125 |

27 | Right Renal | 6.24 | 3.4072 | 0.0125 |

28 | Superior Mesenteric | 1.468 | 2.244 | 0.0829 |

29 | Inferior Mesenteric | 68 | 14.058 | 0.00561 |

30 | Arterioles | 72 | 1 | 1.4 |

31 | Capillaries | 48 | 1 | 71 |

32 | Vein 1 | 9 | - | 210 |

33 | Vein 2 | 1 | 0.1 | 450 |

34 | Right Atrium | 0.5 | 0.1 | 216.45 |

35 | Right Ventricle | 0.5 | 0.1 | 150 |

C | Pulmonary Artery 1 | 1 | 0.1 | 1 |

D | Pulmonary Artery 2 | 4 | - | 1 |

E | Pulmonary Artery 3 | 8 | - | 3 |

F | Pulmonary Vein 1 | 3 | - | 27 |

G | Pulmonary Vein 2 | 1 | 0.1 | 10 |

### The applications of computational fluid dynamics method (CFD) to the modelling

#### 1) The aorta aneurysms

*r*(*x*) = *ax*^{2} + *bx* + *c* (1)

The geometry of the fusiform aneurysm is assumed by
*r*(*x*) = *a* sin *π*.*x* + *b* (2)

The a, b and c coefficients can be easily calculated by the geometrical model of each aorta section, considering the different aneurysm expansion rates, according to Figure 3. In this geometry, (R) is the tube radius of the unobstructed part, (L) is the total length of the tube and (D) is the value of the maximum posterior displacement of the aneurismal wall which is determined by expanding the tube radius (R) with the following rate
*D* = *R* + *n* (3)

The parameter (n) is 20%R, 40%R, 50%R, 70%R and 90%R representing the aneurysm expansion rate. It has been assumed that blood flow is represented by a laminar, incompressible, ideal and Newtonian fluid of constant viscosity, and density. The appropriate experimental equation for blood flow subject to the aorta artery has been expressed by Womersley [13] as a sinusoidal function, with frequency of 1 Hz,
*Q = 1.05+2.407 Sin (6.283t+0.552)+*

*2.324 Sin (12.566t-1.096) -*

*0.921 Sin (18.849t+0.7384) -*

*0.398 Sin (25.132t-0.082)* (4)

Gambit software can automatically generate a mesh for any geometry. The uniform meshes were used for each of the aorta sections with the aneurysms. The quadrilateral and mappable elements were used for the fluid domain. We have used the computational fluid dynamics method, fluent code, to compute the pressure drops of the sections with the aneurysms. The velocity waveform, expressed by equation (5) was applied at the inlet boundary of each studied section. Blood properties chosen were viscosity of 0.0035 (Pa.s) and density of 1050 (kg/m^{3}). The outlet was assumed as the zero pressure state and the inlet pressure was computed by the code. The solution method was 2D, unsteady, 1^{st}-order implicit, segregated and axisymmetric. The time step size was 0.1 (s) and typically 10–20 iterations were required per time steps. The simulation reached nearly steady state oscillation after the second cycle. The pressure difference between the inside and outside of each aorta section was recorded.

#### 2) The renal artery stenosis

The geometrical model of the renal artery with the stenosis was made using the anatomical data [11] and illustrated in Figure 3. The renal artery stenosis due to arterial dysplasia generally affects the middle and distal renal artery in the patients [8], therefore we located the hypothetical stenosis in the middle of the artery. The geometry of the renal artery stenosis is assumed by
*r*(*x*) = *ax*^{2} + *bx* + *c* (6)

*D* = *R* - *n* (7)

The parameter (n) is 20%R, 40%R, 50%R, 70%R and 90%R representing the stenosis narrowing rate. The peak systolic velocity in the renal artery averages 120 ± 12 cm/s) [8]. We assumed a simple sinusoidal function for blood velocity subject to the renal artery which is given by
*V* = *1.2 Sin(6.283t+0.552)* (8)

The parameter (V) is according to (m/s) unit and the frequency of the equation is 1 Hz. The pressure difference between the inside and the outside of the renal artery with different stenosis rates was computed and recorded using the same method which was described above in section A.

### The applications of the mathematical method to the modelling

_{0}= 7L/16, X

_{1}= 9L/16, we have

Where X_{0} = L/10 and X_{1} = 2L/3, according to the geometry in Figure 3. The total compliance of each aorta artery section with the saccular or fusiform aneurysms is given by
C
_{
total
}= C
_{
normal parts
}+ C
_{
aneurysmal parts
}

Where X_{0} = L/3 and X_{1} = 2L/3 in accordance with the geometry in Figure 4. The total compliance of the renal artery with the stenosis is also given by
C
_{
total
}= C
_{
normal parts
}+ C
_{
renal stenosis
}

### The applications of the cardiovascular electronic system to the modelling

The electronic circuit of the aorta artery, shown in Figure 2, consists of six resistors, capacitors and inducers. The computed pressure drop and the compliance of each aorta section with the aneurysms were converted to their electrical counterparts including resistance and capacitance. These new values of the resistances and the capacitances were applied to the relating part on the aorta circuit. The whole cardiovascular electronic system was run to the time, 100 s, and the results were obtained and recorded. The similar method was used to study the effects of the renal stenosis on the electronic cardiovascular system.

## Results

### 1) The aorta artery aneurysms

The results of modelling for the aortic aneurysms. The values of pressure drops (obtained by CFD), compliances (obtained by the mathematics) and final Diastolic/Systolic pressures of different sections of the aorta with the aneurysms (obtained by electrical system). Please note that the values are approximate.

Abdominal I (Dia = 12.2 mm, L = 63 mm) | ΔP | C | ΔP | C | Diastol/Systole Pressure(mmHg) (fusiform) | Diastol/Systole Pressure(mmHg) (Saccular) |
---|---|---|---|---|---|---|

20% Aneurysm | 70.34 | 0.212 | 84.3 | 0.1985 | 55–150 | 55–155 |

40% Aneurysm | 69.9 | 0.302 | 79 | 0.2038 | 55.2–149.7 | 55.3–154 |

50% Aneurysm | 69 | 0.36 | 76.4 | 0.22836 | 56–149.2 | 55.2–153 |

70% Aneurysm | 65 | 0.504 | 74.6 | 0.28677 | 56.8–148.7 | 56.1–152.1 |

90% Aneurysm | 59.5 | 0.692 | 74.1 | 0.3587 | 58–148 | 56.8–151 |

Abdominal II (Dia = 11.7 mm, L = 116 mm) | ΔP | C | ΔP | C | Diastol/Systole Pressure(mmHg) (fusiform) | Diastol/Systole Pressure(mmHg) (Saccular) |

20% Aneurysm | 83.4 | 0.4785 | 87.9 | 0.4454 | 58–158 | 57–156 |

40% Aneurysm | 75.73 | 0.805 | 85 | 0.5678 | 60–155 | 59–155 |

50% Aneurysm | 74.8 | 1.0 | 84.2 | 0.6438 | 62–152 | 60–154 |

70% Aneurysm | 62.4 | 1.385 | 83 | 0.745 | 64–148 | 61.5–152 |

90% Aneurysm | 61.5 | 2.55 | 82.1 | 1.0625 | 70–147 | 63–150 |

Abdominal III (Dia = 10.4 mm, L = 10 mm) | ΔP | C | ΔP | C | Diastol/Systole Pressure(mmHg) (fusiform) | Diastol/Systole Pressure(mmHg) (Saccular) |

20% Aneurysm | 70.4 | 0.225 | 114 | 0.03184 | 55–151 | 55–163 |

40% Aneurysm | 69.6 | 0.3099 | 110 | 0.0406 | 54–150 | 56–161 |

50% Aneurysm | 69.1 | 0.362 | 105 | 0.04603 | 53.8–149.7 | 57–160 |

70% Aneurysm | 64 | 0.489 | 100.8 | 0.0592 | 52–148 | 59–159.2 |

90% Aneurysm | 58.37 | 0.65 | 97.6 | 0.07605 | 55–146 | 60–158.3 |

Thoracic I (Dia = 20 mm, L = 52 mm) | ΔP | C | ΔP | C | Diastol/Systole Pressure(mmHg) (fusiform) | Diastol/Systole Pressure(mmHg) (Saccular) |

20% Aneurysm | 26.2 | 0.61475 | - | - | 53–135 | - |

40% Aneurysm | 23.4 | 0.846 | - | - | 54–133 | - |

50% Aneurysm | 21.9 | 0.9915 | - | - | 56–132.5 | - |

70% Aneurysm | 21.5 | 1.347 | - | - | 56.5–132 | - |

90% Aneurysm | 20.66 | 1.7984 | - | - | 59–130 | - |

Thoracic II (Dia = 13.5 mm, L = 104 mm) | ΔP | C | ΔP | C | Diastol/Systole Pressure(mmHg) (fusiform) | Diastol/Systole Pressure (Saccular) |

20% Aneurysm | 63.7 | 0.505 | - | - | 57–149 | - |

40% Aneurysm | 51.05 | 0.918 | - | - | 61–147 | - |

50% Aneurysm | 50.75 | 1.15 | - | - | 61.8–146.5 | - |

70% Aneurysm | 44.05 | 1.775 | - | - | 66–143.5 | - |

90% Aneurysm | 42.2 | 2.6259 | - | - | 68–142 | - |

### 2) The renal artery stenosis

The results of modelling for the renal stenosis. The values of pressure drops (obtained by CFD), compliances (obtained by the mathematics) and final Diastolic/Systolic pressures of the renal with stenosis (obtained by electrical system). Please note that the values are approximate.

Renal (Dia = 2.6 mm, L = 32 mm) | ΔP(Pa) Stenosis | C(ml/Kpa) Stenosis | Diastol/Systole Pressure(mmHg) |
---|---|---|---|

20% Stenosis | 7.46 | 0.01512 | 82–121 |

50% Stenosis | 17.1 | 0.0236 | 85–127 |

70% Stenosis | 75 | 0.116 | 97–148 |

90% Stenosis | 3790 | 0.136 | 145–210 |

## Discussion

We have modeled the aorta aneurysms and the renal stenosis by means of the computational fluid dynamics and mathematical methods. The results were shown for different pressure graphs in the cardiovascular electronic system. The aortic aneurysm and the renal stenosis cause hypertension which is defined as increasing of blood pulse pressure.

### 1) The aorta artery aneurysms

The aorta aneurysm expansion rate is a function not only of initial size, but also of blood pressure. This indicates that increasing pulse pressure is associated with the aneurysm expansion rate [5]. Our resulting pressure drops in the present study agree with the results in Schurink's paper [3]. Our results, Table 2, show that pulse pressure increases with the rate of both aortic aneurysms including saccular and fusiform. Furthermore, clinical investigations demonstrate that 70–90% of patients with aortic aneurysms have high blood pressure [4] and supports the clinical importance of blood pressure control in reducing the risk of rupturing in the aortic aneurysms. On the other hand, the most effective factor which controls the hypertension of the aortic aneurysms is compliance [3]. Furthermore, alerted elastic properties and a reduced concentration of aortic elastic both have been associated with the aortic aneurysms [3]. In the present study, the compliance of the aorta artery increases with the rate of the aneurysms. The clinical investigations [4] imply that an increase in the compliance at the maximum aneurysm diameter was associated with rupture or need for surgery. We have shown that the higher aneurysm rate causes more hypertension and increasing of the pulse pressure in the cardiovascular system. The clinical data reported the pulse pressure of 52.5–120 mmHg for the aortic aneurysms depending on the rate of the aneurysms [15]. Our results were compared with these data and were in good agreement with them. We have found the average increase of 85 mmHg (volt) in the pulse pressure of the abdominal I aortic aneurysms. The values are 82 mmHg for the abdominal II, 77 mmHg for the thoracic I and 85 mmHg for the thoracic II.

### 2) The renal artery stenosis

The previous studies [6–8] found a positive correlation between blood pulse pressure and the rate of renal stenosis and noted that the hypertension due to the stenosis depends to many genetic factors such as fibrillin. The investigations indicate that increasing pulse pressure is associated with the stenosis expansion rate which leads to hypertension [6]. The other clinical data [9] reported the renal systolic pressure to be 124–166 mmHg and the diastolic to be 84–108 mmHg due to the rate of the stenosis. Our modelling results, Table 3, report the significant increase in the pulse pressure due to the stenosis narrowing rate. These values have the average of 102 mmHg (volt) for diastolic and 152 mmHg (volt) for systolic. This implies that the modelling results are in a good agreement with the clinical data.

## Conclusion

In summary, our results indicate that expansion rate of the aortic aneurysms as well as the narrowing rate of the renal stenosis both are directly associated with hypertension, supporting the clinical importance of blood pressure control. We hereby stress that our model is an ideal and general model of the cardiovascular system. This electrical model proves useful for studying the pathogeneses of the cardiovascular system as discussed above.

## Notes

## Declarations

## Authors’ Affiliations

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