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This is a System Dynamics Model. In order to run it you shoulld download and run it on your PC.

Oxygen delivery (DO2) to the tissues/cells and its subsequent consumption (VO2) is crucial for the body functioning and under certain circumstances, even for survival.

Physiological mechanisms and controls governing these processes are complex and non-linear with an ultimate objective to supply sufficient oxygen for maintaining an aerobic metabolism under a wide range of external and internal conditions.

This model is intended to provide a rough approximation of the essential elements of DO2/VO2 system and their interaction at a systemic level in an attempt to ensure an oxygen delivery sufficient to meet oxygen demands under a range of physiological and pathological conditions.


Human oxygen metabolism represents a complex system by which O2 from the atmospheric air is being transported to its main site of physiological use, the mitochondria. On its way to mitochondria O2 passes a number of distinct steps: airways, alveoli, alveolar-capillary membrane, then binds to hemoglobin in the red blood cells, later being transported to the tissues through vessels due to pumping activity of the heart and at the tissue level diffuses through capillary membrane to the interstitial space, then intracellular space and finally reaches mitochondria. For an effective O2 delivery there should be optimal conditions at any of these steps.

Within a broad range of O2 delivery rates, a more or less constant rate of whole-body O2 consumption (dictated by cellular requirements) is maintained. However, in certain pathological states the relationship between DO2 and VO2 can be altered and can lead to disastrous consequences, especially in critically ill patients.

Oxygen is carried in arterial blood dissolved in solution (< 2% when breathing air) and combined with hemoglobin (> 98%). Cardiac output has a crucial role in this process. DO2 can be calculated using the following formula:

DO2 = CO x (1,34 x Hb x Sa O2 + PaO2 x 0.003),

CO (L/min) – Cardiac Output;
1,34 – Hufner’s constant (the amount of oxygen (ml) 1 gram of hemoglobin binds);
Hb (g/L) – hemoglobin level;
Sa O2 (%)– the arterial Hb oxygen saturation,
PaO2 (mmHg) – arterial partial pressure of oxygen and
0.003 – solubility coefficient of oxygen. Since the latter is small the portion of oxygen dissolved in plasma is usually ignored.

In a similar way can be calculated the amount of oxygen consumed by tissues (VO2):

VO2 = CO x (1,34 x Hb x (Sa O2 - SvO2)),

where SvO2 (%) is the mixed venous Hb oxygen saturation.

Relation between DO2 and VO2 is represented by Oxygen Extraction Ratio: O2ER = VO2/DO2
Along with the above parameters (i.e. DO2, VO2, O2ER) there are additional ones which can help identifying situations when oxygen delivery is not commensurate with tissue metabolic needs. (1) Serum Lactate ≤2 mmol/L, (2) Mixed venous Hb oxygen saturation - SvO2> 65% and Arterial-venous oxygen difference - D (a-v) O2 ≤ 5mL/dL point on an oxygen supply commensurate with tissue consumption.

Oxygen delivery is responsive to (patho-) physiological changes in any of the 3 components of DO2 (Hb, oxygenation, and CO) and changes in VO2. In the case of acute hypoxia or acute anemia, CO increases to maintain normal DO2. However, there is almost no acute compensatory mechanism for acute reduction in CO. Acute reduction in DO2 due to a drop in CO (e.g., acute myocardial infarction) when VO2 is unchanged is "compensated" by greater oxygen extraction (ER), resulting in a drop in mixed venous oxygen saturation (SvO2). Oxygen delivery is also responsive to the changing metabolic needs and VO2, exemplified by the increase in DO2 when VO2 increases from rest to exercise (mediated almost completely by an increase of CO). The proportionate increase in DO2 maintains the ratio of delivery to consumption (DO2-VO2 ratio) at approximately 5:1. This DO2-VO2 ratio is high enough that cellular respiration is not supply-dependent, and VO2 is predominantly a function of tissue oxygen demand. Failure to maintain the DO2-VO2 ratio is initially compensated by increased oxygen extraction and fall in mixed venous oxygen content.

Below this critical level of DO2 (at a DO2-VO2 ratio of approximately 2:1), VO2 falls in a near-linear fashion with ensuing tissue hypoxia. The cells become almost completely reliant on inefficient anaerobic metabolism, generating adenosine triphosphate (ATP) at relatively low rates, and at the unsustainable cost of acidosis induced by unopposed ATP hydrolysis and lactic acid accumulation. ‘‘Oxygen debt’’ is accompanied by an excessive production of lactic acid, which, in the absence of oxygen, is a metabolic end product. Restoration of DO2 before irreversible tissue death repays this oxygen debt, resulting in transient increase in VO2 as DO2 is increased (producing an apparent supply-dependent increase in oxygen uptake), lactic acidosis is cleared, and organ dysfunction is reversed. In case of prolonged hypoxia irreversible cell damage will not be corrected with an increased DO2 and cellular death will occur.

This model tries to reflect DO2-VO2 relation, influenced by a number of parameters which determine DO2 - VO2 or both (e.g. CO, Hb, SaO2, SVO2, etc.). The “mathematical core” of the model is represented by the Lotka-Volterra Equations, a pair of first order, non-linear, differential equations commonly used to describe the dynamics of biological systems in which two species interact (i.e. pray and predator populations):

dX/dt = αX - βXY (1)
dY/dt = δXY - γY (2)

In this model oxygen acts as “pray” and cellular metabolic requirements as “predator/predation” as follows:

X - is the number of prey (in this model, DO2) and equation (1) deals with oxygen delivery aspects

Y - is the number of predator (in this model, VO2) and equation (2) focuses on oxygen consumption

dX/dt and dY/dt - represent the growth rates of the two entities/phenomena over time;
t - represents time;

α, β, γ, δ - are positive real parameters describing the interaction of the two entities/phenomena.

αX - represents oxygenation of blood while passing through lung (an “O2 in-flow”, which is added to DO2 stock) and the rate of predation (i.e. O2 uptake) upon the prey is assumed to be proportional to the rate at which the predators and the prey meet (in the actual model this is ‘O2 outflow", the flow which is subtracted from the DO2 stock, and represents the oxygen diffused from the tissue capillaries); this is represented by βXY, where β is denoted as DE (diffusion efficiency).

δXY - represents the growth of the predator population and in this model it is the amount of oxygen made available after diffusion from capillaries into the tissue and it is equivalent to βXY or (DO2 * VO2 * DE)

γY - represents the loss rate of the predator; in this model it is equvalent to tissue metabolic requirements represented by O2 actually consumed by cells (i.e “O2-utlization” flow calculated as VO2 * O2-UR (Utilization-Rate), not to be confounded with O2 Extraction Ratio).

Each flow is calculated in terms of the variables, and stocks that are linked to it.
As the first step in building this model there were identified “Physiologic conditions” with which equilibrium occurs in the model when neither of the population levels is changing, i.e. when both of the derivatives are equal to 0:

X ( α - β ) = 0
- Y ( γY - δX ) = 0

and Y = α / β ; X = γ / δ or VO2 = (SaO2 - SvO2)/ DE; DO2 = O2-UR / DE , excluding the solution when DO2=VO2=0

As a solution was calculated a steady-state with following parameters (CI = 3,5 L/min/m2, SaO2 = 98%, SvO2 = 77%, O2-UR = 0.977, DE = 0.00152). These variables values serve as setting parameters for “Normal” scenario.


Press the buttons:

(1) Setup: creates basic conditions for the model to run (i.e. erases data from previous runs, sets up the parameters for the selected scenario, etc.).

(2) Go: starts running the model under selected scenario, performing calculations every time-step showing results of calculations on monitors and plots.

Activating/Pressing the above buttons will run the model with initial settings (i.e. “Normal” scenario)

(3) The chooser is for selecting one of the scenarios out of a list with 7 items: Normal, Exercises without correction, Exercises with correction, Cardiogenic shock without/ or with correction, Hemorrhagic Shock without/ or with correction. The scenario should be selected before pressing ‘Setup’ and ‘Go’ buttons.

(4): The plot shows the dynamics of DO2, VO2 and DO2-VO2 difference at any particular time-step during the model run.

(5), (6), (7), (8), (9) monitors show the values of a number of model outputs and some parameters (i.e. DO2, VO2, DO2-VO2 difference, O2 Extraction Ratio and Cardiac Index) at any particular time-step during the model run.

The sliders below allow to change some of the equations parameters or variables that influence these parameters: (10) - SaO2, (11) - SvO2, (12) - Hemoglobin, (13) - Cardiac Output (Index), (14) - O2-DE (Diffusion Efficiency), (15) - O2-UR (Utilization Rate). With every of the selected scenario the sliders will be automatically adjusted according to the respective scenario settings. It is possible to adjust the sliders, except the ones for CO and Hb, during runs of the model:


At the tissue level oxygen diffuses over relatively short distances from arterioles and capillaries in all directions based on the local PO2 gradient. Oxygen diffusion is limited by oxygen solubility (k), oxygen diffusivity (D), and the PO2 gradient (dPO2/dr). The PO2 gradient drives the net movement of oxygen from a region of high PO2 to a region of low PO2. The oxygen diffusion distance is the distance from the Hb in red blood cells to the mitochondria. The critical oxygen diffusion distance, which is the maximum distance that mitochondria can be away from an oxygen source without impaired function, is determined by these oxygen diffusion parameters and by capillary PO2 and tissue oxygen consumption.

The intercapillary distance may be increased under hypoxic conditions, particularly ‘‘hypoxic’’ hypoxia (low arterial PO2) and tissue edema (increased vascular permeability or excessive fluid administration). Hence, in the microcirculation, it may be PO2 rather than DO2 (i.e., diffusion rather than convection) that is vital for local tissue oxygenation. Avoiding tissue edema by avoiding excessive fluid loading and early treatment of congestion and arterial hypoxemia may improve tissue/cellular oxygenation.
In this model the “O2 Diffusion Efficiency” (O2-DE) parameter is a ‘lump variable’ denoting the ‘diffusivity’ issue.

All scenarios in the model (except “Normal”) are present in two versions: (1) - without correction and (2) - with" correction. The first version represents a hypothetical situation when a more or less ‘sudden’ change happens in a normally functioning system (e.g. a drop in cardiac output in Cardiogenic shock after a massive myocardial infarction, or an increase in CO with exercises, or a drop in CO and hemoglobin level in Hemorrhagic shock) and the body did not react yet to these changes (denoted by normal values of other parameters (SvO2, O2-DE, O2-UR, etc.).

The version with correction includes some changes of model parameters in order to improve the system performance, in terms of DO2 and VO2 ‘physiologic normality’. (e.g. by adjusting SvO2 (decreased in shock states and with exercises); partially restoring CO by the shift of fluid from interstitial space to vascular space in hemorrhagic shock; increasing O2-DE in shock states, or decreasing it in case of exercises).

Running different scenarios one can note that this ‘correction’ seems to be efficient in case of exercises, when DO2 stability at higher than ‘resting’ values is achieved accompanied by a stable VO2 values (also higher than in ,resting’ state) with a resulting O2-ER in a normal range, between 20 and 30 percent.

In shock states this is not so efficient and although as a result of ‘correction’ the DO2 and VO2 values move toward normal there persist periods of low DO2 what request emergency treatment intervention (e.g. guided volume replacement, RBC transfusion, CO management, etc.).

Although the model captures important aspects of DO2-VO2 system it is far from “physiologic reality” at least in terms of DO2 - VO2 dynamics patterns in a particular pathology (e.g. shock) where there are probably less evident periods of ‘negative’ DO2, better illustrated by yellow-color bar plot (i.e. DO2-VO2 Difference). This aspect would be an objective for future refinement of the actual model.

O2-DE seems to be a key parameter in this model. And although not much can be done to manipulate O2 ,diffusivity’ at the moment, there might be an unexplored potential for modeling and elaboration of treatment strategies.


After choosing a scenario and pressing the setup button one will see the parameters values settings for the respective scenario on sliders. During the scenario run one can change most of these values and see the resulting effect on main model outputs. It is recommended to pay particular attention to the effect of O2-DE-slider adjustments.

Try to observe the sensitivity of the main model outputs (i.e. DO2, VO2 and their ratio) on adjusting O2-DE.

Try to find the value of the O2-DE which provides the greatest stability of the model in terms of DO2, VO2 and their ratio. For this try to adjust O2-DE after selecting a certain scenario (e.g. “Cardiogenic Shock with correction”) and running this scenario. Do the same but adjust O2-DE but before pressing “Go” button. What is the difference and how it can be explained?


Possible directions for model improvement/refinement and extension would be:
• adding new variables for “disaggregation” of ‘diffusivity parameter’
• using a more complex system of equations in order to make the model more ‘physiologically sound’
• extending the model by adding “treatment” options


This model uses the System Dynamics Modeler to simulate the Lotka-Volterra equations. Setting of the parameters specific for a certain scenario is based on the cod in the main code tab.


• Wolf Sheep Predation (System Dynamics) Model,
• Wolf Sheep Predation (Docked Hybrid) Model,
• Tabonuco Yagrumo Model, all three present in NetLogo model library


This simple abstract model was developed by Victor Iapascurta, MD. At time of development he was in the Department of Anesthesia and Intensive Care at University of Medicine and Pharmacy in Chisinau, Moldova / ICU at City Emergency Hospital in Chisinau. Please email any questions or comments to

The model was created in NetLogo 6.0.2, Wilensky, U. (1999). NetLogo. Center for Connected Learning and Computer-Based Modeling, Northwestern University, Evanston, IL. for CEEA (Committee for European Education in Anaesthesiology) Courses, Chisinau, Moldova, February 7-9, 2018 where the author of the model delivered “Mathematical modeling and computer simulation of biological processes: respiratory system” course.

Re. concerning medical aspects:
• H.S.Lim, Oxygen delivery in cardiogenic shock, Clin. Cardiol.39,8,477–483(2016) Published online in Wiley Online Library ( doi:10.1002/clc.22564
• G. Gutierrez et al., Clinical review: Hemorrhagic shock, Critical Care 2004, 8:373-381, doi:10.1186/cc2851)

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