/* * Guyton Model: muscle_O2_delivery * * Model Status * * This CellML model has been validated. Due to the differences * between procedural code (in this case C-code) and declarative * languages (CellML), some aspects of the original model were * not able to be encapsulated by the CellML model (such as the * damping of variables). This may effect the transient behaviour * of the model, however the steady-state behaviour would remain * the same. The equations in this file and the steady-state output * from the model conform to the results from the MODSIM program. * * Model Structure * * Arthur Guyton (1919-2003) was an American physiologist who became * famous for his 1950s experiments in which he studied the physiology * of cardiac output and its relationship with the peripheral circulation. * The results of these experiments challenged the conventional * wisdom that it was the heart itself that controlled cardiac * output. Instead Guyton demonstrated that it was the need of * the body tissues for oxygen which was the real regulator of * cardiac output. The "Guyton Curves" describe the relationship * between right atrial pressures and cardiac output, and they * form a foundation for understanding the physiology of circulation. * * The Guyton model of fluid, electrolyte, and circulatory regulation * is an extensive mathematical model of human circulatory physiology, * capable of simulating a variety of experimental conditions, * and contains a number of linked subsystems relating to circulation * and its neuroendocrine control. * * This is a CellML translation of the Guyton model of the regulation * of the circulatory system. The complete model consists of separate * modules each of which characterise a separate physiological * subsystems. The Circulation Dynamics is the primary system, * to which other modules/blocks are connected. The other modules * characterise the dynamics of the kidney, electrolytes and cell * water, thirst and drinking, hormone regulation, autonomic regulation, * cardiovascular system etc, and these feedback on the central * circulation model. The CellML code in these modules is based * on the C code from the programme C-MODSIM created by Dr Jean-Pierre * Montani. * * The tissues of the body are divided into non-muscle tissues * and muscle tissues, and the delivery of oxygen to each one of * these is calculated separately. The principal reason for this * separation is that during muscle activity, the delivery of oxygen * to the muscles increases tremendously and correspondingly affects * the blood flow through the muscles. This particular CellML model * describes the delivery of oxygen to the muscle, and several * aspects of local cellular usage of oxygen are also calculated. * * model diagram * * [[Image file: full_model.png]] * * A systems analysis diagram for the full Guyton model describing * circulation regulation. * * model diagram * * [[Image file: m_o2.png]] * * A schematic diagram of the components and processes described * in the current CellML model. * * There are several publications referring to the Guyton model. * One of these papers is cited below: * * Circulation: Overall Regulation, A.C. Guyton, T.G. Coleman, * and H.J. Granger, 1972, Annual Review of Physiology , 34, 13-44. * PubMed ID: 4334846 */ import nsrunit; unit conversion on; unit minute=60 second^1; unit per_minute=.01666667 second^(-1); //Warning: unit mmHg_ renamed from mmHg, as the latter is predefined in JSim with different fundamental units. unit mmHg_=133.322 kilogram^1*meter^(-1)*second^(-2); unit per_mmHg=.00750064 kilogram^(-1)*meter^1*second^2; unit per_mmHg2=5.6259564E-5 kilogram^(-2)*meter^2*second^4; unit mmHg3=2.369766E6 kilogram^3*meter^(-3)*second^(-6); unit monovalent_mEq=.001 mole^1; unit monovalent_mEq_per_minute=1.6666667E-5 second^(-1)*mole^1; unit monovalent_mEq_per_litre=1 meter^(-3)*mole^1; unit monovalent_mEq_per_litre_per_minute=.01666667 meter^(-3)*second^(-1)*mole^1; unit litre2_per_monovalent_mEq_per_minute=1.6666667E-5 meter^6*second^(-1)*mole^(-1); unit L_per_minute=1.6666667E-5 meter^3*second^(-1); unit mL=1E-6 meter^3; unit mL_per_L=.001 dimensionless; unit mL_per_minute=1.6666667E-8 meter^3*second^(-1); unit L_per_minute_per_mmHg=1.2501063E-7 kilogram^(-1)*meter^4*second^1; unit mmHg_per_mL=1.33322E8 kilogram^1*meter^(-4)*second^(-2); math main { realDomain time minute; time.min=0; extern time.max; extern time.delta; real BFM L_per_minute; BFM=0.989949; real OVA mL_per_L; OVA=204.497; real HM dimensionless; HM=40.0381; real AOM dimensionless; AOM=1.00002; real O2ARTM mL_per_minute; real RMO(time) mL_per_minute; real PVO(time) mmHg_; real EXC dimensionless; EXC=1; real EXCXP2 dimensionless; EXCXP2=0.17; real OVS(time) dimensionless; real PMO(time) mmHg_; real MMO(time) mL_per_minute; real P2O(time) mmHg_; real OMM mL_per_minute; OMM=57.1; real PM5 per_mmHg; PM5=30; real QOM(time) mL; real DO2M(time) mL_per_minute; real QOM1(time) mL; when(time=time.min) QOM1=48.0839; real PK2 mmHg_per_mL; PK2=0.79167; // // // O2ARTM=(OVA*BFM); // OVS=((O2ARTM-RMO)/(HM*5.25*BFM)); PVO=((57.14 mmHg_)*OVS*EXC^EXCXP2); // P2O=(if (PMO>(38 mmHg_)) (38 mmHg_) else PMO); MMO=(AOM*OMM*EXC*(1-((38.0001 mmHg_)-P2O)^3/(54872 mmHg3))); // RMO=((PVO-PMO)*PM5*BFM); // DO2M=(RMO-MMO); QOM1:time=DO2M; QOM=(if (QOM1<(1E-4 mL)) (1E-4 mL) else QOM1); // PMO=(PK2*QOM); // }