/* * Guyton Model: Antidiuretic Hormone * * 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. * * This particular CellML model describes antidiuretic hormone * and its control functions. This section calculates the control * of antidiuretic hormone secretion and also calculates multiplier * factors for control of other aspects of circulatory function * by antidiuretic hormone. The major factors that are considered * to affect the rate of antidiuretic hormone secretion are (1) * a feedback effect of osmotic concentration in the extracellular * fluids as determined from the concentration of sodium (CNA), * and (2) a feedback effect of arterial pressure (PA). * * model diagram * * [[Image file: full_model.png]] * * A systems analysis diagram for the full Guyton model describing * circulation regulation. * * model diagram * * [[Image file: antidiuretic_hormone.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_mmHg2=5.6259564E-5 kilogram^(-2)*meter^2*second^4; 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 L_per_minute_per_mmHg=1.2501063E-7 kilogram^(-1)*meter^4*second^1; math main { realDomain time minute; time.min=0; extern time.max; extern time.delta; real CNA monovalent_mEq_per_litre; CNA=142.035; real PA1 mmHg_; PA1=103.525; real ADHNA dimensionless; real CNR monovalent_mEq_per_litre; CNR=139; real ADHNA1 dimensionless; real ADHPR dimensionless; real ADHPUL mmHg_; ADHPUL=85; real ADHPAM per_mmHg2; ADHPAM=0.3; real ADHPA mmHg_; real ADH dimensionless; real ADHINF dimensionless; ADHINF=0; real ADH1 dimensionless; real ADHC(time) dimensionless; when(time=time.min) ADHC=1.0; real ADHTC minute; ADHTC=15; real ADHMV(time) dimensionless; real ADHVUL dimensionless; ADHVUL=2.5; real ADHVLL dimensionless; ADHVLL=0.93617; real ADHMV1(time) dimensionless; real ADHMK(time) dimensionless; real ADHKLL dimensionless; ADHKLL=0.2; real ADHKUL dimensionless; ADHKUL=5; real ADHMK1(time) dimensionless; // // // ADHNA1=((CNA-CNR)/((142 monovalent_mEq_per_litre)-CNR)); ADHNA=(if (ADHNA1<0) 0 else ADHNA1); // ADHPA=(if (PA1>ADHPUL) ADHPUL else PA1); ADHPR=((ADHPUL-ADHPA)^2*ADHPAM); // ADH1=(ADHNA+ADHPR+ADHINF); ADH=(if (ADH1<0) 0 else ADH1); // ADHC:time=((ADH-ADHC)/ADHTC); // ADHMV1=(ADHVUL-(ADHVUL-1)/((ADHVLL-1)/(ADHVLL-ADHVUL)*(ADHC-1)+1)); ADHMV=(if (ADHMV1 ADHMK1=(ADHKUL-(ADHKUL-1)/((ADHKLL-1)/(ADHKLL-ADHKUL)*(ADHC-1)+1)); ADHMK=(if (ADHMK1 }