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Most biomechanical tasks of interest to clinicians can be solved only using personalized mathematical models. Such models allow to formalize and relate key pathophysiological processes, basing on clinically available data evaluate non-measurable parameters that are important for the diagnosis of diseases, predict the result of a therapeutic or surgical intervention. The use of models in clinical practice imposes additional restrictions: clinicians require model validation on clinical cases, the speed and automation of the entire calculated technological chain, from processing input data to obtaining a result. Limitations on the simulation time, determined by the time of making a medical decision (of the order of several minutes), imply the use of reduction methods that correctly describe the processes under study within the framework of reduced models or machine learning tools.

Personalization of models requires patient-oriented parameters, personalized geometry of a computational domain and generation of a computational mesh. Model parameters are estimated by direct measurements, or methods of solving inverse problems, or methods of machine learning. The requirement of personalization imposes severe restrictions on the number of fitted parameters that can be measured under standard clinical conditions. In addition to parameters, the model operates with boundary conditions that must take into account the patient’s characteristics. Methods for setting personalized boundary conditions significantly depend on the clinical setting of the problem and clinical data. Building a personalized computational domain through segmentation of medical images and generation of the computational grid, as a rule, takes a lot of time and effort due to manual or semi-automatic operations. Development of automated methods for setting personalized boundary conditions and segmentation of medical images with the subsequent construction of a computational grid is the key to the widespread use of mathematical modeling in clinical practice.

The aim of this work is to review our solutions for personalization of mathematical models within the framework of three tasks of clinical cardiology: virtual assessment of hemodynamic significance of coronary artery stenosis, calculation of global blood flow after hemodynamic correction of complex heart defects, calculating characteristics of coaptation of reconstructed aortic valve.

Photosynthetic apparatus of a plant cell consists of multiple photosynthetic electron transport chains (ETC). Each ETC is capable of capturing and utilizing light quanta, that drive electron transport along the chain. Light assimilation efficiency depends on the plant’s current physiological state. The energy of the part of quanta that cannot be utilized, dissipates into heat, or is emitted as fluorescence. Under high light conditions fluorescence levels gradually rise to the maximum level. The curve describing that rise is called fluorescence rise (FR). It has a complex shape and that shape changes depending on the photosynthetic apparatus state. This gives one the opportunity to investigate that state only using the non invasive measuring of the FR.

When measuring fluorescence in experimental conditions, we get a response from millions of photosynthetic units at a time. In order to reproduce the probabilistic nature of the processes in a photosynthetic ETC, we created a Monte Carlo model of this chain. This model describes an ETC as a sequence of electron carriers in a thylakoid membrane, connected with each other. Those carriers have certain probabilities of capturing light photons, transferring excited states, or reducing each other, depending on the current ETC state. The events that take place in each of the model photosynthetic ETCs are registered, accumulated and used to create fluorescence rise and electron carrier redox states accumulation kinetics. This paper describes the model structure, the principles of its operation and the relations between certain model parameters and the resulting kinetic curves shape. Model curves include photosystem II reaction center fluorescence rise and photosystem I reaction center redox state change kinetics under different conditions.