EP3685403A1 - Procede de simulation d'une dynamique respiratoire d'un poumon virtuel, simulateur virtuel, ensemble respiratoire - Google Patents
Procede de simulation d'une dynamique respiratoire d'un poumon virtuel, simulateur virtuel, ensemble respiratoireInfo
- Publication number
- EP3685403A1 EP3685403A1 EP18773180.7A EP18773180A EP3685403A1 EP 3685403 A1 EP3685403 A1 EP 3685403A1 EP 18773180 A EP18773180 A EP 18773180A EP 3685403 A1 EP3685403 A1 EP 3685403A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- pressure
- virtual
- lung
- respiratory
- model
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
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- G—PHYSICS
- G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
- G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
- G16H50/00—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics
- G16H50/50—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics for simulation or modelling of medical disorders
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
- A61M16/022—Control means therefor
- A61M16/024—Control means therefor including calculation means, e.g. using a processor
- A61M16/026—Control means therefor including calculation means, e.g. using a processor specially adapted for predicting, e.g. for determining an information representative of a flow limitation during a ventilation cycle by using a root square technique or a regression analysis
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- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F30/00—Computer-aided design [CAD]
- G06F30/20—Design optimisation, verification or simulation
- G06F30/28—Design optimisation, verification or simulation using fluid dynamics, e.g. using Navier-Stokes equations or computational fluid dynamics [CFD]
-
- G—PHYSICS
- G09—EDUCATION; CRYPTOGRAPHY; DISPLAY; ADVERTISING; SEALS
- G09B—EDUCATIONAL OR DEMONSTRATION APPLIANCES; APPLIANCES FOR TEACHING, OR COMMUNICATING WITH, THE BLIND, DEAF OR MUTE; MODELS; PLANETARIA; GLOBES; MAPS; DIAGRAMS
- G09B23/00—Models for scientific, medical, or mathematical purposes, e.g. full-sized devices for demonstration purposes
- G09B23/28—Models for scientific, medical, or mathematical purposes, e.g. full-sized devices for demonstration purposes for medicine
- G09B23/288—Models for scientific, medical, or mathematical purposes, e.g. full-sized devices for demonstration purposes for medicine for artificial respiration or heart massage
-
- G—PHYSICS
- G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
- G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
- G16H40/00—ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices
- G16H40/40—ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices for the management of medical equipment or devices, e.g. scheduling maintenance or upgrades
-
- G—PHYSICS
- G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
- G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
- G16H40/00—ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices
- G16H40/60—ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices for the operation of medical equipment or devices
- G16H40/67—ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices for the operation of medical equipment or devices for remote operation
-
- G—PHYSICS
- G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
- G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
- G16H50/00—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics
- G16H50/20—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics for computer-aided diagnosis, e.g. based on medical expert systems
-
- G—PHYSICS
- G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
- G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
- G16H50/00—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics
- G16H50/30—ICT specially adapted for medical diagnosis, medical simulation or medical data mining; ICT specially adapted for detecting, monitoring or modelling epidemics or pandemics for calculating health indices; for individual health risk assessment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
- A61M16/022—Control means therefor
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F2111/00—Details relating to CAD techniques
- G06F2111/10—Numerical modelling
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F2113/00—Details relating to the application field
- G06F2113/08—Fluids
Definitions
- the field of the invention relates to simulation methods and systems for training medical and paramedical personnel, in particular for the purpose of configuring respiratory assistance devices in given patients.
- the field of the invention relates in particular to the modeling of the respiratory system, a virtual lung and predefined ventilation modes.
- the field of the invention deals with simulators making it possible to generate, in particular, lung pressure and volume plots which are faithful and representative of known pathologies.
- One of the functions to be simulated is the artificial respiration of acute respiratory distress syndrome. This corresponds to the use of a ventilatory assistance machine that replaces the function of the patient who is failing the time that the causal treatment is dealing with.
- lung simulators that can interface with existing respirators so that medical staff can train or learn to adjust the different modes of operation.
- the different simulation modes do not take into account a modeling of complex pathologies or specific physiological functions of the lung, for example such as alveolar recruitment.
- the artificial lung is not compatible with all modes of ventilation and must be adapted to the individual case by case.
- the method of the invention solves the aforementioned problems.
- the objective of the method of the invention is to develop a simulation of the thoracic function of a patient thus making it possible to reproduce the pathologies and critical situations that are the clinical reality in the patient's bed.
- the method may in particular be implemented in a simulator comprising an interactive control screen, for example similar to those of the fans on the market, so that the operator tests the fan settings and observes the consequences of his choices.
- the interface will aim to provide interaction to health professionals in the field of artificial ventilation.
- the medical education of respiratory pathologies can for the most part become totally virtual and no longer require the mobilization of expensive and limited equipment in their operations and interactions.
- the invention relates to a method for simulating a respiratory dynamic of a virtual lung from a virtual lung model and at least one ventilation mode, characterized in that the method comprises:
- ⁇ a first configuration of the virtual lung model, said model comprising: o A non-linear functional relationship between an instantaneous virtual lung volume and an instantaneous virtual lung pressure;
- ⁇ said first configuration comprises determining the following parameters:
- At least one pressure considered in the breathing circuit said pressure being a resulting pressure corresponding to the pressure in the respiratory tract at the output of the virtual lung, called the output pressure, to which is subtracted a pressure internal to the virtual lung, the internal pressure of the virtual lung including muscle pressure and the pressure inside the lung;
- the muscular pressure being determined according to a respiratory adaptation model comprising an adaptation coefficient weighting the value of said muscular pressure and determined as a function of the evolution of a value of a target parameter to be reached;
- said second configuration comprising determining a given characteristic of at least a ventilation resistance of a virtual patient
- ⁇ a third configuration of at least one ventilation mode comprising determining at least one virtual breath cycle comprising at least an expiration phase and an inspiration phase, which phases being associated with a change of the condition to be air flow expelled and / or inspired, ie the outlet pressure
- the method comprises a generating at least one curve representing a plot of the pressure within the virtual lung based on the volume of the virtual lung from the set virtual lung model, the model of the respiratory system and set a mode predefined ventilation.
- the first configuration further comprises a determination:
- the invention relates to a method for simulating a respiratory dynamic of a virtual lung from a virtual lung model and at least one ventilation mode, characterized in that the method comprises:
- a first configuration of the virtual lung model comprising:
- ⁇ said first configuration comprises determining the following parameters:
- a third configuration of at least one ventilation mode comprising determining at least one virtual breath cycle comprising at least an expiration phase and an inspiration phase, which phases being associated with a change of the condition to be expelled and / or inspired air flow (Q), ie the outlet pressure,
- ⁇ the first configuration further comprises a determination:
- recruitment factor a correction factor of an admission volume
- the method comprises a generating at least one curve representing a plot of the pressure within the virtual lung based on the volume of the virtual lung from the set virtual lung model, the model of the respiratory system and set a mode predefined ventilation.
- the application of said recruitment factor generates an increase or decrease of the slope at the point of inflection of the functional relationship between the volume and the pressure of the model of the virtual lung.
- the curve Vf (P) that is to say the functional relationship between the volume and the pressure of the virtual lung model, is not entirely linear. According to one embodiment, it does not comprise a linear portion.
- the first configuration comprises:
- the functional relationship between the volume of the instantaneous virtual lung and the pressure of the instantaneous virtual lung is of the sigmoid type.
- the recruitment factor is determined according to a recruitment model comprising a configurable recruitment coefficient and dependent on a predefined value of a virtual base pressure introduced into the input of the virtual lung.
- the recruitment factor comprises:
- ⁇ a first term which is a function of the virtual base pressure introduced into the virtual lung
- ⁇ a second term which is a function of the virtual air pressure in the virtual lung and the virtual base pressure.
- the recruitment factor is expressed by a linear relationship with the pressure in the lung:
- Ci and C2 are functions of the PPEP basic pressure.
- the model of the respiratory system comprises:
- ⁇ the pressure considered in the respiratory circuit is a resulting pressure equal to the pressure in the airway at the output of virtual lung, called output pressure, from which is subtracted a pressure inside the virtual lung, the internal pressure of the virtual lung comprising a pressure muscle and pressure inside the lung;
- the muscular pressure is determined according to a respiratory adaptation model comprising an adaptation coefficient weighting the value of said muscle pressure and determined as a function of the evolution of a value of a parameter. target to reach.
- the target parameter to be reached is a target volume of the virtual lung to be reached.
- the ventilation mode is a first mode comprising an inspiration phase of the respiratory cycle configured with a constant air flow.
- the ventilation mode is a second mode comprising an inspiration phase of the respiratory cycle configured with a constant output pressure.
- the ventilation mode is a third mode comprising a breathing phase inspiration phase configured with a constant output pressure and whose phase is engaged following the detection of an output pressure threshold exceeding one predefined pressure threshold.
- the ventilation mode is a fourth mode comprising an inspiration phase of the respiratory cycle configured with an output pressure proportional to a setpoint, said setpoint being produced by measuring a physiological parameter, said physiological parameter being :
- a temporal discretization step of the model of the virtual lung and the model of the respiratory system is calculated for at least one given ventilation mode by considering at least a first respiratory phase in which the air flow expelled and / or inspired is constant and / or a second respiratory phase in which the exit pressure of the respiratory system is constant.
- the discretization step comprises an approximation of a constant value of the muscular pressure between two samples of the discretization.
- the invention relates to a computer program product comprising instructions which, when the program is executed by a computer, lead it to implement the method of the invention.
- the invention relates to a computer readable recording medium comprising instructions which, when executed by a computer, lead it to implement the method of the invention.
- the invention relates to a virtual simulator comprising at least one interface for configuring the first, second and third configurations of the simulation method, said at least one interface being defined in the same portable equipment.
- the portable equipment may be a digital tablet or a smartphone known as a smartphone.
- the equipment is a computer.
- the invention in another aspect, relates to a respiratory assembly comprising:
- an intermediate ventilation device intended to mechanically cooperate with a ventilator ventilation system (RESP) intended to assist a patient;
- a virtual lung (VIRTp) generating digital instructions corresponding to an output pressure (PAW) of a virtual respiratory system and an outgoing air flow (Q) according to a predefined respiratory cycle, the virtual lung ( VIRTp) and the breathing cycle being configured according to the method of the invention, said digital instructions controlling the intermediate ventilation device.
- PAW output pressure
- Q outgoing air flow
- FIG. 1 a block diagram of the main models and interfaces for implementing an embodiment of the method of the invention
- ⁇ Figure 2 a plot of a curve generated according to an embodiment of the method of the invention the binder lung pressure and the volume thereof;
- ⁇ Figure 3 interface of an example of a simulator of the invention.
- FIG. 5 an example of a virtual lung interfacing with an intermediate device configured to cooperate mechanically with a respirator.
- FIG. 1 illustrates the various elements for implementing an embodiment of the invention.
- Different models of data can be used to model the behaviors and evolutions of a virtual lung, a respiratory system and a virtual ventilator.
- Each model can be configured independently of each other.
- One goal is to provide accurate modeling of a patient's actual respiratory support. This modeling offers a tool to train a staff able to establish approximations between evolution curves of the breathing of virtual patients and pathologies.
- the invention makes it possible to become familiar with equipment dedicated to the respiratory assistance of a patient and the effects of the different modes of ventilation.
- a model of lung MODp makes it possible to define a virtual lung, that is to say the operation of a lung taking into account different data allowing to configure the model. It can be patient data related to age, body size, sex, etc. and / or pathology data relating to maximal exhaled volume, residual volume in the lung, lung capacity, compliance (lung elasticity) etc.
- the lung model is noted MODp in Figure 1. It is especially characterized by a curve denoted V P f (P P ) which is a non-linear function defining the evolution of the volume of the lung V P as a function of the pressure P P inside the latter. According to one embodiment, this curve is nonlinear. According to a first variant, it can be of the sigmoid type as represented in FIG. other variant, it can be approximated by a polynomial function (not shown).
- Vpf (Pp) K-Vs / (1 + e "Cs ⁇ p - ps >) + A [1]
- ⁇ Pp is the pressure in the lung at time t, also note P (t);
- ⁇ K is a factor that is deduced from a recruitment model, called a recruitment factor. It can be considered as a corrective factor of an admission volume.
- ⁇ C s represents the value of the slope of the sigmoid curve at the point of inflection P s . It can be for example expressed as a function of V s .
- ⁇ Vs represents the value of the maximum dynamic considered for a given lung, that is to say a permissible volume of air calculated between a resting point and an achievable volume value of the lung during the inspiration phase.
- ⁇ "A" represents a given constant calculated as a function of at least one data item related to the patient.
- A is determined as a function of the values of the parameters of P s , Cs and V s .
- the constant "A" may be a function of the coefficient k, for example in a linear relationship, a second degree or third degree relationship.
- An advantage of such a model is to represent a relation binding the volume and the pressure of the lung which is faithful to the behavior of a real lung.
- the sigmoid type curve makes it possible to obtain a good fidelity.
- a disadvantage solved by the model of the virtual lung of the invention is that of the inaccuracy that could generate a linear model fi an example of piecewise linear curve in different pressure zones is also shown in Figure 2.
- parameters defining the profile and the plot of the nonlinear function can simply be defined by an operator from an interface.
- the coordinates of the point of inflection at the point Ps, the value of the maximum dynamic and the slope at the point of inflection of the linear curve are sufficient to characterize a plot of the non-linear function, in particular of the Sigmoid type. This possibility offers an advantage when defining the MODp lung model.
- the abscissa axis represents the pressure, while the ordinate axis represents the volume.
- the linear curve f1 is represented in pieces in three zones ⁇ , Z2 and Z3.
- V P f (Pp) 1 The sigmoid type curve V P f (Pp) 1 is also represented in the three zones.
- the central zone Z2 also has a difference between the sigmoidal curve V P f (Pp) 1 and the linear curve f 1. Furthermore, the curve of the invention V P f (Pp) 1 makes it possible to precisely define the position of an inflection point Ps, the point Ps being a characteristic point of the sigmoid type curve.
- One advantage is to be able to take into account an appreciation of a residual volume in the lung at the neutral point of respiration in proportion to a total volume.
- the neutral point is the point of rest at the end of expiration, that is to say when there is a basic pressure imposed by the respirator, the PEP point (PPEP, VPEP).
- PEP point PPEP, VPEP
- the method of the invention makes it possible to take into account various parameterizations of a curve Vf (P), in particular curves where the pressure Ps at the point of inflection is different from 0.
- Vf curves where the pressure Ps at the point of inflection is different from 0.
- the value of the pressure Ps makes it possible in particular to configure for a given patient a type of lung model. By default this value can be determined in a configuration file on the basis of a set of predefined values corresponding to predefined profiles.
- An advantage of the definition of a point of inflection Ps of the sigmoid is to be able to parameterize in the model of the virtual lung MODp a data relating to a neutral point of respiration according to a typology of patient or pathology.
- the method of the invention comprises a possible parameterization of an alveolar recruitment data K in order to define an enriched MODp virtual lung model that is representative of certain respiratory pathologies responsible for alveolar collapse. .
- the recruitment data can be determined by a MODp recruitment model, representative of the physiological phenomenon that it induces.
- Recruitment consists of reopening collapsed lung territories in order to make ventilation more homogeneous. This recruitment is obtained by all the settings that increase the pressure in the respiratory system. This modeling can be activated or not from a control interface of the simulator when the "patient" parameters are defined.
- the recruitment leads to an increase or decrease in the slope of the curve Vf (P), said slope being called "compliance" of the lung.
- Recruitment can be modeled by a K factor whose expression is defined by the following relation:
- P can be the pulmonary pressure Pp, the outlet pressure of the respiratory system PAW OR the basic pressure PPEP.
- Ci and / or C2 are determined as a function of the base pressure P PEP.
- ⁇ Ci and C2 represent recruitment coefficients that can be normalized according to predefined values. For example, they can be normalized for a normal patient, that is, a healthy lung of an average individual, average height and age.
- ⁇ PPEP represents the minimum air pressure imposed by a virtual fan entering the respiratory system, that is, a virtual lung input.
- This PPEP pressure can be set to provide breathing assistance for some patients to ensure minimal pressure in the respiratory cycle. It aims to take into account the operation of a real fan and also a physiological phenomenon related to its application.
- the phenomenon of recruitment which is a physiological phenomenon can come for a part of the application of the pressure PPEP. This contribution to the recruitment phenomenon can be modeled taking into account the value of the pressure P PEP when it is imposed.
- a first recruitment factor ki refers to the proportion of recruitment associated with the application of PPEP pressure.
- the term ki may be a linear function of the PPEP pressure.
- k1 is to be a polynomial function of PPEP pressure. This is the proportion in the K coefficient of recruitment induced by the application of the PPEP pressure.
- a second recruitment term k2 designates a proportion of recruitment that is associated with the admission of additional air into the lung due to the application of the pressure in the lung which causes a reopening of part of the lung territories. collabés due to alveolar recruitment. This phenomenon of additional recruitment is the consequence of a double phenomenon: the inspired air increases the pressure but also reopens certain cells and increases the pulmonary capacity which causes a local decrease of the pressure.
- the second term k2 is a function of the virtual air pressure PP or the volume of air V P in the virtual lung and the virtual PPEP base pressure or its associated volume VPEP.
- V P f (Pp) 2 and V P f (Pp) 3 of FIG. 2 illustrate the consequences of taking into account the recruitment factors: a change of slope and a translation of the curve with respect to the Vpf curve.
- (Pp) 1 which does not take into account the phenomenon of recruitment. This is illustrated by the evolution of the position of the inflection points of each curve at the point P s 2 and P s 3 .
- k ⁇ of recruitment K is the part induced by the modification of the instantaneous capacity of the virtual lung. It can be modeled by a linear function of the pressure P and also take into account a coefficient involving the basic pressure PPEP, for example by a function also linear.
- V P f (P) 2 , V P f (P) 3 represent sigmoidal obtained for subjects doing recruitment.
- the absolute value of the recruitment factor K is modified to be greater than 1.
- the virtual MODp lung model therefore varies according to the applied MODK recruitment model as illustrated in Figure 2.
- the phenomenon of recruitment can lead to an increase in lung capacity but also a decrease in lung capacity, for example when the recruitment factor K is less than zero.
- the invention comprises a parameterization of the model of the lung.
- a specific interface ⁇ can be designed to adjust the different values of the MODp lung model parameters.
- This interface makes it possible to define parameters of the curve Vf (P) including the slope at the point of inflection C, the maximum capacity of the lung Vs, the pressure at the point of inflection Ps.
- the parameters can be loaded into the simulator from a configuration file. The file can be transferred or directly edited in the simulator.
- Normalized default values may be predefined to correspond, for example, to a holy subject, that is to say without a declared pathology and / or a reference subject which is representative of a nominal of an average subject of the population.
- the PPEP pressure of a virtual respirator can be set.
- the MODK recruitment model can be completely defined, in particular by the determination of the two recruitment factors ki or k2 or by the two factors of the previously defined linear relation Ci and C2.
- the recruitment K is also a function of the pressure in the lung Pp, however the relation could also be written with the pressure P calculated at another point of the system, for example PAW.
- SELECT_CONFp and SELECT_CON FR make it possible to take into account the value of a parameter and to inject it into the model. These functions can be performed using predefined values, a drop-down menu or an input field.
- the data can be entered from a touch interface, for example a digital tablet or a smartphone known as the "Smartphone".
- the data entered are used by a computer MC in order to generate with the other parameterizations a curve Vpf (P) or other plots making it possible to follow the evolution of a parameter related to the respiration
- a model of a virtual MODR breathing system may be defined in particular by a parameterization of values defining certain numerical conditions of the MODR model.
- the model of a virtual respiratory system is defined by the following relation:
- PAW-Pmus R Q + PP [3]
- PAW is the pressure exiting the respiratory system of a virtual patient, that is, the pressure measured by a virtual respirator theoretically connected to a lung.
- the PAW pressure takes into account the pressure of the respiratory system and the pressure from the physiological tubes to the entrance of the respirator.
- Pmus is the muscular pressure of the lung. It corresponds to the muscular pressure generated by a muscular effort of a patient's lung to breathe.
- Q is the flow of air expelled or inspired at the exit of the respiratory system of a virtual patient.
- Pp is the pressure in the lung.
- R is a ventilatory resistance. It can be the sum of the patient's resistance and the respirator's resistance.
- the resistance of the artificial ventilatory system of the respirator for example, the tubes, valves, and any breathing accessory present in the ventilation circuit.
- FIG. 4 represents a diagram of an electric circuit whose calculation of the potential difference at the terminals makes it possible to deduce a relation between the current I, the resistance R, a capacitance C and said difference of potentials.
- the resistance R can be likened to the respiratory resistance R (same notation), the current I to the airflow Q, the capacity to the instantaneous pulmonary pressure P P (t) and the difference of potentials to the difference of pressures at both extremal points of the PAW-Pmus respiratory system unlike circuit potentials.
- One extremal point can be considered as the lung muscle and the other point as the exit of the respiratory system.
- Vpf (Pp) K-Vs / (1 + e "Cs ⁇ p - ps >) + A [1]
- V P f (P) may be used in the present description to signify that the volume of the lung V P may be a function of a pressure measured at a given point of the ventilation circuit.
- Vf (P) we will speak more generally of a relation Vf (P) to characterize a model of a lung.
- An advantage of the respiratory model of the invention is to take into account the muscular pressure Pmus.
- the invention is also based on a modeling of the respiratory resistance of patient profiles according to their pathology (s), their age, their sex, etc.
- the model of the respiratory system of the invention takes into account a dynamic modeling of the muscular pressure Pmus. This modeling can be activated or not from a control interface of the simulator.
- An advantage of the invention is to take into account a faithful model of the muscular pressure of a patient who would be assisted by a respirator.
- One advantage is to more accurately account for phenomena actually occurring in real patients by reconstructing a couple (virtual patient; virtual respirator ⁇ that can be configured according to a given setting.
- a respirator When a patient is assisted by a respirator, he may reduce his muscular effort to breathe, especially under certain conditions relating to a given patient profile and / or a given pathology.
- a magnitude can be regulated to weight a Pmus value representative of certain cases.
- the weighted value is a gas content, which may be, for example, assimilated carbon dioxide per unit volume.
- the weighted value may be an oxygen level.
- the muscular pressure Pmus can be defined according to another variable to be regulated.
- ⁇ ⁇ Pmus (t)> is a theoretical pressure curve.
- ⁇ a (t) is an adaptation coefficient that defines the MODA muscular pressure model, particularly shown in Figure 2.
- the parameter Vcibie is a virtual physiological instruction which simulates a real phenomenon, in particular the fact real patient enslaves his muscular effort to have a certain volume. minute -1 given.
- the calculation of the lung volume may be expressed in ls -1 and may be described as follows:
- VAW-LOCAL VAW ' fresp [6]
- ⁇ fresp is the breathing frequency
- a (n) a (n-1) + 1 / faPmus ' (Vncible - Vnlocal) / Vncible [7]
- ⁇ faPmus is an adaptation factor, which makes it possible to take into account in the modeling the speed of convergence towards the target volume Vcibie.
- Pmus muscular pressure model is to simulate cases, thanks to the simulation method of the invention, related to certain pathologies or certain patient profiles in which the respirator induces a modification of the muscular pressure.
- certain modes of spontaneous ventilation estimate Pmus to deliver a respiratory assistance.
- the method of the invention as well as the simulator thus makes it possible to account for a wide variety of ventilation modes, in particular by modeling Pmus.
- respirator can illustrate many patient profiles and different situations while offering a most faithful simulation that is vis-à-vis real cases.
- the data of the muscular pressure model faPmus and Vdbie, as well as the respiratory resistance R can be entered from a touch interface, for example a digital tablet or a smartphone known as the "Smartphone". According to another example, the data can be entered in a configuration file in order to be recorded in a memory of the simulator. The data entered is used by a computer MC to generate with the other parameters a curve V P f (P P ) taking into account the respiratory model of the equation [3].
- the method of the invention comprises modeling a virtual respirator and therefore different modes of ventilation that can be configured.
- the virtual respirator can be likened to a choice of a given ventilation mode.
- a first VCmode ventilation mode can be configured. This mode is a volume controlled mode by a virtual respirator allowing to reproduce the functioning of a actual respirator in which control can be performed by adjusting the input volume.
- This mode comprises different phases each corresponding to a given moment of the respiratory cycle.
- This phase makes it possible to measure inspiratory pressure values of plateau Ppiateau.
- This phase makes it possible to evaluate the alveolar pressure of the respiratory system.
- the duration of this phase can be defined for example when setting the VCmode mode.
- a third phase of free expiration is modeled by the determination of a PAW outlet pressure of the respiratory system chosen as a constant. When the pressure at the exit of the respiratory system is imposed by the virtual respirator, it is equal to the pressure PPEP.
- the duration of this fourth phase can be set in the VCmode mode configuration.
- the second and fourth phases are optional and may or may not be implemented by the simulation method of the invention.
- An advantage of these optional steps is to enable real-time measurements.
- these phases make it possible to break down the respiratory cycle in a clear manner in order to visualize simulated phenomena, for example for training purposes.
- the second phase and the fourth phase can be configured so that the value of the setpoint relating to the respiratory frequency FR is fixed.
- the VCmode configuration comprises the definition of the following parameters:
- ⁇ Q flow rate expressed in liters per minute
- ⁇ VCE volume to be insufflated in ml
- ⁇ PPEP The value of the basic PPEP pressure imposed by the virtual respirator.
- the VCmode mode can be configured with a trigger triggering on a given pressure threshold or a given flow threshold, for example, if Pmus is different from zero.
- condition for trigger can be for example expressed as:
- An advantage of this mode is to simulate a minimum respiratory assistance punctuated by the respiratory cycle regardless of the muscle strain of the patient.
- PCmode can be configured. This mode is a pressure-controlled mode by a virtual respirator to reproduce the operation of an actual respirator in which control can be performed by adjusting the inlet pressure.
- This mode comprises different phases each corresponding to a given moment of the respiratory cycle.
- This phase makes it possible to measure values of inspiratory pressure of plateau Ppiateau.
- This phase allows to evaluate the alveolar pressure of the respiratory system.
- the duration of this phase can be set for example when setting the PCmode mode.
- a third phase of free expiration is modeled by the determination of a pressure at the outlet of the respiratory system PAW chosen as a constant when it is applied. The patient's breathing is left free. When the outlet pressure PAW of the respiratory system is imposed by the virtual ventilator, it is equal to the pressure PPEP.
- the duration of this fourth phase can be defined in the VCmode mode configuration.
- the second and fourth phases are optional and may or may not be implemented by the simulation method of the invention.
- An advantage of these optional steps is to enable real-time measurements.
- these phases make it possible to break down the respiratory cycle in a clear manner in order to visualize simulated phenomena, for example for training purposes.
- the configuration of the PCmode comprises the definition of the following parameters:
- ⁇ Ti inspiration time, expressed in seconds
- ⁇ Pc + pressure to be imposed by the virtual respirator in addition to the PPEP base pressure
- ⁇ PPEP The value of the basic PPEP pressure imposed by the virtual respirator.
- the PCmode mode can be configured with a trigger triggering on a given pressure threshold or a given flow threshold, for example, if Pmus is different from zero.
- condition for trigger can be for example expressed as:
- An advantage of this mode is to simulate a minimum respiratory assistance punctuated by the respiratory cycle regardless of the muscle strain of the patient.
- a third VSAImode ventilation mode can be configured.
- This mode is a mode controlled by the detection of spontaneous ventilation in the patient.
- an event trigger known as a trigger, is configured to trigger a mode of operation of the virtual respirator according to a given stage of the respiratory cycle.
- This mode is particularly interesting when used with a patient performing a spontaneous breathing effort, for example when he is not anesthetized in apnea or when he is able to achieve a respiratory effort.
- a first Trigger Tr + is generated, a theoretical air volume is then emitted by the virtual respirator which is configured to stop a constant pressure Pc + in the phase corresponding to insufflation.
- the constant pressure is parameterized, it is noted Pc + and it corresponds to the pressure insufflated in addition to the pressure PPEP.
- the virtual respirator controls the exchanged air.
- This mode comprises different phases each corresponding to a given moment of the respiratory cycle.
- a second trigger Tr- is configured to detect the end of the first phase.
- This second trigger can be defined for a value resulting from the maximum insufflation rate of each cycle. It is defined as a percentage of this maximum insufflation rate specific to each cycle. .
- a phase following the first phase, the so-called expiry phase is triggered free is modeled by the determination of a pressure at the outlet of the respiratory system Pc + chosen as a constant.
- the third phase ends when the trigger Tr + is triggered for a given volume of air per min, ie a given flow Ch.
- the VSAImode configuration comprises the definition of the following parameters:
- ⁇ Tr- end of insufflation trigger in [%]
- ⁇ Pc + pressure insufflated in addition to the PPEP pressure
- ⁇ PPEP The value of the basic PPEP pressure imposed by the virtual respirator. - PAVmode
- the PAVmode ventilation mode is used to rewind the ventilator setpoint to a pressure measurement in the P P or PAW patient.
- One advantage is to simulate a ventilation mode in which the respirator provides a breathing aid according to a setpoint proportional to the estimated pressure of the patient.
- PAVmode mode can be an enhanced mode of VSAImode mode with Tr + trigger trigger
- the breathing cycles may be identical to those of the VSAImode mode, that is to say the inspiration phase is carried out with a pressure or flow rate and for example a free expiration.
- VSAI can be defined.
- the duration of this phase can be defined for example when setting the mode PAVmode. It can be suspended if an insufflation is detected by the virtual patient. This pause measures the compliance of the respiratory system as well as the total resistances in order to solve the equation [3].
- the NAVAmode ventilation mode makes it possible to rewire the set point of the respirator on an electrical measurement of a muscular effort representative of a respiratory effort of the patient. It may be an electrical activity Aeie, as illustrated in FIG. 1, of the diaphragm muscle.
- An electrode for example, on the surface of a medical device can be configured to measure an electrical signal on the surface of the diaphragm. The electrical signal, depending on the level measured, can trigger and the end of a suitable instruction of the respirator.
- the inspiratory aid is synchronized with the electrical activation signal of the diaphragm.
- One advantage is to simulate a ventilation mode in which the ventilator provides an inspiratory aid according to a proportional instruction to a measured muscle electrical activity in the patient that is representative of a patient effort to engage his breathing.
- the NAVAmode mode can be an enhanced mode of the VSAImode mode with a Tr + trigger trigger.
- the initiation of the breathing cycles is defined by a certain value of electricity but may be identical to those of the VSAImode mode, that is to say the phase of triggering the inspiration is carried out with a pressure setpoint or of debt.
- the expiration is triggered when the electricity reaches a certain% of the maximum inspiratory electricity. It is followed by a free expiration.
- the choice of a ventilation mode can be determined in order to simulate a mode of operation of a respirator whose configuration is adapted to a given pathology, a given patient.
- An INTv interface can be used to define the different modes and associated parameters.
- This interface can be touch. According to one embodiment, it can be generated on the same display as the interface ⁇ .
- the functions to choose the ventilation mode and the different parameters are shown in Figure 1:
- the SELECT_CONFv function is used to define the ventilation mode
- the PARA_VCmod, PARA_PCmod, PARA_VSAImod, PARA_PAVmod, PARA_NAVAmod functions make it possible to define the parameters of each respiratory phase for each of the modes of ventilation.
- An advantage of the invention is that the method takes into account the different models and certain hypotheses in order to generate a system of equations that can be solved in real time when the simulation is started.
- equation [1] is expressed according to the different possibilities of configuration of the virtual respirator and therefore of the breathing phases corresponding to the different modes of ventilation.
- Vp (n) V P (n-1) + Qo-AT
- V A w (n) V A w (n-1) + QcrAT
- ⁇ PAw (n) R ⁇ Qo + Ppf (V P (n)) + P mU s (n)
- PAw (t) PAWO
- the method of the invention may comprise the formation of a first hypothesis of the model defining an approximation when it is close to V P (n):
- dVpf / dPp is the partial derivative of V P f with respect to the pressure Pp.
- the method of the invention may comprise the determination of a second hypothesis in the development of the model in order to obtain an efficient and faithful system and modeling the evolution of muscular pressure locally.
- PAW (n), Vp (n), Q (n), P p (n) and VAW (n) are then obtained.
- the simulator is configured to simulate the thoracic function of a patient and the function of the ventilator.
- the VIRTp simulator is configured to simulate the thoracic function of a patient to test a real RESP respirator.
- an intermediate ventilation device DISPO_INT_VENT can be used in order to be:
- the interfaces 31 with the RESP respirator then comprise physical channels for generating an air flow or aspirating an air flow according to the conditions imposed by the simulator.
- the virtual simulator and the intermediate device are in the same equipment.
- the virtual simulator comprises only the models and parameters necessary to simulate the thoracic and respiratory functions, that is to say the MODp lung model, the first CONFp configuration, the model of a MODp respiratory system. , and the second CONFp configuration, as well as the default settings or parameters to be set from the interface.
- the simulator of the invention makes it possible to model a virtual respirator, the functions making it possible to define the different modes of ventilation. A pre-configuration can be generated in the simulator so that it can be configured simply by the parameter definition in an input interface.
- the simulator includes a memory for storing the different models as well as all the default parameters.
- the simulator comprises a single INTA display for configuring the first configuration CONFp and the second configuration CON FR.
- the simulator comprises a single display for displaying the curves Vf (P) and the various control parameters that can be controlled whether those of the virtual lung or those of the virtual respirator.
- An advantage of the simulator is that it can be associated with a local database or remote server comprising data representative of a set of pathologies or critical situations that are clinical reality in patient beds.
- the data may also include typical patient profiles.
- the database is defined to group configuration parameters with given pathology contexts or given patient profiles.
- a set of differential equation system parameters can be predefined for each of the pathologies. This solution allows predefining settings to generate plots corresponding to a patient context or pathologies.
- An interest of the simulator of the invention is to understand a mathematical modeling of the movement of the lung (WP1) and the adjustment of the parameters of said model.
- a first task of this WP is to write the differential equations that govern the thoracic system, then to discretize them for use a digital solver.
- a computer such as a microprocessor can be used to perform the resolution and the discretization of the latter.
- the simulator comprises at least one calculation means MC making it possible to carry out the main calculation steps of the method.
- a specific or identical calculator for generating the curves can be used.
- the GEN TRACE function of FIG. 1 makes it possible to draw an evolution curve notably of Vp as a function Pp taking into consideration the different parameterized models.
- the parameterization or the modification of a model can be taken into account when drawing the curve dynamically so as to be able to illustrate on the same graph the different curves changing according to the modifications made.
- a programming of the evolutions of a parameterization can be carried out over a given period and over a predefined value range of the parameter in order to vary the curve in real time with the modifications of the parameterization.
- Such programming is particularly didactic and educational to illustrate causal relationships between patient or pathology modeling and physiological response.
- An advantage of using the method of the invention is to provide a simulator providing a realistic simulation of the output curves related to a given pathology or a given patient profile.
- physiological monitoring tools or adjustments are integrated into the simulator.
- the data and their interaction are calibrated from tests with comparisons to known clinical studies.
- the simulator comprises an I NTA display such as an interactive control screen.
- the interactive screen may comprise ergonomic elements similar to fans known to those skilled in the art.
- Such a simulator allows an operator to test the fan settings and observe the consequences of his choices.
- the interface provides interaction for health professionals in this field of artificial ventilation.
- Such a simulator makes it possible to dispense with the use of complex devices used.
- the method can generate all values representing a state of respiration: volume, pressure or air flow in different places such as for example at the muscle, lung, output of the lung at the level of the respiratory system or at the level of the respirator. It is therefore possible to access PAW, VAW, PP, VP, Pmus, VpEP.
- the simulator comprises selectors for selecting and configuring a display mode of the different values representative of the breathing mode.
- the pressure of the lung can be expressed in relation to the pressure of the Pmus muscle, relative to the atmospheric pressure Patm or to any other pressure.
- FIG. 3 represents an exemplary interface of the simulator of the invention comprising different zones making it possible to define a given parameterization.
- the zone 1 0 makes it possible to define parameters relating to the model of the respiratory system, including the muscular pressure Pmus.
- Zone 1 1 makes it possible to define parameters relating to the model of the respirator and therefore to the various ventilation modes whose modes: VCmode, PCmode, VSAImode, PAVmode, NAVAmode.
- Zone 1 2 makes it possible to define respirator parameters such as trigger thresholds Tr +, Tr-, constant pressure Pc + and PPEP base pressure.
- Area 13 is used to define respiratory cycle data such as respiratory rate FR, target volumes, and boundary condition parameters.
- Zone 14 provides the plot of a reference curve for obtaining a control zone of a lung volume curve V (P) as a function of the pressure of the lung P.
- V (P) a control zone of a lung volume curve
- the zones 20, 21, 22 allow the drawing of curves illustrating the evolution of certain parameters.
- the display can be configured to select or remove specific traces.
- An interest of the simulator of the invention is therefore to propose an integration of the model into a computer software, with a fan control screen interface comprising arrangements and ergonomics facilitating the handling of an operator or a user. doctor.
- the goal is to offer a unique educational tool to health professionals or the manufacturer and easy to use.
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Abstract
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FR1771004A FR3071398A1 (fr) | 2017-09-22 | 2017-09-22 | Procede de simulation d’une dynamique respiratoire d’un poumon virtuel, simulateur virtuel, ensemble respiratoire. |
PCT/EP2018/075585 WO2019057881A1 (fr) | 2017-09-22 | 2018-09-21 | Procede de simulation d'une dynamique respiratoire d'un poumon virtuel, simulateur virtuel, ensemble respiratoire |
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EP18773181.5A Withdrawn EP3685404A1 (fr) | 2017-09-22 | 2018-09-21 | Procede de simulation d'une dynamique respiratoire d'un poumon virtuel avec une modelisation de la pression musculaire, simulateur virtuel |
EP18773180.7A Withdrawn EP3685403A1 (fr) | 2017-09-22 | 2018-09-21 | Procede de simulation d'une dynamique respiratoire d'un poumon virtuel, simulateur virtuel, ensemble respiratoire |
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EP18773181.5A Withdrawn EP3685404A1 (fr) | 2017-09-22 | 2018-09-21 | Procede de simulation d'une dynamique respiratoire d'un poumon virtuel avec une modelisation de la pression musculaire, simulateur virtuel |
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US (2) | US20200312462A1 (fr) |
EP (2) | EP3685404A1 (fr) |
FR (1) | FR3071398A1 (fr) |
WO (2) | WO2019057881A1 (fr) |
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CN205068345U (zh) * | 2015-10-29 | 2016-03-02 | 合肥鑫晟光电科技有限公司 | 一种触控结构、触控屏及显示装置 |
US11428432B2 (en) * | 2018-11-20 | 2022-08-30 | Distech Controls Inc. | Computing device and method for inferring an airflow of a VAV appliance operating in an area of a building |
CN110187860B (zh) * | 2019-04-24 | 2020-10-09 | 北京声智科技有限公司 | 音量模糊调节方法、装置、电子设备及存储介质 |
CN110047594A (zh) * | 2019-05-27 | 2019-07-23 | 北京气象在线科技有限公司 | 基于气象环境监测数据的呼吸系统疾病发病趋势预测方法 |
US12033529B2 (en) * | 2019-09-27 | 2024-07-09 | Covidien Lp | Airway simulator |
CN112819390B (zh) * | 2021-03-26 | 2023-06-16 | 平安科技(深圳)有限公司 | 医疗资源规划方法、装置、设备及存储介质 |
US20230102865A1 (en) * | 2021-09-30 | 2023-03-30 | Koninklijke Philips N.V. | Digital twin of lung that is calibrated and updated with mechanical ventilator data and bed-side imaging information for safe mechanical ventilation |
CN116525118B (zh) * | 2023-03-22 | 2023-09-26 | 哈尔滨理工大学 | 平静呼吸下人体呼吸运动数值模拟系统及数值模拟方法 |
CN116911212B (zh) * | 2023-07-31 | 2024-03-19 | 中国人民解放军总医院第一医学中心 | 一种基于分数阶微积分进行呼吸系统建模的方法 |
CN117323525B (zh) * | 2023-12-01 | 2024-02-23 | 南京沪家医疗科技有限公司 | 呼吸机的压力控制方法及装置 |
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US5772442A (en) * | 1992-05-13 | 1998-06-30 | University Of Florida Research Foundation, Inc. | Apparatus and method for simulating bronchial resistance or dilation |
US5584701A (en) * | 1992-05-13 | 1996-12-17 | University Of Florida Research Foundation, Incorporated | Self regulating lung for simulated medical procedures |
SE9801175D0 (sv) | 1998-04-03 | 1998-04-03 | Innotek Ab | Metod och apparat för optimering av mekanisk ventilation med utgångspunkt från simulering av ventilatonsprocessen efter studium av andningsorganens fysiologi |
US6257234B1 (en) * | 1998-08-21 | 2001-07-10 | Respironics, Inc. | Apparatus and method for determining respiratory mechanics of a patient and for controlling a ventilator based thereon |
DE10260762A1 (de) * | 2002-12-23 | 2004-07-22 | Pulsion Medical Systems Ag | Vorrichtung zur Bestimmung kardiovaskulärer Parameter |
US7651466B2 (en) * | 2005-04-13 | 2010-01-26 | Edwards Lifesciences Corporation | Pulse contour method and apparatus for continuous assessment of a cardiovascular parameter |
US8100836B2 (en) * | 2006-12-06 | 2012-01-24 | Texas Christian University | Augmented RIC model of respiratory systems |
US11020020B2 (en) * | 2014-02-23 | 2021-06-01 | University Of Vermont And State Agricultural College | Variable ventilation as a diagnostic tool for assessing lung mechanical function |
-
2017
- 2017-09-22 FR FR1771004A patent/FR3071398A1/fr not_active Withdrawn
-
2018
- 2018-09-21 EP EP18773181.5A patent/EP3685404A1/fr not_active Withdrawn
- 2018-09-21 US US16/649,490 patent/US20200312462A1/en not_active Abandoned
- 2018-09-21 WO PCT/EP2018/075585 patent/WO2019057881A1/fr unknown
- 2018-09-21 WO PCT/EP2018/075594 patent/WO2019057887A1/fr unknown
- 2018-09-21 EP EP18773180.7A patent/EP3685403A1/fr not_active Withdrawn
- 2018-09-21 US US16/649,464 patent/US20200303080A1/en not_active Abandoned
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US20200312462A1 (en) | 2020-10-01 |
WO2019057887A1 (fr) | 2019-03-28 |
EP3685404A1 (fr) | 2020-07-29 |
WO2019057881A1 (fr) | 2019-03-28 |
US20200303080A1 (en) | 2020-09-24 |
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