WO2019167721A1 - Procédé d'estimation d'informations corporelles internes, programme d'ordinateur, support d'informations contenant ce dernier, et dispositif d'estimation d'informations corporelles internes - Google Patents

Procédé d'estimation d'informations corporelles internes, programme d'ordinateur, support d'informations contenant ce dernier, et dispositif d'estimation d'informations corporelles internes Download PDF

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Publication number
WO2019167721A1
WO2019167721A1 PCT/JP2019/006086 JP2019006086W WO2019167721A1 WO 2019167721 A1 WO2019167721 A1 WO 2019167721A1 JP 2019006086 W JP2019006086 W JP 2019006086W WO 2019167721 A1 WO2019167721 A1 WO 2019167721A1
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internal body
internal
model
body information
information
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PCT/JP2019/006086
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English (en)
Japanese (ja)
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正実 岩本
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株式会社豊田中央研究所
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/22—Ergometry; Measuring muscular strength or the force of a muscular blow

Definitions

  • the present invention relates to an internal body information estimation method, a computer program, a storage medium storing the computer program, and an internal body information estimation apparatus.
  • Patent Document 1 gives acceleration data of motion of a representative body part to a body model defined by data representing a rigid link representing a skeleton and data representing muscles, tendons, and ligaments.
  • a technique for calculating the generation force of muscles, tendons, and ligaments by calculation is disclosed.
  • Patent Document 2 the body surface of a numerical human body model having the structure of human internal tissue and the shape data prepared in advance and the shape of the internal tissue are deformed, and an individual obtained from a medical CT / MRI image is disclosed.
  • Patent Document 3 discloses a technique for calculating the deformation of the human body surface and the force generated on the body surface and inside using the shape deformation method of the human body model by NURBS (Non-Uniform B Spline). ing.
  • the present invention has been made to solve the above-described problems, and an object of the present invention is to improve a technique for estimating body internal information from body motion information using a body model.
  • the present invention has been made to solve at least a part of the problems described above, and can be realized as the following forms.
  • a body model information estimation method for estimating body interior information including blood pressure and muscle strength is provided.
  • This internal body information estimation method includes an input step of inputting physical motion information for causing the rigid body link model to express motion, and following the motion of the rigid body link model based on the physical motion information, A deformation calculation step of calculating a shape change, a body internal information estimation step of estimating the body internal information from a shape change of the internal body tissue using at least one of a mathematical model and a numerical analysis, and the estimated internal body An output process for outputting information.
  • the deformation calculation step of calculating the shape change of the internal body tissue following the movement of the rigid link model, and the internal body information estimation step of estimating the internal body information from the shape change of the internal body tissue are provided. Therefore, internal body information can be estimated from physical movement information.
  • the shape change of the internal body tissue is calculated by deforming the body model by FFD following the motion of the rigid body link model. Also good. According to this configuration, the shape change of the body internal tissue can be easily calculated by deforming the body model by FFD (Free (Form (Deformation).
  • the internal body information estimation step uses a mathematical model to calculate blood pressure and muscle strength of the internal body information, and by numerical analysis, At least one of a micro-calculation step of calculating vascular blood flow and nerve current amount in the internal body information may be included.
  • the internal body information can be calculated at a low calculation cost by the macro calculation process, and the accurate internal body information can be calculated by the micro calculation process.
  • the internal body information calculated by numerical analysis in the micro calculation step is calculated using the mathematical model in the macro calculation step.
  • An integration step used when calculating the internal body information may be included. According to this configuration, it is possible to improve the accuracy of internal body information calculated using a mathematical model.
  • the internal body information calculated using a numerical model in the macro calculation step is obtained by numerical analysis in the micro calculation step.
  • An integration step used as a boundary condition when calculating the internal body information may be included. According to this configuration, the calculation cost of the internal body information calculated by numerical analysis can be reduced.
  • the internal body information estimation step includes a change in the length of the muscle, a change in the length of the muscle, and a change in the length of the muscle from the specific muscle shape change calculated in the deformation calculation step.
  • a step of calculating a contraction speed and calculating the muscle strength of the specific muscle from the calculated change in the length of the muscle and the contraction speed of the muscle using a mathematical model may be included. According to this configuration, the muscle strength can be easily calculated using a mathematical model in which the relationship between the muscle length change and the muscle contraction speed and the muscle strength is shown.
  • a volume change of the left ventricle is calculated from a heart shape change calculated in the deformation calculation step, and the calculated left ventricle
  • a step of estimating the blood pressure from the volume change using a mathematical model According to this configuration, the blood pressure can be easily calculated using a mathematical model in which the relationship between the volume change of the left ventricle and the blood pressure is shown.
  • the internal body information estimation step uses a mixture model in which blood vessels and fats are configured as a single mixture of the internal body tissues.
  • a step of estimating vascular blood flow by element analysis may be included.
  • the blood vessel blood flow rate can be calculated by obtaining a solution of the equilibrium equation for each time step in a mixture including blood vessels and fat.
  • the present invention can be realized in various modes.
  • a computer program for causing a computer to execute internal body information estimation apparatus, a body internal information calculation system, a body internal information estimation method, and a body internal information estimation method It can be realized in the form of a storage medium storing this.
  • FIG. 1 is an explanatory diagram illustrating the configuration of the internal body information estimation device 10 according to the first embodiment.
  • the internal body information estimation apparatus 10 is a computer system that estimates mechanical / electrochemical information (internal body information) in the body from body motion information by simulation using a body model.
  • the internal body information estimation device 10 includes an arithmetic processing device, a storage device, and an input / output device. When the arithmetic processing device executes a program stored in the storage device, two internal calculation units (body An exercise following deformation calculation unit 12 and an internal body information calculation unit 13) are configured.
  • the storage device stores data representing various body models (rigid body link model, musculoskeletal model, human body model, mixed method model, etc.) described later.
  • the body internal information estimation device 10 includes a body motion information input unit 11, a body motion follow-up deformation calculation unit 12, a body internal information calculation unit 13, a body internal information calculation unit, a storage device, and an input / output device.
  • An information output unit 14 is configured.
  • the body movement information input unit 11 is configured by an input device and receives body movement information.
  • the body movement information is information that can specify a person's movement trajectory in a predetermined period. For example, time history data such as position coordinates, speed, and acceleration of each part of a person, time history data of muscle activity, etc. included.
  • time history data such as position coordinates, speed, and acceleration of each part of a person, time history data of muscle activity, etc. included.
  • the body movement follow-up deformation calculation unit 12 expresses body movement using the body movement information input to the body movement information input unit 11 and deforms the body internal / external tissue (skin, muscle, blood vessel) following the movement. , Nerve, etc.) shape change.
  • the skin, muscles, and blood vessels that follow the rigid link model during physical motion and are associated with the rigid body part (for example, the humerus) of the rigid link model Move the internal and external tissues such as nerves to change their shape.
  • Examples of the method for changing the shape include FFD (Free Form Deformation) and NURBS (Non-Uniform Rational B-Spline) used in the computer graphics field.
  • FFD Free Form Deformation
  • NURBS Non-Uniform Rational B-Spline
  • the internal body information calculation unit 13 calculates the internal body information based on the shape change during deformation of the internal and external tissues calculated by the body movement follow-up deformation calculation unit 12.
  • the internal body information is mechanical information or electrochemical information inside the body, and examples thereof include muscle strength, blood flow, blood pressure, nerve current, stress, and strain. These calculation methods will be described later.
  • the internal body information output unit 14 includes an output device, and outputs the internal body information obtained from the internal body information calculation unit 13.
  • FIG. 2 is an explanatory diagram illustrating the rigid link model 20 stored in the storage device.
  • the rigid link model 20 is modeled by using a human body bone as a rigid link 21 and a human body joint as a joint 22.
  • the body motion follow-up deformation calculation unit 12 (FIG. 1), for example, outputs motion data (position, velocity, acceleration) of each joint or feature point position measured by motion capture or the like to the rigid body link model 20. By giving the time history data of the feature point positions, it is possible to express physical movement.
  • FIG. 3 is an explanatory diagram illustrating the whole body of the human body model 30.
  • FIG. 4 is an explanatory diagram illustrating the arm portion of the human body model 30.
  • FIG. 5 is an explanatory view illustrating the vicinity of the chest of the human body model 30.
  • 3 to 5 includes a bone 31, a joint 32, a skin 33, a muscle 34, a blood vessel 35, a nerve 36, and a heart 37.
  • FIG. 3 shows a bone 31, a joint 32, and a blood vessel 35 in the human body model 30.
  • FIG. 4 shows muscles 34, blood vessels 35, and nerves 36 in the arm part (arm model) 30 a of the human body model 30.
  • FIG. 5A shows a bone 31, skin 33, and heart 37 in the chest of the human body model 30.
  • FIG. 5B shows a left ventricle 37a, a right ventricle 37b, a coronary artery 35a, and an aorta 35b of the heart 37 of the human body model 30.
  • the bone 31 and the joint 32 of the human body model 30 are associated with the link 21 and the joint 22 of the rigid body link model 20 (FIG. 2), respectively.
  • the skin 33, muscle 34, blood vessel 35, nerve 36, and heart 37 of the human body model 30 are associated with the link 21 of the rigid link model 20.
  • the body movement follow-up deformation calculation unit 12 (FIG. 1), for example, expresses body movement by the rigid body link model 20, the skin 33, muscle 34, muscle 34 of the human body model 30 associated with the link 21 of the rigid body link model 20.
  • the blood vessel 35, the nerve 36, and the heart 37 can be deformed by FFD or the like described later.
  • FIG. 6 is an explanatory diagram illustrating the musculoskeletal model 40
  • FIG. 7 is an explanatory diagram illustrating a correspondence relationship between the human body model 30 and the musculoskeletal model 40.
  • an arm model 30 a that is a part of the human body model 30 and a muscle model 41 that constitutes a part of the musculoskeletal model 40 are shown.
  • the musculoskeletal model 40 of FIG. 6 can be created from the human body model 30 of FIG. Specifically, as shown in FIG.
  • a musculoskeletal model 40 can be created by creating a muscle model 41 modeled as a connecting straight line or curve and adding it to the rigid link model 20 of FIG. As described above, the musculoskeletal model 40 is associated with the rigid body link model 20, and the muscle model 41 of the musculoskeletal model 40 is calculated based on the muscle activity and the muscle control algorithm estimated by electromyography. By giving time history data on the degree of muscle activity, physical movement can be expressed.
  • FIG. 8 is an explanatory diagram showing the bending of the arm model 30a by FFD.
  • the entire arm model 30a which is a part of the human body model 30, is surrounded by the FFD lattice 71, and the arm can be bent by applying a rotational motion to the forearm around the elbow joint.
  • the body motion following deformation calculation unit 12 expresses the body motion by the rigid link model 20 (FIG. 2)
  • the FFD is associated with changes in the position and posture of the link 21 and the joint 22 at each time step. Deform the lattice.
  • this simulation for example, it is possible to calculate a change in muscle length and a change in cross-sectional area of the muscle during and before exercise.
  • FIG. 9 is an explanatory diagram showing torsional deformation of the heart model 37 by FFD.
  • the heart model 37 that is a part of the human body model 30 also represents the left ventricle 37a inside.
  • the body movement following deformation calculation unit 12 (FIG. 1) can calculate the change in the volume of the left ventricle by simulating the shape change of the heart model 37 using FFD.
  • FIG. 10 is an explanatory diagram showing the configuration of the internal body information calculation unit 13. Here, a method for calculating internal body information by the internal body information calculation unit 13 will be described.
  • the internal body information calculation unit 13 includes a macro calculation unit 131 and a micro calculation unit 132.
  • the macro calculation unit 131 calculates the mechanical and electrochemical information for each part in the body by macro calculation from the shape change at the time of deformation of the internal and external tissues calculated by the body movement following deformation calculation unit 12.
  • the macro calculation unit 131 can calculate, for example, muscle strength, blood flow, blood pressure, force on bones, and the like using an integrated mathematical model of the musculoskeletal system and the circulatory system. This macro calculation can be used for repeated calculation of learning because it can simulate body movements and heart movements at a low calculation cost.
  • the micro-calculation unit 132 calculates mechanical / electrochemical information for each body tissue by micro-calculation from the shape change at the time of deformation of the internal and external tissues.
  • the micro calculation unit 132 performs numerical analysis (such as finite element analysis) to determine, for example, vascular blood flow, nerve current, stress / strain acting on muscles / blood vessels / nerves, muscle cross-sectional area change, neurotransmitter concentration, and the like. Can be calculated.
  • This micro-calculation can be used to accurately obtain information such as forces acting on blood vessels and nerves, detailed deformation shapes of each tissue, blood flow, and nerve transmission.
  • macro calculation a calculation example of muscle strength, blood flow, and blood pressure using an integrated mathematical model of the musculoskeletal system and the circulatory system will be described.
  • micro-calculation a calculation example of vascular blood flow and nerve current using finite element analysis by a mixing method will be described. Note that both macro calculation and micro calculation may be used while interpolating each other. This is illustrated in the second embodiment.
  • Equation (1) PCSA M is a muscle cross-sectional area, and here, it is assumed that each muscle has a constant value.
  • ⁇ M is muscle activity and takes a value of 0 to 100%.
  • ⁇ M max is a coefficient representing the maximum muscular strength per unit muscle cross-sectional area.
  • F CE, L (L M ) is a relational expression between active muscle strength and muscle length.
  • L M is the normalized muscle length at the natural length of the muscle.
  • F CE, V (L M , L * M ) is a relational expression between active muscle strength and speed.
  • L * M is the muscle contraction rate normalized by the maximum contraction rate.
  • F PE (L M ) is a relational expression between passive muscle strength and muscle length.
  • strength F M can be expressed by the product of the Sujidan area PCSA M, the muscle stress is the force per unit area.
  • the first term in ⁇ indicates active muscle stress, and the second term indicates passive muscle stress.
  • Each muscle stress is expressed as a product of its maximum value ⁇ M max (assuming constant for each muscle type, human: 5 g / cm 2 ) and variables related to muscle length and muscle contraction speed.
  • F CE, L (L M ) depends on changes in muscle length.
  • F CE, V (L M , L * M ) depends on the contraction speed of the muscle.
  • F PE (L M ) depends on changes in muscle length.
  • ⁇ M can be estimated separately from a muscle control algorithm and electromyography measurement data.
  • muscle strength F M can be calculated by a function that varies in length and muscle, and muscle contraction speed and variable.
  • the muscle length change and the muscle contraction speed for each time step are obtained by measuring the muscle length after flexing of the arm obtained from the musculoskeletal model 40 or the FFD deformation calculation in the body movement following deformation calculation unit 12. be able to.
  • the method of bending the arm by the FFD deformation calculation is as described in FIG.
  • the muscle model is given a time history data of the muscle activity to contract the muscle, or the muscle link is bent by giving motion trajectory data to the rigid link model that is the skeleton part.
  • the length of can be changed.
  • the body internal information calculation section 13 can calculate the strength F M from the body of the deformation calculated by the body motion tracking deformation calculation unit 12.
  • the macro calculator 131 of the internal body information calculation unit 13 calculates the blood flow volume and blood pressure using a mathematical model from the shape change at the time of deformation of the internal and external tissues calculated by the body movement follow-up deformation calculation unit 12 will be described. To do.
  • the macro calculator 131 can calculate the arterial blood pressure P (t) by the following equation (2).
  • the cardiac output Q (t) can be calculated by the following equation (3).
  • R peripheral vascular resistance.
  • ⁇ is the compliance of the aorta and is a constant here.
  • ⁇ is the cardiac output (ml) per minute.
  • T is the cardiac cycle.
  • the cardiac output Q (t) (ml / s) at time t can be obtained from the time series change f (t / T) of the left ventricular volume. That is, Q (t) can be calculated from the volume change of the left ventricle 37a accompanying the shape change at the time of deformation of the heart model 37 (FIG. 9) using FFD by the body movement follow-up deformation calculation unit 12. From the above, the internal body information calculation unit 13 can calculate the blood pressure P (t) and the cardiac output Q (t) from the heart deformation calculated by the body movement follow-up deformation calculation unit 12.
  • vascular blood flow and nerve current A method in which the micro-calculation unit 132 of the internal body information calculation unit 13 calculates the vascular blood flow volume and the nerve current amount by numerical analysis from the shape change at the time of deformation of the internal and external tissues calculated by the body movement follow-up deformation calculation unit 12. explain. Here, the finite element analysis by the mixing method using the model for the mixing method shown in FIG. 11 will be described.
  • FIG. 11 is an explanatory view illustrating a cross section Sa of the human arm and the arm model 50 for the mixing method.
  • skin 53, muscle 54, and bone 51 are arranged on the cross section Sa of the arm, respectively, and fat 52, nerve 56, and blood vessels are placed in the gaps between skin 53, muscle 54, and bone 51.
  • the mixture 57 containing 55 is arrange
  • the muscle 54 includes a humerus 541, a biceps 542 (long head 542a and short head 542b), and a triceps 543 (long head 543a, outer head 543b, and inner head 543c). Yes.
  • the bone 51 is a humerus.
  • the skin 53, the muscle 54, and the bone 51 are each configured as a mesh-divided model by the finite element method, and the fat 52, the nerve 56, and the blood vessel 55 are one
  • the mixture 57 is configured as a model (mixture model) obtained by mesh division by a finite element method.
  • the internal body information calculation unit 13 gives the positions of bones, muscles, and skin obtained from the FFD deformation result of the arm model 30a to the mixing method arm model 50.
  • bone, muscle, and skin shape data obtained from the FFD is applied to the mixing method arm model 50 using a technique such as morphing.
  • the internal body information calculation unit 13 performs normal finite element analysis at each time step on the bone 51, muscle 54, and skin 53 included in the arm model 50 for the mixing method.
  • the mixture 57 of fat 52, nerve 56, and blood vessel 55 is analyzed using a mixing method based on the three-phase theory described below.
  • the technique of Non-Patent Document 2 can be adopted.
  • Equation (4) is the equilibrium equation of the mixture
  • Equation (5) is the solid compression equation
  • Equation (6) is the fluid equilibrium equation
  • Equation (7) is the mixture compression equation
  • equation (8) is an ion equilibrium equation
  • equation (9) is an electrical neutral condition.
  • the unknown variable at each node of the mesh is the solid phase displacement (3 degrees of freedom) u, the fluid relative velocity (3 degrees of freedom) Q w , the solid phase pressure (1 degree of freedom) ⁇ S , It is assumed that the pressure (one degree of freedom) of the mixture is ⁇ m , the concentration (9 degrees of freedom) of four types of ions and five types of metabolites is c ⁇ , and the potential (one degree of freedom) is ⁇ .
  • ⁇ is a reference arrangement based on the solid phase before deformation.
  • F is a deformation gradient.
  • S is the second Piola-Kirchhoff stress of the mixture.
  • J is the volume change rate.
  • ⁇ s is the bulk modulus of the solid phase.
  • c ⁇ is the molar concentration of ion ⁇ .
  • c tot is the sum of the ion molar concentrations.
  • c F is the static charge per unit fluid volume.
  • z is the valence of the ion.
  • ⁇ is an electrostatic potential.
  • phi w is the ratio of the fluid in the mixture.
  • D ⁇ is the diffusion coefficient of ions ⁇ .
  • K is a water permeability coefficient (reciprocal of friction coefficient between fluid and solid).
  • ⁇ is the penetration coefficient.
  • R is a gas constant.
  • T is the
  • Q is an internal force vector
  • F is an external force vector
  • the unknown vector X can be calculated by solving this governing equation.
  • the dynamics, potentials, and ion reactions have different time scales and the frequency to be updated is different. Therefore, four mechanical mechanical variables (two Lagrange undetermined multipliers for displacement, flow velocity, and pressure), potentials, and ions can be expressed as the following formula (11).
  • a mixing method based on a two-phase theory using only a solid phase and a fluid phase may be employed.
  • the process of neurotransmission from the nerve axon through the synapse to the next cell by chemical transmission can be modeled with ions, when modeling this part, the three-phase theory including the ionic phase A method using a mixing method is preferably used. Thereby, the potential field can also be calculated from the change of the ions.
  • the body motion following deformation calculation unit 12 calculates the shape change of the body internal tissue following the body motion of the rigid link model 20, Since the internal information calculation unit 13 estimates the internal body information by macro calculation or micro calculation from the shape change of the internal body tissue, the internal body information can be estimated from the body movement information.
  • the body internal information calculating unit 13 uses a mathematical model, a macro calculation unit 131 for calculating the blood pressure P and strength F M of the internal body information
  • the macro internal unit 131 can calculate the internal body information at a low calculation cost, Accurate internal body information can be calculated by the micro calculator 132.
  • the internal body information and the human body model on the computer are obtained from the internal body information that is difficult to measure with the existing body measurement apparatus while the body is stationary or in motion. It can be obtained by a calculation program that gives the body function.
  • a calculation program that gives the body function.
  • the deformation of the internal tissues of the body such as the muscles of the upper arm, blood vessels, and nerves associated with flexion and extension movements in the joints, and the stress / strain state of each tissue at that time, the blood vessels and nerves
  • the amount of transmission, muscle strength, etc. can be calculated.
  • changes in the shape of internal tissues such as muscles, blood vessels, and nerves, stress and strain of each tissue, blood and nerve transmission, aortic blood pressure, etc. It can be calculated.
  • the internal body information estimation apparatus 10 of the present embodiment it is possible to visualize not only muscle load and joint load due to exercise, but also the load on the entire body during physical exercise such as heart rate rise, blood pressure, respiratory change, and the like. Therefore, it can be used for strengthening the development of sports athletes, rehabilitation support for patients with various diseases including respiratory and circulatory systems, and walking support for the elderly.
  • it is possible to calculate internal body information that is difficult to measure with an existing body measurement device at a low calculation cost it is easy to repeatedly use it for learning, and a neural network model incorporating internal body information can be easily constructed.
  • FIG. 12 is an explanatory diagram illustrating the configuration of the internal body information calculation unit 13A according to the second embodiment.
  • the internal body information calculation unit 13A of the second embodiment is different from the internal body information calculation unit 13 of the first embodiment in that an integration unit 133 is further provided.
  • the integration unit 133 uses the internal body information from the macro calculation unit 131 and the internal body information from the micro calculation unit 132 while interpolating each other.
  • the integration unit 133 can supply the internal body information from the macro calculation unit 131 to the micro calculation unit 132 and use it for the boundary condition of the micro calculation.
  • the internal body information from the micro calculation unit 132 can be given to the macro calculation unit 131 and used as physical property parameters of the macro calculation formula.
  • the muscle cross-sectional area PCSA M is a constant value when the macro calculation unit 131 calculates the muscular strength using the equation (1).
  • the integration unit 133 performs the macro calculation on the muscle cross-sectional area A calculated by the micro calculation unit 132.
  • the macro calculation unit 131 uses the Sujidan area A microphase calculating unit 132 is calculated as Sujidan area PCSA M of formula (1).
  • the micro-calculating unit 132 uses the arm model 50 for mixing method (FIG.
  • the muscle and skin of the arm model 50 for the mixing method are modeled with a material such as a superelastic body, the muscle deformation can be calculated in consideration of the influence of the fluid phase such as blood, so that the muscle cross-sectional area can be calculated more accurately. A can be obtained. Also, when analyzing the deformed state of the arm by the finite element analysis of the mixed method, unlike the case of deforming the arm by FFD, it is difficult for the muscle to penetrate into the bone at the time of deformation. It can be said that the muscle cross-sectional area A can be calculated.
  • FIG. 13 is an explanatory view illustrating the pterygium 64.
  • the muscle cross-sectional area PCSA M in Expression (1) is a cross-sectional area in the direction of the muscle fiber, and therefore, Acos ⁇ , which is a cross-sectional area considering the wing angle ⁇ , is more preferable.
  • the wing angle can be calculated with reference to the muscle running of the anatomical chart from the three-dimensional detailed deformation state of the muscle, so that the muscle strength can be calculated with higher accuracy.
  • the micro calculation unit 132 analyzes not only the force / stress / strain applied to the muscles and bones but also the force / stress / force applied to the blood vessels and nerves by the analysis using the above-described mixed method arm model 50 (FIG. 11B). Strain and blood flow can also be calculated.
  • the integration unit 133 may give the result of the macro calculation by the macro calculation unit 131 to the micro calculation unit 132. Thereby, the accuracy of the calculated value can be improved.
  • the integration unit 133 uses the bone and muscle force and blood flow information obtained from the macro calculation by the macro calculation unit 131 as information on the bone and muscle force and blood flow rate (boundary condition) on the boundary surface of the mixed method arm model 50.
  • the micro calculation unit 132 May be input to the micro calculation unit 132. If the time series change of the shape of the bone and muscle is given to the micro calculation unit 132, the calculation of the mixed method finite element analysis becomes only the fat layer, blood vessel, and nerve portion, and the calculation amount of the micro calculation unit 132 can be reduced. it can.
  • the integration unit 133 calculates the aortic compliance Cw calculated by the micro calculation unit 132 and the peripheral vascular resistance R. You may give p to the macro calculation part 131.
  • the macro calculation part 131 can use the compliance Cw of the aorta calculated by the micro calculation part 132 as the compliance ⁇ in the equation (2).
  • the compliance ⁇ of the aorta and the peripheral blood vessel resistance R are constant.
  • the aortic compliance Cw is the maximum value A max of the cross-sectional area of the aorta at the time of systolic blood pressure, the effective length l of the artery, and the vicinity of each of the contraction and dilation of the heart. Affected by intracardiac blood pressure p.
  • the intracardiac blood pressure p in the above equation (12) and the peripheral vascular resistance R in the equation (2) are affected by the concentration Cv NE of the neurotransmitter norepinephrine (noradrenaline) in the periphery as described below. receive.
  • the intracardiac blood pressure p and the peripheral vascular resistance R are diastolic blood pressure defined by the equation (15) as shown in the following equations (13) and (14). It is a function of the factor ⁇ v (t) that determines As shown in equations (15) and (16), this factor ⁇ v (t) is influenced by the concentration Cv NE of the neurotransmitter norepinephrine in the periphery. From this, it can be seen that the intracardiac blood pressure p and the peripheral vascular resistance R are influenced by the concentration Cv NE of the neurotransmitter norepinephrine in the periphery.
  • ⁇ v NE is constant
  • the weight of the k s CvNE mother sympathetic activity v s is a time lag.
  • the cross sectional area A of the aorta, the effective length l of the aorta, and the concentration Cv NE of the neurotransmitter norepinephrine are known, the peripheral vascular resistance R and the compliance ⁇ of the aorta can be obtained, and the blood pressure can be calculated more accurately.
  • the maximum value A max of the cross-sectional area of the aorta at the time of systolic blood pressure and the effective length l of the artery indicate the characteristics of aortic extensibility and volume change.
  • the aortic compliance ⁇ indicates the amount of increase in blood vessel volume with respect to an increase in unit pressure.
  • the peripheral vascular resistance R is related to the hardness of the blood vessel. That is, by obtaining the peripheral vascular resistance R and the aorta compliance ⁇ as described above, the hardness of the blood vessel can be taken into consideration, and the prediction accuracy of blood pressure can be improved.
  • the cross-sectional area A of the artery and the effective length l of the artery can be calculated by taking into account the contraction of the blood vessel, by calculating the deformation of the three-dimensional aorta by FFD and the mixing method.
  • the neurotransmitter norepinephrine concentration Cv NE can be calculated by a mixing method. Therefore, the peripheral vascular resistance R and the aortic compliance ⁇ can be calculated from the FFD and the mixing method, and the arterial blood pressure P with higher accuracy can be calculated.
  • the norepinephrine concentration Cv NE can be calculated, for example, by treating the ionic phase in the mixed-arm model 50 taking into account neurotransmission up to synaptic transmission.
  • the norepinephrine concentration Cv NE is affected by the activity of the sympathetic nerve and the time delay.
  • the integration unit 133 of the internal body information calculation unit 13A performs the internal body information from the macro calculation unit 131 and the internal body information from the micro calculation unit 132. Since these are used while interpolating each other, the calculation cost can be reduced while improving the accuracy of the internal body information.
  • the integration unit 133 can give the internal body information calculated by the macro calculation unit 131 using the mathematical model to the micro calculation unit 132 and can use it for the boundary condition of the micro calculation. Thereby, the calculation cost of the internal body information calculated by numerical analysis can be reduced.
  • the internal body information calculated by numerical analysis by the micro calculation unit 132 can be given to the macro calculation unit 131 and used for the physical property parameter of the macro calculation formula. Thereby, the precision of the internal body information calculated using a mathematical model can be improved.
  • the example of the micro calculation by the macro calculation unit 131 and the example of the macro calculation by the micro calculation unit 132 shown in the first and second embodiments are examples thereof, and the inside of the body estimated by the macro calculation unit 131 or the micro calculation unit 132
  • the information is not limited to the content exemplified in this embodiment.
  • internal body information may be calculated using a mathematical model described in Non-Patent Document 1, or a numerical analysis method described in Non-Patent Document 2 may be employed.
  • the integration unit 133 shown in the second embodiment includes the muscle strength and blood pressure calculated by the macro calculation unit 131, the muscle stress and strain calculated by the micro calculation unit 132, the blood flow rate of blood vessels, the flow velocity, the pressure, Internal body information such as joint angle, muscle stretch, blood pressure, heart rate, etc. may be calculated from the amount of nerve current and the ion transmission speed.
  • the arm model 50 was illustrated as a model for mixing methods.
  • the model for the mixing method can be created for any part of the body. That is, the internal body information calculation unit 13 can estimate internal body information about an arbitrary part of the body.
  • human body internal information is estimated using a human body model.
  • the body internal information estimation device 10 uses the model of an arbitrary living creature other than a human to calculate the internal body information of the living creature. Can be estimated.
  • the internal body information estimation device 10 of the first embodiment has been described on the assumption that the rigid link model 20, the human body model 30, the musculoskeletal model 40, and the arm model 50 for the mixing method are stored in the storage device. However, these models are examples, and some of these models may not be stored, and other models may be stored.
  • the internal body information estimation apparatus 10 may have a function of creating a necessary body model each time when calculating internal body information.
  • the internal body information calculation unit 13 includes a macro calculation unit 131 and a micro calculation unit 132. However, the internal body information calculation unit 13 may include only one of the macro calculation unit 131 and the micro calculation unit 132.
  • the internal body information estimation apparatus 10 can simultaneously perform macro calculation by the macro calculation unit 131 and micro calculation by the micro calculation unit 132 at each time step, or perform only macro calculation or only micro calculation. You can also. In addition, it is possible to repeatedly perform calculation for simultaneous calculation of macro calculation and micro calculation, and to use the results of a plurality of body parts (upper limbs, lower limbs, internal organs, etc.). Thereby, it is possible to improve the calculation accuracy of each of the macro calculation and the micro calculation.

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  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

L'invention concerne un procédé d'estimation d'informations corporelles internes destiné à estimer des informations corporelles internes, notamment la pression artérielle et la force musculaire, à l'aide de données provenant d'un modèle de liaison rigide représentant une structure squelettique, et de données provenant d'un modèle de corps conçu au moyen d'un modèle de systèmes corporels internes associés au modèle de liaison rigide comprenant des os, des muscles, des vaisseaux sanguins et un cœur, ledit procédé comprenant : une étape d'entrée consistant à entrer des informations de mouvement corporel afin d'exprimer un mouvement dans le modèle de liaison rigide ; une étape de calcul de déformation consistant, sur la base des informations de mouvement corporel, à suivre un mouvement dans le modèle de liaison rigide et à calculer un changement de forme dans les systèmes corporels internes ; une étape d'estimation d'informations corporelles internes consistant à estimer des informations corporelles internes à partir du changement de forme dans les systèmes corporels internes, à l'aide d'un modèle mathématique et/ou d'une analyse numérique ; et une étape de sortie consistant à délivrer en sortie les informations corporelles internes estimées.
PCT/JP2019/006086 2018-03-02 2019-02-19 Procédé d'estimation d'informations corporelles internes, programme d'ordinateur, support d'informations contenant ce dernier, et dispositif d'estimation d'informations corporelles internes WO2019167721A1 (fr)

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JPS6449540A (en) * 1987-08-19 1989-02-27 Toshimitsu Musha Simulator for cardiac electric phenomenon
JP2002186588A (ja) * 2000-12-22 2002-07-02 Pasuko:Kk 人体数値管理システム及び人体モデリングシステム
WO2006000789A1 (fr) * 2004-06-25 2006-01-05 Imperial Innovations Ltd. Procede de correlation du mouvement de tissus internes
JP2013534154A (ja) * 2010-08-12 2013-09-02 ハートフロー， インコーポレイテッド 患者固有の血流のモデリングのための方法およびシステム
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