Kinematics and dynamics index output method based on human body model

Abstract

The invention relates to the technical field of finite element modeling, in particular to a kinematics and dynamics index output method based on a human body model, which comprises the following steps of: S1, establishing acceleration modules at the head, the chest, the hip and the lower limbs of the human body model for global and local acceleration and angular velocity output; s2, building displacement modules at the chest, abdomen, knee joints and achilles tendons of the human body model, wherein the displacement modules are used for outputting the compression amount and the elongation amount; and S3, establishing section force modules at the spine, crista iliaca, femur and tibia of the human body model for outputting local force and torque. According to the scheme, the technical problem that kinematics and dynamics indexes of the human body model cannot be effectively extracted in the prior art can be solved, the obtained kinematics and dynamics indexes can be compared with data collected by various sensors in a real physical test, and biological fidelity verification of the human body model is facilitated.

Description

Technical Field

[0001] The present invention relates to the technical field of finite element modeling, and in particular to a kinematic and dynamic index output method based on a human body model. Background Art

[0002] As road vehicle safety assessment is also developing towards the direction of diversified occupant protection and complex test scenarios, existing physical tests can no longer meet the needs of multi-sign and multi-condition assessment. Virtual assessment based on the human finite element model (hereinafter referred to as the "human body model") has gradually become a consensus in the development of vehicle safety assessment.

[0003] At present, human models have been widely used in research related to human injuries, but the application of human models in vehicle safety testing and evaluation is still immature. The main reason is that for human models, the commonly used output indicators are biomechanical indicators, such as stress, strain, pressure, etc., while in vehicle safety evaluation, the common evaluation indicators are kinematic indicators, such as displacement and acceleration, and dynamic indicators, such as force and torque, among which kinematic and dynamic indicators cannot be unified for effective extraction. The traditional biomechanical indicator method cannot be compared with the data collected by various sensors in real physical experiments, which is not convenient for the biofidelity verification of human models.

[0004] Therefore, how to establish a unified kinematic and dynamic index output on the human body model becomes a key issue in the application of human body models in vehicle safety virtual evaluation. Summary of the invention

[0005] The present invention aims to provide a method for outputting kinematic and dynamic indicators based on a human body model, which can solve the technical problem that the kinematic and dynamic indicators of the human body model cannot be effectively extracted in the prior art. The obtained kinematic and dynamic indicators can be compared with the data collected by various sensors in real physical experiments, which is convenient for verifying the biological fidelity of the human body model.

[0006] The present invention provides the following basic scheme: a method for outputting kinematic and dynamic indicators based on a human body model, comprising the following contents:

[0007] S1. Acceleration modules are established at the head, chest, hips, and lower limbs of the human body model for global and local acceleration and angular velocity output;

[0008] S2. Establish displacement modules at the chest, abdomen, knee joint and Achilles tendon of the human body model to output compression and elongation;

[0009] S3. Establish section force modules at the spine, iliac crest, femur, and tibia of the human body model for the output of local forces and moments.

[0010] Further, it also includes: S4, the acceleration module outputs global and local acceleration and angular velocity, the displacement module outputs compression and elongation, and the section force module outputs local force and moment.

[0011] Further, the S1 includes:

[0012] S101, establishing a general acceleration module, wherein the acceleration module includes: a rigid shell unit component, a deformable shell unit component, a global output node and an accelerometer unit;

[0013] S102, a rigid shell unit component, comprising: three orthogonal triangular shell units connected by common nodes, wherein three orthogonal edges of the accelerometer unit are defined by the orthogonal triangular shell units, and the common intersection vertex is the coordinate origin;

[0014] S103, a deformable shell element assembly, comprising: three trapezoidal quadrilateral shell elements and one orthogonal triangular shell element, wherein the trapezoidal quadrilateral shell element is connected to all orthogonal triangular shell elements at common nodes;

[0015] S104, the global output node is consistent with the spatial coordinates of the vertices of the rigid shell element component, and is rigidly connected to the rigid shell element component using rigid node constraints;

[0016] S105, the middle n nodes of the deformable shell element component and the m nodes evenly distributed on the target bone are softly connected through the first interpolation constraint of the interpolation node constraint;

[0017] S106, target bones, including: skull, cervical vertebrae, thoracic vertebrae, lumbar vertebrae, hip, femur, tibia and talus;

[0018] S107, the center vertex of the acceleration module at the skull is placed at the center of mass of the human model head, the orthogonal bottom surface is parallel to the Frankfurt plane of the head, and the orthogonal side surface coincides with the symmetry plane of the human model;

[0019] S108, the central vertex of the acceleration module at the spinal vertebra is placed at the mass center of the corresponding vertebra, the orthogonal bottom surface is parallel to the corresponding vertebral end surface, and the orthogonal side surface coincides with the symmetry surface of the human body model;

[0020] S109, the center vertex of the acceleration module at the hip bone is placed at point H of the human body model, that is, the midpoint of the center points of the left and right hip joints, the orthogonal bottom surface is parallel to the initial horizontal plane, and the orthogonal side surface coincides with the symmetry plane of the human body model;

[0021] S110, the central vertex of the acceleration module at the femur and tibia is placed at the center point of the long bone, the orthogonal bottom surface is perpendicular to the axis of the long bone, and the orthogonal side surface is parallel to the symmetry plane of the human body model;

[0022] S111, the central vertex of the acceleration module at the talus is placed at the centroid of the talus, the orthogonal bottom surface is parallel to the initial horizontal plane, and the orthogonal side surface is parallel to the symmetry plane of the human body model;

[0023] S112, setting the node output option in the data set output setting item, and setting the output time step based on the unit system of the human body model;

[0024] S113, establishing an accelerometer seat belt unit through the accelerometer unit, and outputting three-dimensional acceleration and angular velocity of the local coordinate system;

[0025] S114, outputting the three-dimensional acceleration and angular velocity of the global coordinate system through the global output point and node time history data set;

[0026] S115. The rigid shell unit component and the deformable shell unit component are set to have a material density lower than a preset material density.

[0027] Furthermore, n is 3 and m is 30.

[0028] Further, the S2 includes:

[0029] S201, establishing a general displacement module, including: a second interpolation constraint and a spring unit; wherein the spring unit is connected to the human body model in two ways: one is that the end point of the spring unit is connected to the corresponding part of the human body model through a common node, and the other is that the end point of the spring unit is connected to the corresponding part of the human body model through a second interpolation constraint of an interpolation node constraint;

[0030] S202, an endpoint of one side of the displacement module at the chest is located at the centroid of the sternum and connected to the common node of the sternum node, and an endpoint of the other side of the displacement module at the chest is located at the centroid of the fourth thoracic vertebra and connected to i nodes evenly distributed on the vertebra through a second interpolation constraint;

[0031] S203, one end point of the displacement module at the abdomen is located at the center point of the abdominal skin and is connected to j nodes evenly distributed on the abdominal skin through a second interpolation constraint, and the other end point of the displacement module at the chest is located at the center point of the first lumbar vertebra and is connected to i nodes evenly distributed on the vertebra through a second interpolation constraint;

[0032] S204, the displacement module at the knee joint includes four spring units, which are respectively located at the lateral collateral ligament, the medial collateral ligament, the anterior cruciate ligament and the posterior cruciate ligament. One end point of the displacement module at the knee joint is connected to the common node of the ligament-femoral distal end attachment center point, and the other end point is connected to the common node of the ligament-tibia proximal end attachment center point;

[0033] S205, one end point of the displacement module at the Achilles tendon is connected to a common node with the center point of attachment of the upper end of the Achilles tendon, and the other end point is connected to a common node with the center point of attachment of the Achilles tendon to the calcaneus;

[0034] S206, setting a Hooke's coefficient of the spring unit lower than a preset Hooke's coefficient to ensure that there is no additional influence on the movement of the human body model itself;

[0035] S207, setting the spring displacement option in the keyword data set output setting item, and setting the output time step based on the unit system of the human body model;

[0036] S208. Set a spring time history data set, and output the local compression and elongation by recording the displacement changes of the spring unit.

[0037] Furthermore, i is 10 and j is 20.

[0038] Further, the S3 includes:

[0039] S301, establishing a general section force module, including: a volume unit set, a shell unit set, a node set, a local coordinate system and a transfer section;

[0040] S302, a local coordinate system, including: a rigid orthogonal tetrahedron unit, three sides of the orthogonal tetrahedron unit define three coordinate axes of the local coordinate system, and the central vertex of the rigid tetrahedron is the coordinate origin;

[0041] S303, target cross sections, including: cross sections at the cervical vertebrae, cross sections at the thoracic vertebrae, cross sections at the lumbar vertebrae, cross sections at the iliac bone, cross sections at the upper end of the femur, cross sections at the lower end of the femur, cross sections at the upper end of the tibia, and cross sections at the lower end of the tibia;

[0042] S304, the target section of the cervical, thoracic and lumbar vertebrae is located at the section passing through the centroid of the vertebrae and parallel to the end face of the vertebrae, the center point of the rigid orthogonal tetrahedron unit is located at the centroid of the vertebrae, the orthogonal bottom surface is parallel to the section, and the orthogonal side surface is parallel to the symmetry plane of the vertebrae;

[0043] S305, the target section at the ilium is parallel to the end surface of the iliac crest and there is a quantitative offset, and the section force module at the ilium does not set a local coordinate system;

[0044] S306, the target section at the upper end of the femur and tibia is located at the proximal third of the long bone, and the section is perpendicular to the axis of the long bone, the center point of the rigid orthogonal tetrahedron unit is located at the center of the section, the orthogonal bottom surface is parallel to the section, and the orthogonal side surface is parallel to the symmetry plane of the human body model;

[0045] S307, the target section at the lower end of the femur and tibia is located at one-third of the distal end of the long bone, and the section is perpendicular to the axis of the long bone, the center point of the rigid orthogonal tetrahedron unit is located at the center of the section, the orthogonal bottom surface is parallel to the section, and the orthogonal side surface is parallel to the symmetry plane of the human body model;

[0046] S308, setting the section force option in the data set output setting item, and setting the output time step based on the unit system of the human body model;

[0047] S309: Set the section force data, select the corresponding solid element set, shell element combination, node set and local coordinate system, and transmit the output of global or local forces and moments in three directions on the section.

[0048] Further, the volume unit set includes: traversing all volume units on the complete target cross section;

[0049] The shell element set includes: traversing all shell elements outside the complete target cross section;

[0050] The node set includes: traversing all nodes on the complete target section.

[0051] Beneficial effects: This scheme provides a detailed method for outputting kinematic and dynamic indicators applied to a human finite element model, by establishing acceleration modules at the head, chest, hip, and lower limbs of the human body model for global and local acceleration and angular velocity output; establishing displacement modules at the chest, abdomen, knee joint, and Achilles tendon of the human body model for compression and elongation output; and establishing section force modules at the spine, iliac crest, femur, and tibia of the human body model for local force and torque output.

[0052] Compared with traditional biomechanical index methods, kinematic and kinetic indexes can be compared with data collected by various sensors in real physical experiments, which facilitates the biofidelity verification of human models;

[0053] The acceleration module establishment method not only provides the setting method of providing global and local three-dimensional acceleration and angular velocity output at the same time, but also explains the detailed positioning process of various parts of the human body model. At the same time, this method can be expanded and applied to other parts of the human body model.

[0054] The establishment method of the displacement module and the cross-sectional force module not only provides the setting method of providing the stretching amount, compression amount and cross-sectional force at the same time, but also explains the detailed positioning process in various parts of the human body model. At the same time, this method can be expanded to other parts of the human body model.

[0055] In summary, this solution can solve the technical problem that the existing technology cannot effectively extract the kinematic and dynamic indicators of the human body model. The obtained kinematic and dynamic indicators can be compared with the data collected by various sensors in real physical experiments, which is convenient for the biological fidelity verification of the human body model. BRIEF DESCRIPTION OF THE DRAWINGS

[0056] Figure 1A schematic flow chart of an embodiment of a method for outputting kinematic and dynamic indicators based on a human body model according to the present invention;

[0057] Figure 2 A schematic diagram of an acceleration module in an embodiment of a method for outputting kinematic and dynamic indicators based on a human body model of the present invention;

[0058] Figure 3 A schematic diagram of the positioning and connection of a skull acceleration module in an embodiment of a method for outputting kinematic and dynamic indicators based on a human body model of the present invention;

[0059] Figure 4 A schematic diagram of positioning and connection of a chest displacement module in an embodiment of a method for outputting kinematic and dynamic indicators based on a human body model of the present invention;

[0060] Figure 5 This is a schematic diagram of positioning the femur and vertebral cross-section force modules in an embodiment of a method for outputting kinematic and dynamic indicators based on a human body model of the present invention. DETAILED DESCRIPTION

[0061] The following is further described in detail through specific implementation methods:

[0062] The figure marks in the drawings of the specification include: rigid shell unit component 201, deformable shell unit component 202, global output node 203, accelerometer unit 204, target bone 301, first interpolation constraint 302, accelerometer module 303, sternum 401, spring unit 402, second interpolation constraint 403, vertebra 404, unit set 501, shell unit set 502, node set 503, spinal vertebra 504, proximal end of long bone 505, distal end of long bone 506, transfer section 507, orthogonal tetrahedron unit 508, local coordinate system 509.

[0063] In the description of this application, unless otherwise clearly specified and limited, the terms "first" and "second" are used for descriptive purposes only and cannot be understood as indicating or implying relative importance; unless otherwise specified or explained, the term "plurality" refers to two or more; the terms "connected" and "fixed" should be understood in a broad sense, for example, "connected" can be a fixed connection, a detachable connection, an integral connection, or an electrical connection; it can be directly connected or indirectly connected through an intermediate medium. For ordinary technicians in this field, the specific meanings of the above terms in this application can be understood according to specific circumstances.

[0064] In the description of this specification, it should be understood that the directional words such as "upper", "lower", "left", and "right" described in the embodiments of the present application are described at the angles shown in the accompanying drawings and should not be understood as limitations on the embodiments of the present application. In addition, in the context, it should also be understood that when it is mentioned that an element is connected to the "upper", "lower", "left", or "right" of another element, it can not only be directly connected to the "upper", "lower", "left", or "right" of another element, but can also be indirectly connected to the "upper", "lower", "left", or "right" of another element through an intermediate element.

[0065] The embodiment is basically as shown in the attached Figure 1 As shown: A method for outputting kinematic and dynamic indicators based on a human body model, including the following contents:

[0066] S1. Acceleration modules are established at the head, chest, hips, and lower limbs of the human body model to output global and local acceleration and angular velocity;

[0067] The specific steps of S1 are as follows:

[0068] S101, establish a general acceleration module, such as Figure 2 As shown, the acceleration module includes: a rigid shell unit component 201, a deformable shell unit component 202, a global output node 203 and an accelerometer unit 204;

[0069] S102, a rigid shell element component 201, comprising: three orthogonal triangular shell elements connected by common nodes, wherein three orthogonal edges of the accelerometer unit 204 are defined by the orthogonal triangular shell elements, and the common intersection vertex is the coordinate origin;

[0070] S103, a deformable shell element assembly 202, comprising: three trapezoidal quadrilateral shell elements and one orthogonal triangular shell element, wherein the trapezoidal quadrilateral shell element is connected to all orthogonal triangular shell elements at common nodes;

[0071] S104, the global output node 203 is consistent with the vertex space coordinates of the rigid shell element component 201, and is rigidly connected to the rigid shell element component 201 using rigid node constraints; in this embodiment, the keyword *CONSTRAINED_EXTRA_NODES (rigid node constraints) is used for rigid connection;

[0072] S105, such as Figure 3As shown, the middle n nodes of the deformable shell unit component 202 and the m nodes evenly distributed on the target skeleton 301 are softly connected through the first interpolation constraint 302 of the interpolation node constraint; in this embodiment, the first interpolation constraint 302 of the keyword *CONSTRAINED_INTERPLOLATION (interpolation node constraint) is used for soft connection; in this embodiment, n is 3 and m is 30; in other embodiments, m can also be set to 20, 40, or 50;

[0073] S106, target skeleton 301, including: skull, cervical vertebrae, thoracic vertebrae, lumbar vertebrae, hip bone, femur, tibia and talus;

[0074] S107, the center vertex of the acceleration module at the skull is placed at the center of mass of the human model head, the orthogonal bottom surface is parallel to the Frankfurt plane of the head, and the orthogonal side surface coincides with the symmetry plane of the human model;

[0075] S108, the central vertex of the acceleration module at the spinal vertebra is placed at the mass center of the corresponding vertebra, the orthogonal bottom surface is parallel to the corresponding vertebral end surface, and the orthogonal side surface coincides with the symmetry surface of the human body model;

[0076] S109, the center vertex of the acceleration module at the hip bone is placed at point H of the human body model, that is, the midpoint of the center points of the left and right hip joints, the orthogonal bottom surface is parallel to the initial horizontal plane, and the orthogonal side surface coincides with the symmetry plane of the human body model;

[0077] S110, the central vertex of the acceleration module at the femur and tibia is placed at the center point of the long bone, the orthogonal bottom surface is perpendicular to the axis of the long bone, and the orthogonal side surface is parallel to the symmetry plane of the human body model;

[0078] S111, the central vertex of the acceleration module at the talus is placed at the centroid of the talus, the orthogonal bottom surface is parallel to the initial horizontal plane, and the orthogonal side surface is parallel to the symmetry plane of the human body model;

[0079] S112, setting the node output option in the data set output setting item, and setting the output time step based on the unit system of the human body model; in this embodiment, setting the *NODOUT (node ​​output) option in the keyword *DATABASE_OPTION (data set output setting item);

[0080] S113, establishing an accelerometer seat belt unit at the accelerometer unit 204, and outputting the three-dimensional acceleration and angular velocity of the local coordinate system 509; in this embodiment, establishing a keyword *ELEMENT_SEATBELT_ACCELERATOR (accelerometer seat belt unit) at the accelerometer unit 204, and outputting the three-dimensional acceleration and angular velocity of the local coordinate system 509;

[0081] S114. The three-dimensional acceleration and angular velocity of the global coordinate system are output through the global output point and the node time history data set. In this embodiment, the three-dimensional acceleration and angular velocity of the global coordinate system are output through the global output point and the keyword *DATABASE_HISTORY_NODE (node ​​time history data set).

[0082] S115. The rigid shell unit component 201 and the deformable shell unit component 202 are set to have a material density lower than a preset material density so that their weight can be ignored.

[0083] S2. Establish displacement modules at the chest, abdomen, knee joint and Achilles tendon of the human body model to output compression and elongation;

[0084] The specific steps of S2 are as follows:

[0085] S201, establish a general displacement module, such as Figure 4 As shown, it includes: a second interpolation constraint 403 and a spring unit 402; wherein the spring unit 402 is connected to the human body model in two ways: one is that the end point of the spring unit 402 is connected to the corresponding part of the human body model at a common node, and the other is that the end point of the spring unit 402 is connected to the corresponding part of the human body model through the second interpolation constraint 403 of the interpolation node constraint; in this embodiment, the end point of the spring unit 402 is connected to the corresponding part of the human body model through the second interpolation constraint 403 with the keyword *CONSTRAINED_INTERPOLATION (interpolation node constraint);

[0086] S202, one end point of the displacement module at the chest is located at the mass center of the sternum 401 and is connected to the common node of the sternum 401, and the other end point of the displacement module at the chest is located at the mass center of the fourth thoracic vertebra and is connected to i nodes evenly distributed on the vertebral body 404 through the second interpolation constraint 403;

[0087] S203, one end point of the displacement module at the abdomen is located at the center point of the abdominal skin and is connected to j nodes evenly distributed on the abdominal skin through a second interpolation constraint 403, and the other end point of the displacement module at the chest is located at the center point of mass of the first lumbar vertebra and is connected to i nodes evenly distributed on the vertebral body 404 through a second interpolation constraint 403; in this embodiment, i is 10 and j is 20; in other embodiments, i can also be 5, 15, 20; j can also be 10, 30, 40;

[0088] S204, the displacement module at the knee joint comprises four spring units 402, which are respectively located at the lateral collateral ligament, the medial collateral ligament, the anterior cruciate ligament and the posterior cruciate ligament, and one end point of the displacement module at the knee joint is connected to the common node of the ligament-femoral distal end attachment center point, and the other end point is connected to the common node of the ligament-tibia proximal end attachment center point;

[0089] S205, one end point of the displacement module at the Achilles tendon is connected to a common node with the center point of attachment of the upper end of the Achilles tendon, and the other end point is connected to a common node with the center point of attachment of the Achilles tendon to the calcaneus;

[0090] S206, the spring unit 402 is set to have a Hooke's coefficient lower than a preset Hooke's coefficient to ensure that there is no additional influence on the movement of the human body model itself;

[0091] S207, setting the spring displacement option in the data set output setting item, and setting the output time step based on the unit system of the human body model; in this embodiment, setting the *DEFORC (spring displacement) option in the keyword *DATABASE_OPTION (data set output setting item);

[0092] S208, setting a spring time history data set, and outputting the local compression and elongation by recording the displacement change of the spring unit 402; in this embodiment, the keyword *DATABASE_HISTORY_DISCRETE (spring time history data set) is set.

[0093] S3, establishing a cross-sectional force module at the spine, iliac crest, femur, and tibia of the human body model to output local forces and moments;

[0094] The specific steps of S3 are as follows:

[0095] S301. Establish a general section force module, such as Figure 5 As shown, it includes: a body unit set 501, a shell unit set 502, a node set 503, a local coordinate system 509 and a transfer section 507; wherein the body unit set 501 includes: traversing all body units on the complete target section; the shell unit set 502 includes: traversing all shell units outside the complete target section; the node set 503 includes: traversing all nodes on the complete target section;

[0096] S302, a local coordinate system 509, comprising: a rigid orthogonal tetrahedron unit 508, wherein three coordinate axes of the local coordinate system 509 are defined by three sides of the orthogonal tetrahedron unit 508, and the central vertex of the rigid tetrahedron is the coordinate origin;

[0097] S303, target cross sections, including: cross sections at the cervical vertebrae, cross sections at the thoracic vertebrae, cross sections at the lumbar vertebrae, cross sections at the iliac bone, cross sections at the upper end of the femur, cross sections at the lower end of the femur, cross sections at the upper end of the tibia, and cross sections at the lower end of the tibia;

[0098] S304, the target section at the cervical, thoracic and lumbar vertebrae is located at a section passing through the centroid of the vertebrae 404 and parallel to the end face of the vertebrae 404, the center point of the rigid orthogonal tetrahedron unit 508 is located at the centroid of the vertebrae 404, the orthogonal bottom surface is parallel to the section, and the orthogonal side surface is parallel to the symmetry plane of the vertebrae 404;

[0099] S305, the target section at the ilium is parallel to the end surface of the iliac crest and there is a quantitative offset, and the section force module at the ilium does not set a local coordinate system 509;

[0100] S306, the target section at the upper end of the femur and tibia is located at one third of the proximal end 505 of the long bone, and the section is perpendicular to the axis of the long bone, the center point of the rigid orthogonal tetrahedron unit 508 is located at the center of the section, the orthogonal bottom surface is parallel to the section surface, and the orthogonal side surface is parallel to the symmetry plane of the human body model;

[0101] S307, the target section at the lower end of the femur and tibia is located at one third of the distal end 506 of the long bone, and the section is perpendicular to the axis of the long bone, the center point of the rigid orthogonal tetrahedron unit 508 is located at the center of the section, the orthogonal bottom surface is parallel to the section surface, and the orthogonal side surface is parallel to the symmetry plane of the human body model;

[0102] S308, setting the section force option in the data set output setting item, and setting the output time step based on the unit system of the human body model; in this embodiment, setting the *SECORC (section force) option in the keyword *DATABASE_OPTION (data set output setting item);

[0103] S309: Set the section force data, select the corresponding solid unit set 501, shell unit combination, node set 503 and local coordinate system 509, and transmit the output of global or local forces and moments in three directions on the section 507; in this embodiment, set the keyword *DATABASE_CROSS_SECTION (section force data).

[0104] S4. The acceleration module outputs global and local acceleration and angular velocity, the displacement module outputs compression and elongation, and the section force module outputs local force and moment.

[0105] This solution provides a detailed method for outputting kinematic and dynamic indicators for human finite element models. It establishes acceleration modules at the head, chest, hips, and lower limbs of the human model for global and local acceleration and angular velocity output; establishes displacement modules at the chest, abdomen, knee joints, and Achilles tendons of the human model for compression and elongation output; and establishes cross-sectional force modules at the spine, iliac crest, femur, and tibia of the human model for local force and torque output. Compared with traditional biomechanical indicator methods, kinematic and dynamic indicators can be compared with data collected by various sensors in real physical experiments, which facilitates the verification of the biofidelity of the human model.

[0106] Among them, the method for establishing the acceleration module not only provides the setting method for simultaneously providing global and local three-dimensional acceleration and angular velocity outputs, but also explains the detailed positioning process in various parts of the human body model. At the same time, this method can be expanded and applied to other parts of the human body model; the method for establishing the displacement module and the cross-sectional force module not only provides the setting method for simultaneously providing the stretching amount, compression amount and cross-sectional force, but also explains the detailed positioning process in various parts of the human body model. At the same time, this method can be expanded and applied to other parts of the human body model.

[0107] The above is only an embodiment of the present invention. The common sense such as the known specific structure and characteristics in the scheme is not described in detail here. The ordinary technicians in the relevant field know all the common technical knowledge in the technical field of the invention before the application date or priority date, can obtain all the existing technologies in the field, and have the ability to apply the conventional experimental means before that date. The ordinary technicians in the relevant field can improve and implement this scheme in combination with their own abilities under the enlightenment given by this application. Some typical known structures or known methods should not become obstacles for ordinary technicians in the relevant field to implement this application. It should be pointed out that for those skilled in the art, without departing from the structure of the present invention, several deformations and improvements can be made, which should also be regarded as the protection scope of the present invention, which will not affect the effect of the implementation of the present invention and the practicality of the patent. The protection scope required by this application shall be based on the content of its claims, and the specific implementation methods and other records in the specification can be used to interpret the content of the claims.

Claims

1. A method for outputting kinematic and dynamic indicators based on a human body model, characterized in that: It includes the following: S1. Acceleration modules are established at the head, chest, hips, and lower limbs of the human body model for global and local acceleration and angular velocity output; S2. Establish displacement modules at the chest, abdomen, knee joint and Achilles tendon of the human body model to output compression and elongation; S3. Establish section force modules at the spine, iliac crest, femur, and tibia of the human body model for the output of local forces and moments.

2. The method for outputting kinematic and dynamic indicators based on a human body model according to claim 1, characterized in that: Also includes: S4. The acceleration module outputs global and local acceleration and angular velocity, the displacement module outputs compression and elongation, and the section force module outputs local force and moment.

3. The method for outputting kinematic and dynamic indicators based on a human body model according to claim 1, characterized in that: Said S1 comprises: S101, establishing a general acceleration module, wherein the acceleration module includes: a rigid shell unit component, a deformable shell unit component, a global output node and an accelerometer unit; S102, a rigid shell unit component, comprising: three orthogonal triangular shell units connected by common nodes, wherein three orthogonal edges of the accelerometer unit are defined by the orthogonal triangular shell units, and the common intersection vertex is the coordinate origin; S103, a deformable shell element assembly, comprising: three trapezoidal quadrilateral shell elements and one orthogonal triangular shell element, wherein the trapezoidal quadrilateral shell element is connected to all orthogonal triangular shell elements at common nodes; S104, the global output node is consistent with the spatial coordinates of the vertices of the rigid shell element component, and is rigidly connected to the rigid shell element component using rigid node constraints; S105, the middle n nodes of the deformable shell element component and the m nodes evenly distributed on the target bone are softly connected through the first interpolation constraint of the interpolation node constraint; S106, target bones, including: skull, cervical vertebrae, thoracic vertebrae, lumbar vertebrae, hip, femur, tibia and talus; S107, the center vertex of the acceleration module at the skull is placed at the center of mass of the human model head, the orthogonal bottom surface is parallel to the Frankfurt plane of the head, and the orthogonal side surface coincides with the symmetry plane of the human model; S108, the central vertex of the acceleration module at the spinal vertebra is placed at the mass center of the corresponding vertebra, the orthogonal bottom surface is parallel to the corresponding vertebral end surface, and the orthogonal side surface coincides with the symmetry surface of the human body model; S109, the center vertex of the acceleration module at the hip bone is placed at point H of the human body model, that is, the midpoint of the center points of the left and right hip joints, the orthogonal bottom surface is parallel to the initial horizontal plane, and the orthogonal side surface coincides with the symmetry plane of the human body model; S110, the central vertex of the acceleration module at the femur and tibia is placed at the center point of the long bone, the orthogonal bottom surface is perpendicular to the axis of the long bone, and the orthogonal side surface is parallel to the symmetry plane of the human body model; S111, the central vertex of the acceleration module at the talus is placed at the centroid of the talus, the orthogonal bottom surface is parallel to the initial horizontal plane, and the orthogonal side surface is parallel to the symmetry plane of the human body model; S112, setting the node output option in the data set output setting item, and setting the output time step based on the unit system of the human body model; S113, establishing an accelerometer seat belt unit through the accelerometer unit, and outputting three-dimensional acceleration and angular velocity of the local coordinate system; S114, outputting the three-dimensional acceleration and angular velocity of the global coordinate system through the global output point and node time history data set; S115. The rigid shell unit component and the deformable shell unit component are set to have a material density lower than a preset material density.

4. The method for outputting kinematic and dynamic indicators based on a human body model according to claim 3, characterized in that: The n is 3 and the m is 30.

5. The method for outputting kinematic and dynamic indicators based on a human body model according to claim 1, characterized in that: The S2 comprises: S201, establishing a general displacement module, including: a second interpolation constraint and a spring unit; wherein the spring unit is connected to the human body model in two ways: one is that the end point of the spring unit is connected to the corresponding part of the human body model through a common node, and the other is that the end point of the spring unit is connected to the corresponding part of the human body model through a second interpolation constraint of an interpolation node constraint; S202, an endpoint of one side of the displacement module at the chest is located at the centroid of the sternum and connected to the common node of the sternum node, and an endpoint of the other side of the displacement module at the chest is located at the centroid of the fourth thoracic vertebra and connected to i nodes evenly distributed on the vertebra through a second interpolation constraint; S203, one end point of the displacement module at the abdomen is located at the center point of the abdominal skin and is connected to j nodes evenly distributed on the abdominal skin through a second interpolation constraint, and the other end point of the displacement module at the chest is located at the center point of the first lumbar vertebra and is connected to i nodes evenly distributed on the vertebra through a second interpolation constraint; S204, the displacement module at the knee joint includes four spring units, which are respectively located at the lateral collateral ligament, the medial collateral ligament, the anterior cruciate ligament and the posterior cruciate ligament. One end point of the displacement module at the knee joint is connected to the common node of the ligament-femoral distal end attachment center point, and the other end point is connected to the common node of the ligament-tibia proximal end attachment center point; S205, one end point of the displacement module at the Achilles tendon is connected to a common node with the center point of attachment of the upper end of the Achilles tendon, and the other end point is connected to a common node with the center point of attachment of the Achilles tendon to the calcaneus; S206, setting a Hooke's coefficient of the spring unit lower than a preset Hooke's coefficient to ensure that there is no additional influence on the movement of the human body model itself; S207, setting the spring displacement option in the keyword data set output setting item, and setting the output time step based on the unit system of the human body model; S208. Set a spring time history data set, and output the local compression and elongation by recording the displacement changes of the spring unit.

6. The method for outputting kinematic and dynamic indicators based on a human body model according to claim 5, characterized in that: The i is 10 and j is 20.

7. The method for outputting kinematic and dynamic indicators based on a human body model according to claim 1, characterized in that: The S3 includes: S301, establishing a general section force module, including: a volume unit set, a shell unit set, a node set, a local coordinate system and a transfer section; S302, a local coordinate system, including: a rigid orthogonal tetrahedron unit, three sides of the orthogonal tetrahedron unit define three coordinate axes of the local coordinate system, and the central vertex of the rigid tetrahedron is the coordinate origin; S303, target cross sections, including: cross sections at the cervical vertebrae, cross sections at the thoracic vertebrae, cross sections at the lumbar vertebrae, cross sections at the iliac bone, cross sections at the upper end of the femur, cross sections at the lower end of the femur, cross sections at the upper end of the tibia, and cross sections at the lower end of the tibia; S304, the target section of the cervical, thoracic and lumbar vertebrae is located at the section passing through the centroid of the vertebrae and parallel to the end face of the vertebrae, the center point of the rigid orthogonal tetrahedron unit is located at the centroid of the vertebrae, the orthogonal bottom surface is parallel to the section, and the orthogonal side surface is parallel to the symmetry plane of the vertebrae; S305, the target section at the ilium is parallel to the end surface of the iliac crest and there is a quantitative offset, and the section force module at the ilium does not set a local coordinate system; S306, the target section at the upper end of the femur and tibia is located at the proximal third of the long bone, and the section is perpendicular to the axis of the long bone, the center point of the rigid orthogonal tetrahedron unit is located at the center of the section, the orthogonal bottom surface is parallel to the section, and the orthogonal side surface is parallel to the symmetry plane of the human body model; S307, the target section at the lower end of the femur and tibia is located at one-third of the distal end of the long bone, and the section is perpendicular to the axis of the long bone, the center point of the rigid orthogonal tetrahedron unit is located at the center of the section, the orthogonal bottom surface is parallel to the section, and the orthogonal side surface is parallel to the symmetry plane of the human body model; S308, setting the section force option in the data set output setting item, and setting the output time step based on the unit system of the human body model; S309: Set the section force data, select the corresponding solid element set, shell element combination, node set and local coordinate system, and transmit the output of global or local forces and moments in three directions on the section.

8. The method for outputting kinematic and dynamic indicators based on a human body model according to claim 7, characterized in that: The volume unit set includes: traversing all volume units on the complete target cross section; The shell element set includes: traversing all shell elements outside the complete target cross section; The node set includes: traversing all nodes on the complete target section.

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