A brain injury injury mechanism simulation system and electronic equipment

Abstract

The application discloses a brain injury injury mechanism simulation system and electronic equipment, and relates to the technical field of medical simulation. The simulation system comprises a data acquisition module, a simulation module and a result determination module. The data acquisition module is used for acquiring the shaking frequency range of a target tester and displacement-time curves under different shaking directions. The simulation module is used for simulating and determining the biomechanical data of brain tissue injury formation processes under different shaking injury modes according to the shaking frequency range, the displacement-time curves and a full human body finite element model. The result determination module is used for determining the occurrence positions of adult shaking syndrome under different shaking injury modes, and the formation characteristics and injury mechanisms of adult shaking syndrome according to the biomechanical data. The application can simulate the formation characteristics and injury mechanisms of adult shaking syndrome under different shaking injury modes.

Description

Technical Field

[0001] This invention relates to the field of medical simulation technology, and in particular to a brain injury mechanism simulation system and electronic device. Background Technology

[0002] Abusive head trauma (AHT), also known as shaking baby syndrome, is common in cases of child abuse and typically presents with a triad of subdural hemorrhage, retinal hemorrhage, and brain injury. AHT is a clear indicator of infant and child abuse, resulting in high rates of disability and mortality. It is generally believed that AHT usually occurs in very young infants, rarely in children over 2 years of age. However, publicly available data reports four cases of shaking adult syndrome (SAS). These four cases involved individuals being shaken by another person and exhibited the pathological features of the "triad," with all deaths attributed to shaking adult syndrome. From a mechanistic perspective, shaking adult syndrome should be classified as AHT; due to the minimal or absent evidence of external bodily injury from shaking, it easily becomes a means of abuse or torture in supervised settings. Due to the limited number of publicly reported cases of adult shaking syndrome and the lack of further research into its injury mechanisms, forensic experts often struggle to consider adult shaking syndrome in forensic examinations without supporting investigative materials or surveillance footage. Furthermore, they may easily overlook its possibility. Therefore, it is necessary to study the biomechanical characteristics of injuries caused by adult shaking syndrome to elucidate its injury mechanisms. Given the potential for injury, it is impossible to assess the injury mechanisms and damage indicators related to adult shaking syndrome in actual identification and research using live individuals subjected to violent shaking. Therefore, establishing more effective technical solutions to simulate the formation process of adult shaking syndrome under different shaking injury modes is crucial for providing a reference basis for forensic identification. Summary of the Invention

[0003] The purpose of this invention is to provide a brain injury mechanism simulation system and electronic device to simulate the formation characteristics and injury mechanism of adult shake syndrome under different shaking injury modes.

[0004] To achieve the above objectives, the present invention provides the following solution: In a first aspect, the present invention provides a simulation system for the brain injury mechanism, comprising: The data acquisition module is used to acquire the range of head shaking frequency of the target test subject and the displacement-time curves under different shaking directions; the horizontal axis of the displacement-time curve is time, and the vertical axis of the displacement-time curve is the shaking amplitude. The simulation module is used to simulate and determine the biomechanical data of the brain tissue injury formation process under different shaking injury modes based on the shaking frequency range, the displacement-time curve and the whole human finite element model; the shaking injury mode is the injury mode determined by the shaking frequency, shaking amplitude and shaking direction. The result determination module is used to determine, based on the biomechanical data, the location of brain tissue damage in adult shake syndrome under different shaking injury modes, as well as the formation characteristics and injury mechanism of adult shake syndrome.

[0005] Secondly, the present invention provides an electronic device, including a three-dimensional motion capture system and finite element analysis software; the finite element analysis software is equipped with the brain injury mechanism simulation system described in the first aspect.

[0006] According to specific embodiments provided by the present invention, the present invention discloses the following technical effects: This invention can simulate the formation process of adult brain tissue damage under different shaking injury methods, and can quantitatively and objectively explain the formation characteristics and injury mechanism of adult shake syndrome under different shaking injury methods. It provides a basis for the forensic identification of adult shake syndrome from a biomechanical perspective, and has the advantages of good intuitiveness, low cost and high repeatability. Attached Figure Description

[0007] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0008] Figure 1 This is a structural block diagram of the brain injury mechanism simulation system of the present invention; Figure 2 This is a structural block diagram of the electronic device of the present invention; Figure 3 These are imaging images and histopathological findings of victims of the present invention. Figure 4 This is a diagram showing the three-dimensional motion capture results for the three head-shaking directions of this invention; Figure 5 These are kinematic reconstruction results for the three types of shaking-induced injury described in this invention. Figure 6 This is a comparison diagram of the strain contour maps of real cerebral hemorrhage and simulated maximum principal strain (MPS) in this invention. Detailed Implementation

[0009] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0010] Three-dimensional (3D) motion capture systems have been widely used in film, military, sports, and medical fields. They are primarily used to record human movement information under different conditions, reflecting real-world kinematic parameters with millimeter-level accuracy. Capture speeds can reach 10,000 Hz, accurately capturing the trajectory of high-speed moving objects and performing related technical parameter analysis. Therefore, they are crucial equipment for providing accurate finite element simulation boundary conditions.

[0011] The finite element method (FEM) is a numerical analysis method for solving engineering and mathematical physics problems. It represents the application and development of matrix methods in structural mechanics and elasticity, falling under the category of computational mechanics. The FEM discretizes an object's structure into a computational model composed of different elements. These elements are interconnected via element nodes, and equivalent nodal forces replace all forces acting on the elements. Under specific loads, the overall response of the object is determined by the responses of all elements. Existing human finite element models are established based on the above principles, involving steps such as meshing and discretizing a three-dimensional human body model, selecting and assigning material models, and setting contact parameters. Parameters measured in a three-dimensional motion capture system can serve as realistic and accurate boundary conditions. Through calculation using a finite element solver, biomechanical indicators such as force, displacement, stress, and strain at various anatomical locations of the cranial brain model can be obtained. This allows for the prediction of potential injury locations and extent, providing a reference for forensic injury mechanism identification.

[0012] In view of this, the present invention provides a brain injury mechanism simulation system and electronic device to simulate the formation characteristics and injury mechanism of adult shake syndrome under different shaking injury modes.

[0013] To make the above-mentioned objects, features and advantages of the present invention more apparent and understandable, the present invention will be further described in detail below with reference to the accompanying drawings and specific embodiments.

[0014] Example 1 The purpose of this invention is to address the characteristics and injury mechanisms of adult shake syndrome, as it is impossible to conduct research on the injury caused by adult shake syndrome using real human subjects. Currently, quantitative and systematic analysis of adult shake syndrome is lacking. Therefore, this invention provides a simulation system for the brain injury mechanism.

[0015] like Figure 1 As shown, an embodiment of the present invention provides a brain injury mechanism simulation system comprising: Data acquisition module 1 is used to acquire the head shaking frequency range of the target test subject and the displacement-time curves under different shaking directions; the horizontal axis of the displacement-time curve is time, and the vertical axis of the displacement-time curve is the shaking amplitude.

[0016] Simulation module 2 is used to simulate and determine the biomechanical data of brain tissue injury formation process under different shaking injury modes based on the shaking frequency range, the displacement-time curve and the whole human finite element model; the shaking injury mode is the injury mode determined by the shaking frequency, shaking amplitude and shaking direction.

[0017] Result determination module 3 is used to determine, based on the biomechanical data, the location of brain tissue damage in adult shake syndrome under different shaking injury modes, as well as the formation characteristics and injury mechanism of adult shake syndrome.

[0018] The data acquisition module 1 includes: The first data acquisition unit is used to acquire the shaking frequency of the target test subject recorded by the three-dimensional motion capture system; the shaking frequency range is the range of hand shaking frequency generated when the target test subject shakes the weight in his / her hand within a set time.

[0019] The second data acquisition unit is used to acquire the displacement-time curve of the target test subject recorded by the three-dimensional motion capture system; the displacement-time curve is determined based on the actual head movement trajectory of the target test subject (in the case of non-injury); the head movement trajectory is the movement trajectory generated by the target test subject when performing a head shaking experiment within a set time.

[0020] The full-body finite element model includes at least a cranial model and a neck model; the simulation module 2 includes: The cranial model verification unit is used to load translational impact experiments, translational rotational impact experiments, and translational impact experiments, and to verify the effectiveness of the cranial model based on the translational impact experiments, the translational rotational impact experiments, and the translational impact experiments.

[0021] The shaking injury mode determination unit is used to determine multiple shaking injury modes based on the shaking frequency range, the displacement-time curve, and the shaking direction.

[0022] The simulation unit is used to perform finite element simulations on the cranial model using different shaking injury methods to determine the biomechanical data of the brain tissue damage formation process under different shaking injury methods.

[0023] The result determination module 3 includes: A data processing unit is used to process the biomechanical data; the processed biomechanical data includes CSDM. 0.25 HIC 36 MPS, brain pressure, and Von Mises stress.

[0024] The result determination unit is used to determine the location of adult shake syndrome under different shaking injury modes, as well as the formation characteristics and injury mechanism of adult shake syndrome, based on the processed biomechanical data.

[0025] Furthermore, the result determination unit includes: The load curve determination subunit is used to determine the load curves of different brain regions under different shaking injury methods based on the processed biomechanical data; the horizontal axis of the load curve is time, and the vertical axis of the load curve is load.

[0026] The site of injury determination subunit is used to determine the site of brain tissue damage in adult shake syndrome under different shaking injury modes by combining the load curve and brain tissue tolerance threshold.

[0027] The formation characteristics and injury mechanism determination unit is used to determine the strain cloud map based on the processed biomechanical data, and to determine the formation characteristics and injury mechanism of adult shake syndrome under different shaking injury modes based on the strain cloud map.

[0028] Using the shaking motion parameters measured in a 3D motion capture system as boundary conditions for finite element simulation, the existing, fully validated human finite element model offers advantages such as high biosimulation accuracy, low cost, high efficiency, and good repeatability. The frequency of violent shaking in adult males is 3.2-6.8 Hz. At these frequencies, head shaking may lead to severe brain damage. Therefore, the potential injury conditions in real-world scenarios are systematically loaded into the finite element dummy model to obtain the formation mechanisms of adult shake syndrome under different shaking injury modes, providing a reference and basis for the identification of adult shake syndrome from the perspective of injury biomechanics.

[0029] Example 2 like Figure 2 As shown, this embodiment of the invention provides an electronic device, which includes a three-dimensional motion capture system and finite element analysis software. The finite element analysis software incorporates the brain injury mechanism simulation system described in Embodiment 1.

[0030] The three-dimensional motion capture system is used for: The shaking frequency of the target test subject is recorded; the shaking frequency range is the range of hand shaking frequencies generated when the target test subject shakes the weight in his / her hand within a set time period.

[0031] The displacement-time curve of the target test subject is recorded; the displacement-time curve is determined based on the head movement trajectory of the target test subject; the head movement trajectory is the movement trajectory generated by the target test subject when performing a head shaking experiment within a set time period.

[0032] The three-dimensional motion capture system is used to acquire shaking motion parameters of adult male test subjects and import the shaking motion parameters of adult male test subjects into the brain injury mechanism simulation system of the finite element analysis software; the shaking motion parameters of adult male test subjects include the frequency, amplitude and displacement-time curve of the shaking motion of adult male test subjects.

[0033] The 3D motion capture system consists of 12 capture cameras arranged around the performance area. The overlapping area of ​​their fields of view represents the range of motion of the adult male test subject. For ease of processing, the adult male test subject is typically required to wear monochromatic clothing, and special "markers" are affixed to key body parts such as joints, hips, and elbows. The 3D motion capture system identifies and processes these marked points. The system can capture the frequency, amplitude, and displacement-time curve of the adult male test subject's shaking movements (such as head shaking). The captured information is then loaded onto a full-body finite element model to serve as realistic and effective boundary conditions for finite element simulation.

[0034] Currently, there are internationally recognized, widely verified and applied finite element mannequin models, such as the THUMS 4.0, 5.0 and 6.0 (The Total Human Model for Safety Version 4.0, 5.0 & 6.0) models developed by Toyota Research Center, and the GHBMC (Global Human Body Models Consortium) model; and finite element preprocessing software, such as LS-PrePost (ANSYS, Inc.), ANSYS Workbench (ANSYS, Inc.), and HyperWorks (Altair Engineering, Inc.).

[0035] Compared with the prior art, the technical effects of the embodiments of the present invention are as follows: 1. Based on the principles of computational mechanics and biomechanics, the simulation results are reliable, objective, and repeatable, providing a scientific reference for forensic identification work.

[0036] 2. The advanced motion capture system used in this invention can effectively provide boundary conditions for finite element simulation.

[0037] 3. This invention is based on an existing and widely validated human finite element model. After comprehensive validity verification, it has a high degree of biological simulation and the simulation results are close to the real situation.

[0038] 4. This invention is based on a digital dummy model, which has advantages such as high feasibility, high efficiency, low cost, and no medical ethics issues compared to cadaver experiments.

[0039] 5. The results are presented in a clear and intuitive manner. They can reflect the changes in indicators of the damaged area through common graphs and data tables, or represent the location of the damage through stress and strain cloud maps. They can also visually demonstrate the formation process of adult shaking syndrome through animation.

[0040] 6. A series of injury condition matrices can be loaded onto the same model to compare and analyze the characteristics of damage caused by different injury conditions, thereby achieving the purpose of identifying the injury mode.

[0041] Example 3 This invention, based on a real-world case study, explores the characteristics and injury mechanisms of adult shake syndrome. A three-dimensional motion capture system is used to obtain realistic shaking amplitude and frequency to reconstruct more realistic brain injury simulation results. This invention designs a series of simulation experiments based on a whole-human safety model (THUMS) finite element model, i.e., whole-human finite element model simulation experiments, to analyze the relationship between shaking direction, shaking frequency, repetitive shaking effects, and brain injury in adult shake syndrome. It also compares the differences in brain tissue damage and adult shake syndrome under the same impact and shaking load conditions at the same speed to identify adult shake syndrome and assess the risk of brain tissue damage.

[0042] Case: A man was repeatedly shaken (more than 20 times) by his cellmates over a 12-hour period, each shaking lasting approximately 0.3-2 minutes. Around 3 PM that day, the man exhibited abnormal behavior, such as swaying while walking and unsteadiness while standing. He fell into a coma around 11 PM that night, and his cellmates placed him on a bed around midnight, after which he remained unsupervised. At 5 AM the next morning, his cellmates found him with unstable vital signs and unconsciousness, and he was immediately taken to the hospital for emergency treatment. Hospital examinations revealed "left temporo-occipital lobe hemorrhage, subdural hemorrhage, subarachnoid hemorrhage, and brain herniation." He subsequently underwent emergency craniectomy and evacuation of the intracranial hematoma. After the surgery, he remained in a coma and died 10 days later. Imaging findings are as follows. Figure 3 As shown, Figure 3 (a) shows patchy high-density areas in the left temporal and occipital lobes, and small patchy areas (horizontal plane) in the lateral ventricle of the right occipital lobe. Figure 3(b) shows a large patchy high-density area in the left temporal lobe (sagittal plane). Figure 3 Image (c) shows a hematoma in the left temporal lobe, close to the tentorium and temporal bone (coronal plane). Figure 3 Image (d) shows bilateral optic nerve distortion. Figure 3 (e) shows brain hemorrhage under a microscope (HE, ×100). Figure 3 Image (f) shows a β-APP immune-reactive axonal contraction sphere (HE, ×200). Imaging findings: Large patchy high-density areas in the left temporal and occipital lobes. Blood casts are visible in the left lateral ventricle, small patchy areas are visible in the right occipital lateral ventricle, and an arc-shaped high-density area is visible below the left temporal bone. The midline of the brain is significantly shifted to the right, and cerebral edema is obvious. Bilateral optic nerve distortion with localized high-density shadows, most prominent on the left. Autopsy results: Hemorrhage in the left temporal and occipital lobes extending into the lateral ventricles, subdural hemorrhage in the left temporal lobe, cerebral edema, and encephalomalacia. Hypostatic pneumonia, cerebral hemorrhage, and diffuse axonal injury (DAI) were observed under a microscope. No other signs of trauma, asphyxia, or poisoning were found. Therefore, it is necessary to determine the injury mechanism of cerebral hemorrhage (pathological or traumatic mechanism) to elucidate the manner of death. Based on this case, this invention embodiment conducted a series of simulations. First, the experimental parameters of the volunteer were obtained in a three-dimensional motion capture system as simulation boundary conditions. Next, a validated full-body finite element model was loaded into LS-PrePost, contact was defined, and simulation boundary conditions were set to simulate scenarios with different shaking frequencies and directions, generating a K-file. Then, the LS-DYNA solver was used to calculate the solution, and the calculated d3plot file was imported into LS-PrePost. Biomechanical data after head shaking was extracted and analyzed to predict whether adult shake syndrome would occur under different shaking injury modes, as well as its formation characteristics and injury mechanisms. The specific steps are as follows: Step 1: Use a 3D motion capture system to provide simulation boundary conditions for the full-body finite element model.

[0043] (1) The three-dimensional motion capture system was equipped with 12 capture lenses; at a measurement accuracy of 1000Hz, 14 adult male volunteers (aged 22-51) held a 1 kg object with both hands and shook it rapidly. Each adult male volunteer shook the object 3 times, and each shaking process lasted 15 seconds. The average frequency of the 3 shaking events was calculated.

[0044] (2) To quantify the actual head shaking amplitude, a volunteer with a height almost identical to that of the victim was selected, and a head shaking experiment was conducted based on the victim's sitting posture and height. Markers were placed between the auricle and the iliac bone above the external occipital protuberance of the volunteer, and the head movement trajectory was recorded using a three-dimensional motion capture system, including the head trajectory in the forward-backward (AP), left-right (LR), and left-forward-right-backward (LARP) directions. The displacement-time curves synthesized by the four markers in the main movement directions were extracted.

[0045] Figure 4 Images (a) and (b) show the location of the head markers. Figure 4 (c) shows the displacement-time curves for the forward and backward swaying and the left and right swaying. Figure 4 The middle (d) section displays the displacement-time curve in the left-front-right-rear swaying direction.

[0046] Step 2: Perform finite element calculations on the existing whole-body finite element model to determine the formation characteristics and injury mechanism of adult shake syndrome under different shaking injury modes.

[0047] (1) Load the full human body finite element model in finite element preprocessing software (such as LS-PrePost).

[0048] The full-body finite element model (height 175cm, weight 77kg) features detailed anatomical structures. The cranial model should include specific anatomical structures such as the three layers of the skull, meninges, maxilla, cerebrum, cerebellum, and brainstem. Bony structures should include the outer table, inner table, diploic plate, and the main foramina and fissures of the skull base. Mesh quality requirements for the full-body finite element model: element length approximately 3-5mm, warpage ≤50°, aspect ratio ≤5, offset ≤60°, Jacobian ≥0.3. The cranial model's effectiveness is verified through translational impact tests (horizontal plane), translational-rotational impact tests (sagittal plane), and translational impact tests (coronal plane).

[0049] (2) Based on relevant case data, determine the mode of injury caused by shaking through the parameters obtained in step one.

[0050] During the head-shaking injury, the skull showed almost no deformation, and was therefore considered a rigid body. The midpoint between the glabella and the external occipital protuberance (essentially the same as the composite point in motion capture) was used as the loading point for the displacement-time curve. Simultaneously, the loading points and nodes of the frontal, temporal, parietal, and occipital bones were bound together (equivalent to a structure) using the keyword *CONSTRAINED_NODAL_RIGID_BODY to load the head-shaking data.

[0051] According to statistics from 14 volunteers, the frequency range of vigorous shaking in adults was 3.2-6.8 Hz, and the amplitude of the shaking was 98.04 ± 17.928 mm. During the test, the maximum linear acceleration of the volunteers' handshake was 90.1 m / s². 2 The study simulated brain injury responses at 4Hz, 5Hz, 6Hz, and 7Hz, as well as brain injury responses in the anterior-posterior (AP), left (LR), and left anterior-right posterior (LARP) directions, and performed permutation and combination calculations to obtain a total of 17 different shaking injury modes.

[0052] (3) Set the calculation time and output data type: Set the calculation time to 20ms and output d3plot file (interval time 0.01ms).

[0053] (4) Submit the calculation file generated by preprocessing to the server.

[0054] (5) Post-processing of calculation results.

[0055] Import the calculated d3plot file into finite element post-processing software (such as LS-PrePost) to extract the CSDM under different shaking injury modes. 0.25 HIC 36 Biomechanical data such as MPS, brain pressure, and Von Mises stress were compared with brain tissue tolerance thresholds to predict the possible sites of adult shake syndrome. The formation characteristics and injury mechanisms of adult shake syndrome were then analyzed using stress and strain contour maps. The simulation results are shown in Table 1.

[0056] Table 1. Values ​​of damage criteria under different load conditions

[0057] Figure 5 Images (a)-(c) show the simulated head swaying motion in the AP direction. Figure 5 Image (d) shows the displacement-time curves and loading curves of different brain regions under AP shaking conditions. Figure 5 The middle (e)-(g) images show the simulated head rocking motion in the LR direction. Figure 5 The middle (h) image shows the displacement-time curves and loading curves of different brain regions under LR shaking conditions. Figure 5 The middle (i)-(k) diagram shows the simulated head rocking motion in the LARP direction. Figure 5 middle( l The displacement-time curves and loading curves of different brain regions under LARP shaking conditions are displayed.

[0058] Figure 6 Image (a) shows a three-dimensional reconstruction of the patient's intracranial hematoma, illustrating its relative position within the cranial cavity. Figure 6(b) shows the contour distribution of MPS ≥ 0.21 caused by swaying in the AP direction. Figure 6 Image (c) shows the contour distribution of MPS ≥ 0.21 caused by LARP directional swaying. Figure 6 (d) shows the cloud map distribution of MPS≧0.21 caused by swaying in the LR direction.

[0059] Based on the simulation results, the strain distribution of MPS is consistent with the pathological and radiological interpretation of this case. Finite element simulation reconstructed the brain contusion and hemorrhage process. In the AP sagittal plane, the strain is concentrated in the inferior temporal lobe (MPS>0.21), which is consistent with the hemorrhage site in this case, indicating that brain contusion can occur under this type of shaking injury.

[0060] Since there is no simulation calculation of HIC 36 Reaching the threshold, this contradictory phenomenon may indicate that kinematic HIC... 36 The value can predict the risk of injury to the entire head, including skull fractures, intracranial hemorrhage, and cerebral contusion, while adult shaken syndrome mainly consists of subdural hemorrhage, cerebral contusion, and DAI. Therefore, HIC 36 The threshold of 1040 may be too high to assess the likelihood of shake-induced brain injury. Von Mises stress is not sensitive or effective in predicting brain responses under different shake loading conditions, possibly because these injury indicators and tolerance limits were not developed based on a full-body finite element model. It is noteworthy that under rapid impact conditions (collisions, falls, etc.), brain pressure is highly correlated with localized compression between the brain and skull. Therefore, under shake loading in the AP direction, the duration is relatively long, and the linear acceleration is not high enough to generate sufficient brain pressure to cause cerebral hemorrhage. MPS and CSDM 0.25 The standard can predict brain contusion and hemorrhage with relatively high sensitivity and specificity, and can distinguish the injury biomechanical response of brain injury under shaking load. Because CSDM 0.25 The tolerance limit is 0.69, which can predict anatomical brain injury in AIS4+. According to Table 1, MPS values ​​indicate a risk of brain injury under high-frequency AP, LARP, and LR shaking conditions. CSDM values ​​show that anatomical brain injury only occurs under high-frequency AP and LARP loads. Therefore, the shaking direction has a significant impact on brain injury.

[0061] This invention demonstrates that by using a three-dimensional motion capture system and a full-body finite element model to simulate and analyze adult shaking syndrome, the injury mechanism of adult shaking syndrome can be explained more intuitively and objectively from a biomechanical perspective, and the conditions for injury formation can be inferred, providing a basis for forensic identification of adult shaking syndrome cases.

[0062] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on the differences from other embodiments. The same or similar parts between the various embodiments can be referred to each other.

[0063] This document uses specific examples to illustrate the principles and implementation methods of the present invention. The descriptions of the above embodiments are only for the purpose of helping to understand the method and core ideas of the present invention. Furthermore, those skilled in the art will recognize that, based on the ideas of the present invention, there will be changes in the specific implementation methods and application scope. Therefore, the content of this specification should not be construed as a limitation of the present invention.

Claims

1. A simulation system for the mechanism of brain injury, characterized in that, include: The data acquisition module is used to acquire the range of head shaking frequency of the target test subject and the displacement-time curves under different shaking directions; The horizontal axis of the displacement-time curve is time, and the vertical axis of the displacement-time curve is the swaying amplitude. The simulation module is used to simulate and determine the biomechanical data of the brain tissue injury formation process under different shaking injury modes based on the shaking frequency range, the displacement-time curve and the whole human finite element model; the shaking injury mode is the injury mode determined by the shaking frequency, shaking amplitude and shaking direction. The result determination module is used to determine, based on the biomechanical data, the location of brain tissue damage in adult shake syndrome under different shaking injury modes, as well as the formation characteristics and injury mechanism of adult shake syndrome.

2. The brain injury mechanism simulation system according to claim 1, characterized in that, The data acquisition module includes: The first data acquisition unit is used to acquire the shaking frequency of the target test subject recorded by the three-dimensional motion capture system; the shaking frequency range is the range of hand shaking frequency generated when the target test subject shakes the weight in his / her hand within a set time. The second data acquisition unit is used to acquire the displacement-time curve of the target test subject recorded by the three-dimensional motion capture system; the displacement-time curve is determined based on the head movement trajectory of the target test subject; the head movement trajectory is the movement trajectory generated by the target test subject when performing a head shaking experiment within a set time.

3. The brain injury mechanism simulation system according to claim 1, characterized in that, The full-body finite element model includes at least a cranial model and a neck model; the simulation module includes: The shaking injury mode determination unit is used to determine multiple shaking injury modes based on the shaking frequency range, the displacement-time curve, and the shaking direction. The simulation unit is used to perform finite element simulations on the cranial model using different shaking injury methods to determine the biomechanical data of the brain tissue damage formation process under different shaking injury methods.

4. The brain injury mechanism simulation system according to claim 3, characterized in that, The simulation module further includes: The cranial model verification unit is used to load translational impact experiments, translational rotational impact experiments, and translational impact experiments, and to verify the effectiveness of the cranial model based on the translational impact experiments, the translational rotational impact experiments, and the translational impact experiments.

5. The brain injury mechanism simulation system according to claim 1, characterized in that, The result determination module includes: A data processing unit is used to process the biomechanical data; the processed biomechanical data includes CSDM. 0.25 HIC 36 MPS, brain pressure, and Von Mises stress; The result determination unit is used to determine the location of adult shake syndrome under different shaking injury modes, as well as the formation characteristics and injury mechanism of adult shake syndrome, based on the processed biomechanical data.

6. The brain injury mechanism simulation system according to claim 5, characterized in that, The result determination unit includes: The load curve determination subunit is used to determine the load curves of different brain regions under different shaking injury methods based on the processed biomechanical data; the horizontal axis of the load curve is time, and the vertical axis of the load curve is load. The site of injury determination subunit is used to determine the site of brain tissue damage in adult shake syndrome under different shaking injury modes by using the load curve and brain tissue tolerance threshold. The formation characteristics and injury mechanism determination unit is used to determine the strain cloud map based on the processed biomechanical data, and to determine the formation characteristics and injury mechanism of adult shake syndrome under different shaking injury modes based on the strain cloud map.

7. An electronic device, characterized in that, Includes a three-dimensional motion capture system and a brain injury mechanism simulation system as described in any one of claims 1-6.

8. An electronic device according to claim 7, characterized in that, The three-dimensional motion capture system is used for: The shaking frequency of the target test subject is recorded; the shaking frequency range is the range of hand shaking frequency generated when the target test subject shakes the weight in his / her hand within a set time period. The displacement-time curve of the target test subject is recorded; the displacement-time curve is determined based on the head movement trajectory of the target test subject; the head movement trajectory is the movement trajectory generated by the target test subject when performing a head shaking experiment within a set time period.

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