A biomechanical simulation module and measurement method for the chest cavity that mimics the shape of a human rib.

Abstract

This invention relates to the field of automotive testing technology, specifically to a biomechanical performance simulation module and measurement method for a human-like ribcage. It includes a fixed support, rib units, and an arm unit. The fixed support comprises a shoulder support and a chest support, both fixedly connected to the rib units. The rib units include inner ribs, outer ribs, and displacement sensors. An inner layer pad is located at the center of the inner side of the inner ribs, and the outer ribs are semi-open rings with an outer layer pad located at the center of their outer side. The inner and outer pads are fixedly connected by screws. Openings are provided along the centerlines of the inner ribs, outer ribs, inner pads, and outer pads. One end of the displacement sensor is fixedly connected to the chest support, and the other end is fixed in the opening via a pin. An arm connecting block is fixedly connected to the outer side of the rib unit at the shoulder support, and is fixedly connected to the arm unit. This solution can more accurately simulate and evaluate the damage to a pedestrian's chest in a side-impact accident.

Description

Technical Field

[0001] This invention relates to the field of automotive testing technology, specifically to a biomechanical performance simulation module and measurement method for a human rib-like chest. Background Technology

[0002] In various traffic accidents, the pedestrian's chest is a highly vulnerable area due to its unique physiological structure and location, especially in side-impact accidents where pedestrians may suffer injuries while crossing the road, where the risk of chest injury increases significantly. Accident statistics and simulation experiments clearly indicate that the pedestrian's chest is more likely to suffer serious injuries in side-impact collisions than in frontal collisions, and the high disability rate poses a direct and serious threat to the life safety of pedestrians.

[0003] However, the current pedestrian protection assessment system is relatively weak in evaluating the effectiveness of chest protection for pedestrians. Specifically, the following technical problems urgently need to be addressed:

[0004] 1. Lack of targeted assessment methods: Currently, there is no systematic assessment method to accurately measure the protective effect of different vehicle models on pedestrian chests in accidents. This results in a lack of scientific basis and effective guidance in vehicle design and pedestrian protection strategy formulation.

[0005] 2. Lack of efficient simulation tools: Existing pedestrian chest simulation devices differ significantly from the actual human rib structure in terms of structure and materials, making it difficult to achieve highly biorealistic simulations in impact experiments. This difference not only limits the accuracy and reliability of impactors in assessing pedestrian chest safety performance but also hinders the development of related research.

[0006] 3. Insufficient simulation of side impacts: Most pedestrian chest simulation devices and evaluation methods focus on frontal or specific angle impact simulations, while the simulation of high-risk side impact scenarios is insufficient. This results in a significant gap and shortcoming in evaluating the effectiveness of vehicles in protecting pedestrians' chests from the side.

[0007] Therefore, in order to solve the above problems, it is urgent to develop a new and efficient biomechanical performance simulation module and measurement method for the human chest using an artificial rib. Summary of the Invention

[0008] The purpose of this invention is to propose a biomechanical performance simulation module and measurement method for the chest of a human rib, which can accurately simulate the damage to the chest of a pedestrian in a side impact accident.

[0009] To achieve the above objectives, in a first aspect, embodiments of this disclosure provide a biomechanical performance simulation module for the chest of a human-like rib, comprising a fixation bracket, rib units, and arm units; the fixation bracket includes a shoulder bracket and a chest bracket, both of which are fixedly connected to rib units; the rib unit includes an inner ring rib, an outer ring rib, and a displacement sensor, the outer ring rib being semi-open-ring shaped, an inner layer pad being disposed at the center of the inner side of the inner ring rib, and an outer layer pad being disposed at the center of the outer side of the outer ring rib, the inner layer pad and the outer layer pad being fixedly connected by screws; openings are provided on the center lines of the inner ring rib, the outer ring rib, the inner layer pad, and the outer layer pad; one end of the displacement sensor is fixedly connected to the chest bracket, and the other end is fixed in the opening by a pin; an arm connecting block is fixedly connected to the outer side of the rib unit at the shoulder bracket, the arm connecting block is fixedly connected to a U-shaped clamp, the U-shaped clamp is fixed to both sides of the arm connecting block by bolts, and the U-shaped clamp is fixedly connected to an arm support plate.

[0010] Beneficial effects of the basic scheme: The simulation module in this scheme can simulate the chest response of a pedestrian when hit from the side, taking into account the protection of the pedestrian's chest safety by the vehicle. This can not only improve the pedestrian safety assessment indicators of the vehicle model and provide guidance for the vehicle's shape during the vehicle development process, but also reduce the injuries suffered by pedestrians in accidents and lower the traffic accident casualty rate.

[0011] Since injuries to the pedestrian's chest caused by a vehicle in a side-impact collision generally do not involve the non-impact side, the simulation module in this design only simulates the pedestrian's hemi-chest structure. This simplifies the structure, reduces weight, and lowers the requirements for the impactor launching device. The modular design, including independently replaceable or adjustable components such as the fixing bracket, rib units, and arm units, not only facilitates customized configuration according to specific experimental needs but also improves the module's versatility and reusability, reducing experimental costs and time.

[0012] The simulation module's rib unit comprises inner and outer rib rings, supplemented by inner and outer pads. This structure highly simulates the complex anatomical structure and biomechanical properties of the human chest. The inner rib rings closely replicate the curved shape of human ribs, while the semi-open ring shape of the outer rib rings resembles the contour of the human chest cavity, allowing the module to move laterally, forward / backward, and vertically. This helps to more accurately simulate the actual movement of pedestrian ribs during an accident. An arm unit simulates a pedestrian's arm to assess the impact of arm position on chest injury during a side impact.

[0013] The design of the inner and outer pads ensures that the inner and outer ribs move in the same direction during testing. This allows the deformation of the simulated module caused by the impact to be measured more directly and effectively by the displacement sensor, ensuring the accuracy of the side impact test results.

[0014] This technical solution uses an arm unit to simulate an arm, enabling the assessment of chest injuries under the most severe conditions. The U-shaped clamp allows for lateral rotation of the arm, better transferring force to the chest during experiments. A locking nut secures the arm support plate to the U-shaped clamp, ensuring the arm angle remains constant during testing, but can be adjusted as needed for different test conditions.

[0015] As a feasible preferred embodiment, the chest brace is fixedly connected to a launcher, the center of which is aligned with the center of gravity of the chest impactor.

[0016] As a feasible preferred option, the chest support is made by connecting two side plates using a support shaft with internal threads and screws.

[0017] As a feasible preferred embodiment, the two ends of the inner and outer ribs are fixed to the chest support with screws, the outer sides of the inner and outer ribs are in contact with the chest support, and the screw heads are located on the inner side of the inner or outer ribs.

[0018] As a feasible preferred solution, the chest support is fixedly connected with several rib units, each rib unit having a height of 40mm and a gap of 16mm between each rib unit.

[0019] As a feasible preferred embodiment, the inner side of the inner ring ribs is bonded with damping material by an adhesive; the outer side of the outer ring ribs is bonded with an outer layer of rubber.

[0020] As a feasible preferred option, chest foam is bonded to the outside of the rib unit at the chest support, and the outside of the chest foam is covered with a layer of rubber.

[0021] As a feasible preferred embodiment, the arm support sheet is covered with arm foam, and the arm foam has openings in the shape of the arm support sheet, so that the arm foam can be covered to the surface of the arm support sheet by adhesive.

[0022] As a feasible preferred option, the arm support plate is made of steel.

[0023] Secondly, this disclosure provides a method for measuring the biomechanical properties of a human chest using a simulated human rib, employing the aforementioned simulated human rib chest biomechanical properties module. By measuring the change in the length of the displacement sensor sleeve and the deflection angle, the compression amount of the chest upon lateral impact is obtained. The formula is as follows:

[0024]

[0025] In the formula, The distance between the sensor hinge points. for Spacing between hinge points of the time sensor for Spacing between hinge points of the time sensor; For the sensor hinge point spacing in Projection along the axial direction, for The distance between the hinge points of the time sensor is Projection along the axial direction, for The distance between the hinge points of the time sensor is Projection along the axial direction; The angle between the sensor's axis and the Y-axis. for Time and angle, for Time and angle; This refers to the lateral compression of the impactor. Attached Figure Description

[0026] Figure 1 This is a schematic diagram of a fixation bracket for a chest biomechanical performance simulation module that mimics human ribs.

[0027] Figure 2 This is a schematic diagram of the rib unit of a chest biomechanical performance simulation module that mimics human ribs.

[0028] Figure 3 This is a schematic diagram of a chest biomechanical performance simulation module that mimics human ribs.

[0029] Figure 4 This is a side view of a chest biomechanical performance simulation module that mimics human ribs.

[0030] Figure 5 This is a schematic diagram of the deformation of a rib unit in a biomechanical performance simulation module for a human-like rib.

[0031] Figure 6 This is a top view of a chest biomechanical performance simulation module that mimics human ribs.

[0032] Figure 7 This is a schematic diagram of the structural parameters of a displacement sensor for a chest biomechanical performance simulation module that mimics human ribs.

[0033] Figure 8 This is a schematic diagram showing the forces acting along the coronal axis and the vertical axis.

[0034] Figure 9 This is a schematic diagram of the structure of an electronic device according to an embodiment of the present invention. Detailed Implementation

[0035] To make the technical solution and advantages of this application clearer, the technical solution of the present invention will be further described in detail below with reference to the accompanying drawings. It is understood that the specific embodiments described herein are only some embodiments of the present invention, and are only used to explain this application, not to limit it. It should be noted that the technical features or combinations of technical features described in the following embodiments should not be considered isolated; they can be combined with each other to achieve better technical effects. The same reference numerals appearing in the accompanying drawings of the following embodiments represent the same features or components, and can be applied to different embodiments.

[0036] Furthermore, unless otherwise defined, the technical or scientific terms used in this invention description shall have the ordinary meaning understood by one of ordinary skill in the art to which this invention pertains.

[0037] The present invention will now be described in further detail with reference to the accompanying drawings:

[0038] Reference numerals: 1. Shoulder support; 2. Chest support; 3. Support shaft; 4. Side plate; 5. Launcher; 6. Mounting plate; 7. Rubber; 8. Chest foam; 9. Arm foam; 10. Arm support plate; 11. Locking nut; 12. U-clamp; 13. Arm connecting block; 14. Damping material; 15. Inner ring rib; 16. Outer ring rib; 17. Outer layer rubber; 18. Inner layer pad; 19. Pin shaft; 20. Outer layer pad; 21. Displacement sensor; 500. Electronic device; 501. Processor; 502. Communication interface; 503. Memory; 504. Bus.

[0039] Example 1

[0040] A biomechanical simulation module for the chest of a human-like rib includes a fixation frame, rib units, and arm units.

[0041] Reference Figure 1 The fixed support includes a shoulder support 1 and a chest support 2. The chest support 2 is formed by connecting two side plates 4 using a support shaft 3 with internal threads and screws. The chest support 2 is fixedly connected to a launcher 5. The center of the launcher 5 is at the same height as the center of gravity of the chest biomechanical performance simulation module. The launcher 5 is connected to the launch device through a pin. Torque loading can be set in the launcher and the pin.

[0042] The shoulder support 1 is fixedly connected to rib units for simulating the mechanical properties of the shoulder, and the chest support is fixedly connected to several rib units for simulating the mechanical properties of the chest. In this embodiment, one rib unit is provided at the shoulder and three rib units are provided at the chest. The rib units at the shoulder support and the rib units at the chest support have similar structures. The outer ring ribs of the rib units at the shoulder support are slightly smaller in the anterior-posterior direction than the outer ring ribs of the rib units at the chest support, which corresponds to the slightly smaller size of the upper ribs of the human body.

[0043] The module has an overall thickness of 218mm and a width of 149mm. The individual rib unit in the rib unit group at the chest support is 40mm high, and the gap between the rib units is 16mm. From an ergonomic perspective, a person's height is closely related to their center of gravity, moment of inertia, and radius of rotation. By setting these parameters, the biomechanical performance simulation module for the human chest closely approximates the dimensions of a pedestrian, thus avoiding significant deviations in chest compression values ​​(symbolizing chest injury) from pedestrian measurements. This ensures that the data obtained from this module can represent the degree of injury suffered by a person in a side impact. The device can also adjust the rib spacing according to the anatomical structure of the human chest at different percentiles, allowing the chest height to adapt to different percentages of the human body.

[0044] Reference Figure 2 Each rib unit includes an inner ring rib 15, an outer ring rib 16, and a displacement sensor 21. In this embodiment, a 2D IR-TRACC displacement sensor is used. A damping material 14 is bonded to the inner side of the inner ring rib 15 with an adhesive; the damping material 14 is used to absorb a certain amount of impact energy and reduce rebound. An outer layer of rubber 17 is bonded to the outer side of the outer ring rib 16, which provides a certain buffering effect for the inner and outer ring ribs, avoiding direct contact between them. An inner layer pad 18 is provided at the center of the inner side of the inner ring rib 15, and an outer layer pad 20 is provided at the center of the outer side of the outer ring rib 16. The inner layer pad 18 and the outer layer pad 20 are fixedly connected by several screws. In this embodiment, the screws pass through the outer layer pad 20, the outer ring rib 16, the inner ring rib, and the inner layer pad 18 in sequence, thereby ensuring consistent movement of the components on the impact side. Openings are provided on the center lines of the inner ring rib 15, the outer ring rib 16, the inner layer pad 18, and the outer layer pad 20. One end of the displacement sensor 21 is fixedly connected to the chest support 2, and the other end (the ring end) is fixed in the opening through the pin 19.

[0045] Reference Figure 4 The chest foam 8 is bonded to the outside of the rib unit at the chest support. The outside of the foam is covered with a layer of rubber 7 to simulate skin. The two ends of the rubber are pressed and fixed to the support 2 by the mounting plate 6.

[0046] The inner rib 15 and outer rib 16 are fixed to the chest support 2 at both ends with screws. The outer sides of the inner rib 15 and outer rib 16 are in contact with the chest support 2, and the screw heads are located inside the inner rib 15 or outer rib 16. In this technical solution, the inner ribs highly replicate the arc shape of human ribs, while the semi-open ring shape of the outer ribs is similar to the contour of the human chest cavity. This allows the ribs to not only move laterally but also move in the front-back and up-down directions, better simulating the response of pedestrian ribs in an accident.

[0047] Reference Figure 3An arm connecting block 13 is fixedly connected to the outer side of the rib unit at the shoulder support. A U-shaped clip 12 is fixedly connected to the arm connecting block 13, and the U-shaped clip 12 is fixedly connected to both sides of the arm connecting block 13 by bolts. An arm support plate 10 is fixedly connected to the U-shaped clip 12 by a locking nut 11. The arm support plate 10 is preferably made of steel. The arm foam 9 has openings shaped like the arm support plate 10, allowing the arm foam 9 to be adhesively applied to the surface of the arm support plate 10. The U-shaped clip 12 can rotate around the arm connecting block 13 at a certain angle, thereby simulating different arm lifting angles and positions. During a pedestrian-vehicle collision, different arm movements affect the severity of chest injuries. If the arm is located between the chest and the head covering, it will aggravate chest injuries. This technical solution simulates the arm through an arm unit, allowing for the assessment of chest injuries under the most severe conditions. The U-shaped clamp 12 allows the arm to rotate laterally, which can better transfer the force of the arm to the chest during a side impact. The arm support plate is fixed to the U-shaped clamp 12 with a locking nut, so that the arm angle of the arm unit remains stable during the test. However, the arm angle can be adjusted as needed in different test conditions. By simulating the different positions of the arm between the chest and the head cover, the damage to the chest under the most severe conditions can be evaluated, which provides an important reference for improving vehicle safety design.

[0048] Before using the chest impactor, calibration is required. The impactor is fixed on a calibration test bench, and a standard calibration hammer is used to impact the four rib units in this embodiment, referring to... Figure 5 As shown in the figure (disp represents displacement and time represents time), if the maximum deformation of the rib element is within the calibration range, the calibration is passed.

[0049] Example 2

[0050] The technical feature that distinguishes this embodiment from Embodiment 1 is that it provides a method for measuring the biomechanical properties of the human chest using a human-like rib, and uses chest compression to assess human chest injury.

[0051] Reference Figure 6 and Figure 7 The compression of the chest upon side impact is obtained by measuring the change in the length of the sleeve of displacement sensor 21 and the deflection angle, as shown in the following formula:

[0052]

[0053] In the formula, The distance between the sensor hinge points. for Spacing between hinge points of the time sensor for Spacing between hinge points of the time sensor; For the sensor hinge point spacing in Projection along the axial direction, for The distance between the hinge points of the time sensor is Projection along the axial direction, for The distance between the hinge points of the time sensor is Projection along the axial direction; The angle between the sensor's axis and the Y-axis. for Time and angle, for Time and angle; This refers to the lateral compression of the impactor.

[0054] Example 3

[0055] In crash tests, the launch force directly affects whether a chest biomechanical performance simulation module, which mimics human ribs, can accurately reflect the damage to the chest. Due to differences in the geometry of different vehicles, the force experienced by a pedestrian's chest when it contacts the helmet also varies significantly. Therefore, the launch force used when testing different vehicle models with a chest impactor also differs.

[0056] This disclosure provides a method for determining the emission force of a biomechanical performance simulation module for the chest cavity, which mimics the shape of a human rib.

[0057] Step S100, construct the simulation model, including:

[0058] Step S101: Import the finite element model of the vehicle under test and the 50th percentile pedestrian model of TB 024 posture, and simultaneously establish a shoe model that meets J2782; adjust the center point of the pedestrian's hip to align with the center line of the vehicle's hood, and establish a side impact condition between the person and the vehicle; ensure that the height of the vehicle and the pedestrian are consistent with the actual height; constrain the vehicle's degrees of freedom so that it can only move in the direction of the vehicle speed, which is 40 km / h; set the friction coefficient between the human model and the vehicle to 0.3.

[0059] Step S102: Define the planar positions of the neck and chest: the neck plane is the cross-section passing through the lowest point of the C6 cervical vertebra, and the chest plane is the cross-section passing through the middle crest of the seventh rib. Define the output of the cross-sectional force on each of the two planes.

[0060] Step S103: Output the cross-sectional force curves of the two planes in the simulation results, and select the two time points of chest contact with the headgear and chest leaving the headgear according to the impact animation.

[0061] Step S200, calculate the section force, refer to Figure 8To simplify the test conditions to some extent, the motion of the human body along the sagittal axis (Y-axis) is ignored. Therefore, only the force conditions in the coronal axis (X-axis) and vertical axis (Z-axis) are considered, as shown in the following formula:

[0062]

[0063]

[0064] In the formula, This represents the average force acting on the neck along the X-axis; This represents the average force acting on the neck along the Z-axis; F NECKX This represents the force exerted on the neck along the X-axis; F NECKZ This represents the force exerted on the neck along the Z-axis; t 1 represents the time the chest is in contact with the hairnet; t 2 represents the time the chest is removed from the headband.

[0065] Similarly, the average force in the chest plane along the X and Z axes can be calculated. and .

[0066] Step S300: Calculate the emission force using the following formula:

[0067]

[0068]

[0069]

[0070] In the formula, This represents the launching force applied to the impactor along the X-axis; This represents the launching force applied to the impactor along the Z-axis; This indicates the magnitude of the launching force.

[0071] This disclosure also provides a system for determining the emission force of a human chest biomechanical performance simulation module, which utilizes the aforementioned method for determining the emission force of a human chest biomechanical performance simulation module.

[0072] This disclosure also provides a storage medium storing a computer program. When the computer program is executed by a processor, it can implement all the steps of the above-described method for determining the emission force of a human chest biomechanical performance simulation module.

[0073] Those skilled in the art will understand that all or part of the process in the method for determining the emission force of a human chest biomechanical performance simulation module can be implemented by a computer program instructing related hardware. The program can be stored in a non-volatile computer-readable storage medium. When executed, the program can include the processes of various embodiments of the method for determining the emission force of a human chest biomechanical performance simulation module. Any references to memory, storage, databases, or other media used in the embodiments provided in this application can include non-volatile and / or volatile memory. Non-volatile memory may include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM), or flash memory. Volatile memory may include random access memory (RAM) or external cache memory. By way of illustration and not limitation, RAM is available in a variety of forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), dual data rate SDRAM (DDRSDRAM), enhanced SDRAM (ESDRAM), synchronous link DRAM (SLDRAM), RAMbus direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM), and memory bus dynamic RAM (RDRAM), etc.

[0074] This application also provides an electronic device, including a memory, a processor, and a computer program stored in the memory and executable on the processor. When the processor executes the program, it implements the steps of the above-described method for determining the emission force of a human chest biomechanical performance simulation module. In this application embodiment, the processor is the control center of the computer system; it can be a physical machine processor or a virtual machine processor.

[0075] Reference Figure 9The electronic device 500 includes at least one processor 501, at least one communication interface 502, at least one memory 503, and at least one bus 504. The bus 504 is used for communication between these components, the communication interface 502 is used for signaling or data communication with other node devices, and the memory 503 stores machine-readable instructions executable by the processor 501. When the electronic device 500 is running, the processor 501 and the memory 503 communicate via the bus 504. When the machine-readable instructions are invoked by the processor 501, they execute the steps of the method for determining the emission force of a human chest biomechanical performance simulation module as described above. The above description is merely an embodiment of the present invention. Commonly known structures and characteristics are not described in detail here. Those skilled in the art are aware of all common technical knowledge in the field prior to the application date or priority date, are able to access all existing technologies in the field, and have the ability to apply conventional experimental methods prior to that date. Those skilled in the art can improve and implement this solution based on the inspiration provided in this application and their own capabilities. Some typical known structures or methods should not be obstacles for those skilled in the art to implement this application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the structure of this invention, and these should also be considered within the scope of protection of this invention. These modifications and improvements will not affect the effectiveness of the invention or the practicality of the patent. The scope of protection claimed in this application shall be determined by the content of its claims, and the specific embodiments described in the specification can be used to interpret the content of the claims.

Claims

1. A biomechanical performance simulation module for the chest cavity, mimicking human ribs, characterized in that: The device includes a fixed support, rib units, and an arm unit. The fixed support includes a shoulder support and a chest support, both of which are fixedly connected to rib units. Each rib unit includes an inner ring rib, an outer ring rib, and a displacement sensor. The outer ring rib is semi-open-ring shaped. An inner layer pad is located at the center of the inner side of the inner ring rib, and an outer layer pad is located at the center of the outer side of the outer ring rib. The inner and outer layer pads are fixedly connected by screws. Openings are provided on the center lines of the inner ring rib, outer ring rib, inner layer pad, and outer layer pad. One end of the displacement sensor is fixedly connected to the chest support, and the other end is fixed in the opening by a pin. An arm connecting block is fixedly connected to the outer side of the rib unit at the shoulder support. A U-shaped clamp is fixedly connected to the arm connecting block, and the U-shaped clamp is fixed to both sides of the arm connecting block by bolts. An arm support plate is fixedly connected to the U-shaped clamp.

2. The biomechanical performance simulation module for a human-like ribcage in the chest according to claim 1, characterized in that: The chest support is fixedly connected to the launcher, and the center of the launcher is at the same height as the center of gravity of the chest impactor.

3. The biomechanical performance simulation module for a human-like ribcage in the chest according to claim 2, characterized in that: The chest support is made by connecting two side plates using a support shaft with internal threads and screws.

4. The chest biomechanical performance simulation module for a human-like rib as described in claim 1, characterized in that: The inner and outer ribs are fixed to the chest support with screws at both ends. The outer sides of the inner and outer ribs are in contact with the chest support, and the screw heads are located on the inner side of the inner or outer ribs.

5. The chest biomechanical performance simulation module for a human-like rib as described in claim 4, characterized in that: The chest support is fixedly connected to several rib units, each rib unit is 40mm high, and the gap between each rib unit is 16mm.

6. A biomechanical performance simulation module for a human-like rib chest as described in claim 1, 4, or 5, characterized in that: The inner side of the inner ring ribs is bonded with damping material using adhesive; the outer side of the outer ring ribs is bonded with an outer layer of rubber.

7. The biomechanical performance simulation module for a human-like ribcage in the chest according to claim 1, characterized in that: The chest foam is bonded to the outside of the rib unit at the chest support, and the outside of the foam is covered with a layer of rubber.

8. The biomechanical performance simulation module for a human-like rib chest according to claim 7, characterized in that: The arm support plate is covered with arm foam, and the arm foam has openings shaped like the arm support plate inside, so that the arm foam can be covered on the surface of the arm support plate by adhesive.

9. The biomechanical performance simulation module for a human-like rib chest according to claim 8, characterized in that: The arm support plate is made of steel.

10. A method for measuring the biomechanical properties of a human chest cavity modeled after human ribs, characterized in that: The chest biomechanical performance simulation module of the anthropomorphic rib as described in any one of claims 1-9 is used to obtain the compression amount of the chest upon lateral impact by measuring the change in the length of the displacement sensor sleeve and the deflection angle. The formula is as follows: In the formula, The distance between the sensor hinge points. for Spacing between hinge points of the time sensor for Spacing between hinge points of the time sensor; For the sensor hinge point spacing in Projection along the axial direction, for The distance between the hinge points of the time sensor is Projection along the axial direction, for The distance between the hinge points of the time sensor is Projection along the axial direction; The angle between the sensor's axis and the Y-axis. for Time and angle, for Time and angle; This refers to the lateral compression of the impactor.

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