Intelligent spinal column bionic model

Abstract

The present invention discloses an intelligent spinal bionic model and relates to the technology of surgical simulation instruments. It includes a model base and a model case, a bionic spinal column body installed on the model base and having a development effect, and a simulated muscle layer and a simulated skin layer enclosing the bionic spinal column body. A bionic nerve body having a contact alarm mechanism is installed in the cavity inside the bionic spinal column body. [Effects] This invention creates a spinal bionic model for surgical simulation through precise design and material selection, faithfully reproducing several important processes in actual spinal surgery (X-ray development, simulation of internal human structure, simulation of the surgical water environment, nerve contact alarm, etc.). It provides physicians with a highly simulated surgical training platform, contributing to the rapid improvement of spinal endoscopic surgical skills and clinical experience.

Description

Technical Field

[0001] The present invention relates to the technical field of surgical simulation instruments, and particularly to an intelligent spinal bioionic model.

Background Art

[0002] Traditional spinal or partial spinal (such as vertebral column) surgical training methods rely on the observation of anatomical specimens and the study of image materials. These methods provide a basic understanding of the spinal structure, but there are obvious limitations in aspects such as the simulation of the actual surgical process, the response to complex clinical situations, and the improvement of surgical decision-making ability. Therefore, seeking more combat-like training means has become an urgent issue in improving the level of spinal endoscopy surgery. In response to this demand, several simulation spinal models are used in surgical skills training in the market.

[0003] However, the existing simulated spinal surgery models still have significant deficiencies in the simulation of the actual surgical site and the human body's internal environment. For example, the design of many current models is directly based on static anatomical spines, lacking the important X-ray imaging process before surgery. Furthermore, the existing models cannot sufficiently simulate the dynamic performance of the human body's internal environment (especially physiological elements such as blood and body fluids) in terms of material selection and structural design. There are dense distributions of blood vessels, nerves, and various soft tissues around the spine, and precise operations in an exudate environment are always required during the surgical process. At the same time, using saline to clarify the surgical field is also one of the standard operations. In addition, many commercially available simulated spinal models adopt a frame structure, making it difficult to truly reproduce the texture of human tissues during surgery, the fluid dynamics, and the possible bleeding situations during surgery. Such a simplified treatment of the complexity of the internal environment makes it difficult for doctors to obtain a sense of presence during simulation training, and it is difficult to comprehensively train the accurate operation under complex physiological conditions and the ability to respond to emergencies.

[0004] Solving the above-mentioned technical problems is the issue faced by the present invention. [Overview of the project]

[0005] To address the shortcomings of conventional technology, this invention provides a rationally designed, safe, and reliable intelligent spinal bionic model, offering physicians a comprehensive and three-dimensional surgical skills training tool that contributes to improving surgical skills and reducing actual surgical risks.

[0006] To achieve the aforementioned objectives, the present invention provides an intelligent spinal bionic model comprising a model base and a model case, a bionic spinal column body installed on the model base and having a development effect, and a simulated muscle layer and a simulated skin layer enclosing the bionic spinal column body. A bionic nerve body having a contact alarm mechanism is installed in the cavity inside the bionic spinal column.

[0007] In this model base, an inverted trapezoidal spine holder is installed, and a simulated muscle layer with a bionic spine is placed inside the spine holder.

[0008] The spinal column holder includes an embedded base embedded in the model base, fan-shaped plates installed at both ends of the embedded base, and inclined plates installed on both sides of the embedded base. A vertical plate is installed at the upper end of the inclined plate. The upper end surface of the embedded base is provided with an internal groove that fits with the lower end surface of the bionic spinal column, and is used to fix the bionic spinal column. The spinal column holder is made of polyester ammonia material and is integrally molded by foam, and the upper end surface of the fan-shaped plates has a curved shape that conforms to the back of the human body. The bionic spinal column can be realized by methods such as 3D printing, and its shape and structure can be installed as a full-size bionic lumbar skeletal member of L1, L2, L3, L4, L5, S1 as needed. The lumbar canal of the bionic spinal column can further contain a posterior longitudinal ligament, bionic nerve bundles, epidural fat, ligamentum flavum, interspinous ligaments, etc., and a supraspinous ligament can further be installed on the upper surface of the lumbar spinous process.

[0009] A skin layer receiving surface is provided on the upper end surface of the vertical plate at the upper end of the inclined plate, and the simulated skin layer is placed on the upper end surface of the simulated muscle layer, with both sides hanging down to the skin layer receiving surface. The simulated skin layer has a two-layer structure and includes a simulated fat inner layer and a simulated epidermal layer. The simulated muscle layer is cast in one piece. The model base is provided with a cavity for enhancing development, and the embedded base is installed above the cavity.

[0010] The spinal column holder is filled with a liquid to simulate a surgical water environment, and the spinal column holder is provided with an inlet and an overflow port, which are used to connect the inside of the spinal column holder with an external water source to form a fluid.

[0011] To better achieve the aforementioned objectives, the present invention further provides a bionic vertebral body. The bionic vertebral body comprises a core material layer (i.e., bionic cancellous bone) and an outer material layer (i.e., bionic cortical bone) attached to the outside of the core material layer, and the bionic vertebral body is a hard layer having a developing effect. The method for manufacturing the bionic spinal column includes the following steps. S1, a method for manufacturing a core material layer, in which rigid polyurethane foam raw materials are stirred and mixed, then injected into a lumbar skeletal mold and foamed to obtain a core material layer. S2, a method for producing the outer material layer raw material, wherein a styrene-acrylic emulsion and a SAN emulsion are co-mixed to obtain the outer material layer liquid material. S3, a method for manufacturing a bionic lumbar vertebral skeleton, wherein an outer material layer liquid material is attached to the outer surface of the core material layer using a spray coating or immersion process, ultimately forming a bionic lumbar vertebral skeleton having developing properties.

[0012] The specific manufacturing steps for the core material layer are as follows: In S101, 100 parts by weight of polyether polyol, 1 part by weight of polydimethylsiloxane (PDMS), 30 parts by weight of 1,4-butanediol, 0.2 parts by weight of catalyst A33, 1 part by weight of triethanolamine, 10 parts by weight of trimethylolpropane, and 0.8 parts by weight of deionized water are uniformly stirred in a mixing tank, and the stirring speed is maintained at 1000 rpm. In step S102, simultaneously with the stirring in step S101, 170 parts by weight of polyphenylpolymethylene polyisocyanate are slowly added, the stirring speed is adjusted to 500 rpm, and the mixture is stirred at high speed for 15 seconds. In S103, after high-speed stirring, the material is quickly injected into a skeletal mold, a sealed reaction is carried out, the internal temperature of the mold is controlled to 25°C, and the solidification time is set to 24 hours to obtain a solid core material layer.

[0013] The specific manufacturing steps for the aforementioned outer material layer liquid material are as follows: In S201, 10-20 parts by weight of styrene, 20-30 parts by weight of acrylic acid ester monomer, 0.5-1.5 parts by weight of emulsifier, 0.1-3.0 parts by weight of chain transfer agent, and 10-40 parts by weight of deionized water are mixed in reactor A and stirred to form a preliminary emulsion. In step S202, 10-60 parts by weight of deionized water, 0.5-3 parts by weight of initiator, 0.5-1.0 part by weight of emulsifier, and 1-30 parts by weight of developer are added to reactor B, the temperature is raised to 80°C while stirring, the preliminary emulsion from step S201 is added dropwise under a nitrogen atmosphere, emulsion polymerization is carried out for 1-2 hours, and after the reaction is complete, the mixture is cooled to room temperature to obtain the emulsion. In S203, 30 parts by weight of styrene, 20 parts by weight of acrylonitrile, 1.0 part by weight of emulsifier, 0.5 parts by weight of potassium persulfate, and 100 parts by weight of deionized water are added to reactor C, and a styrene-acrylonitrile copolymer emulsion is formed by emulsion polymerization at an appropriate stirring speed. In step S204, the emulsion obtained in step S202 is stirred at a constant temperature in reactor B, 5-40 parts by weight of the styrene-acrylonitrile copolymer emulsion prepared in step S203 is slowly added, and after uniform stirring, it is cooled to room temperature, 0.1-1.0 parts by weight of pigment is added, and after uniform stirring, an outer material layer liquid material having developing properties is obtained.

[0014] Of these, step S3 is specifically as follows: The outer material layer liquid material is attached to the surface of the solid core material layer using a spray coating or immersion process.

[0015] The bionic spinal column with X-ray developing capabilities provided by this invention has extremely excellent practical effects. (1) Significant improvement in development effect: By adding the water-soluble developer KI to the emulsion synthesis process, uniform mixing of the developer and emulsion was achieved. This mixing method allows the developer to be distributed in the emulsion in a finer form, and compared to conventional coarse-grained developers, this fine liquid distribution significantly enhances the development contrast and clarity under X-ray. Therefore, it is possible to create more effective contrast in the image formation process, significantly improving the physician's ability to distinguish skeletal structures and lesion details, which is extremely important for precise diagnosis and treatment planning. (2) Enhanced environmental and biocompatibility: Compared to developing materials that rely on conventional high-concentration inorganic developers (such as barium and iodine), the water-soluble developer KI used in the present invention has clear advantages in terms of safety and biocompatibility. The low-toxicity water-soluble developer further reduces environmental and patient health risks and meets the stringent requirements for environmental protection and human safety demanded by modern medical materials. (3) Improvement of coating mechanical properties: The addition of SAN resin in the present invention not only improves the development performance of the emulsion but also enhances the mechanical properties of the material by improving hardness and wear resistance. As a result, the modified styrene-acrylic emulsion of the present invention is particularly suitable for simulating bone materials of people of different age groups and with different medical conditions, such as the bones of children, adults, the elderly, and patients with osteoporosis. (4) Wide range of applications and flexibility: In addition to the application of medical bionic bones, the colorless and transparent characteristics and adjustable color characteristics of the SAN resin-modified styrene acrylic emulsion also have broad application possibilities in fields such as industrial non-destructive inspection. Different color options can be adjusted according to specific application requirements, providing more customized solutions.

[0016] To better achieve the above object of the invention, the present invention further provides a simulated nerve body having a contact warning mechanism. The simulated nerve body includes a simulated nerve main body and a warning mechanism installed on the simulated nerve main body. The warning mechanism includes a sensing coil attached to the simulated nerve main body, a power supply electrically connected to the sensing coil, and an external controller that receives a sensing signal and issues a warning after processing.

[0017] The simulated nerve main body includes an inner layer tube, the sensing coil is wound around the outer wall of the inner layer tube, and the outside of the sensing coil is covered by an outer layer covering wall.

[0018] When the simulated nerve main body is a single path (or when only the main nerve is simulated), the sensing coil is continuously wound around the outer wall of the inner layer tube. When the simulated nerve main body is a plurality of communicating paths, the sensing coils on the inner layer tube located between two adjacent path nodes and between the path node and the path end are all independently wound.

[0019] A distance is maintained between the shortest distances between the approaching ends of any two independently wound sensing coils.

[0020] The simulated nerve main body includes a tube body, and the sensing coil is uniformly distributed in the tube body in the form of a plurality of coil-shaped metal sensing probes.

[0021] The metal sensing probe is adhered to the inner wall of the tube body, or the metal sensing probe is fixedly installed on the inner wall of the tube body via a holder.

[0022] The metal sensing probe is drawn out from inside the tube body and electrically connected to an external controller.

[0023] By providing the above warning mechanism in the human body simulation path, the present invention realizes the warning mechanism of the human body simulation conduction path based on the electromagnetic induction principle of the metal detector, detects the distance between the human body simulation conduction path and the surgical instrument under non-visible conditions, obtains the corresponding surgical feedback, and greatly improves the surgical training efficiency.

[0024] The beneficial effects of the present invention are as follows. The present invention manufactures a spinal bioionic model for surgical simulation through precise design and material selection, faithfully reproduces multiple important processes in actual spinal surgery (such as X-ray imaging, simulation of the internal structure of the human body, simulation of the surgical water environment, nerve contact warning, etc.), provides a highly simulated surgical training platform for doctors, and contributes to the rapid improvement of endoscopic spinal surgery skills and clinical experience.

Brief Description of the Drawings

[0025] [Figure 1] Figure 1 is a structural schematic diagram of Examples 1 to 5 of the present invention. [Figure 2] Figure 2 is an end face schematic diagram of Examples 1 to 5 of the present invention. [Figure 3] Figure 3 is a cross-sectional view taken along the line A-A of Figure 2. [Figure 4] Figure 4 is an exploded view of the components of Examples 1 to 5 of the present invention. [Figure 5] Figure 5 is a structural schematic diagram of the bioionic spinal body of Examples 1 to 5 of the present invention. [Figure 6] Figure 6 is a structural schematic diagram of the model base of Examples 1 to 5 of the present invention. [Figure 7] Figure 7 is a structural schematic diagram of the model case of Examples 1 to 5 of the present invention. [Figure 8] Figure 8 is a structural schematic diagram of the spinal holder of Examples 1 to 5 of the present invention. [Figure 9] Figure 9 is an end face schematic diagram of the spinal holder of Examples 1 to 5 of the present invention. [Figure 10] Figure 10 is a cross-sectional view of BB in Figure 9. [Figure 11] Figure 11 is a schematic diagram of the cross-sectional structure of the simulated nerve body and induction coil in Embodiment 6 of the present invention. [Figure 12] Figure 12 is a schematic diagram of the planar structure of the simulated nerve body and induction coil in Embodiment 6 of the present invention. [Figure 13] Figure 13 is a schematic diagram of the cross-sectional structure of the simulated nerve body and probe distribution in Embodiment 7 of the present invention. [Figure 14] Figure 14 is a schematic plan view of the simulated nerve body and probe distribution in Embodiment 7 of the present invention. [Figure 15] Figure 15 is a circuit diagram of the metal detector in Embodiment 7 of the present invention. [Figure 16] Figure 16 shows the X-ray development effect of actual bone. [Figure 17] Figure 17 shows the X-ray development effect of Example 8 of the present invention. [Figure 18] Figure 18 shows the X-ray development effect of Example 14 of the present invention. [Figure 19] Figure 19 shows the X-ray development effect of Example 15 of the present invention. [Figure 20] Figure 20 shows the X-ray development effect of Comparative Example 1 of the present invention. [Figure 21] Figure 21 shows the X-ray development effect of Comparative Example 3 of the present invention. [Figure 22] Figure 22 is a photograph comparing the appearance of the emulsions of Example 1 and Comparative Example 3 of the present invention. [Figure 23] Figure 23 shows the X-ray development effect, where a is Example 1, b is real bone, and c is without developer. [Modes for carrying out the invention]

[0026] To clearly explain the technical features of this solution, it will be described below through specific embodiments.

[0027] Example 1 Referring to Figures 1 to 10, embodiments of the present invention provide an intelligent spinal bionic model comprising a model base 100 and a model case 600, a bionic spinal column 700 installed on the model base 100 and having a developing effect, and a simulated muscle layer 300 and a simulated skin layer enclosing the bionic spinal column 700. A bionic nervous system with a contact alarm mechanism is installed in the internal cavity of the bionic spinal column 700.

[0028] A trapezoidal spine holder 200 is installed on the model base 100, and a simulated muscle layer 300 with a bionic spine body 700 is placed inside the spine holder 200 and sealed and fixed by a model case 600 installed on the model base 100. See Figure 1 for the specific structure. A simulation surgery access port is provided on the upper end surface of the model case 600, and a tightening groove 621 for compressing a simulated skin layer is provided around the simulation access port. A cover can be installed on the simulation surgery access port. In addition, a tightening ring seat 120 is installed on the model base 100, and the tightening ring seat 120 has a butt-fitting groove 121 that follows the external curve of the model base 100. The model case 600 includes a support ring case 610 that fits into the butt-fitting groove 121, and a back case 620 that matches the curve of the human back is installed at the top end of the support ring case 610. The design of the clamping groove 621 and fixing groove 622 ensures that the model case 600 can be tightly fixed to the model base 100, preventing movement or deformation during the surgical simulation process.

[0029] The spinal column holder 200 includes an embedded base 210 embedded in the model base 100, fan-shaped plates 220 positioned at both ends of the upper surface of the embedded base 210, and inclined plates 230 on both sides. Of these, the embedded base 210 is provided with an internal groove 211 that engages with the bionic vertebral body 700. The embedded base 210 is the part to which the spinal column holder 200 engages with the support seat 110, and is usually located in the center of the support seat 110. Fan-shaped plates 220 are provided at both ends of the embedded base 210 to simulate the upper and lower ends of the spine. The inclined plates 230 are located on both sides of the embedded base 210 and are plate-like structures that engage with the support seat 110. The inclined plates 230 are provided with longitudinal plates 240, which are for supporting the simulated muscle layer 300 and fat layer 400, etc., outside the spine. The role of the spinal longitudinal plates 240 is to provide support that fits the bionic vertebral body 700 and to simulate the appearance of a human spine. The spinal column holder 200 is further provided with an internal groove 211 for securing the bionic vertebral body 700. The design of the internal groove 211 ensures the stability of the bionic vertebral body 700 and prevents it from loosening or falling out.

[0030] A vertical plate 240 is provided on the upper end surface of the inclined plate 230, and a skin layer receiving surface is provided on the upper end surface of the vertical plate 240. The simulated skin layer is placed on the upper end surface of the simulated muscle layer 300, and both sides hang down and are in contact with the skin layer receiving surface of the vertical plate.

[0031] Example 2 Based on Example 1, in this embodiment, the simulated muscle layer 300 is further integrally molded by casting. The simulated skin layer can include an internal fat layer 400 and an external epidermal layer 500, forming a multi-layered biotissue structure together with the simulated muscle layer, making it closer to a realistic human body and providing a more realistic surgical simulation experience. In addition, the tightening groove 621 provided in the model base 600 works in conjunction with the external epidermal layer 500, allowing each layer to adhere tightly and simulate the actual structure of the human body. Furthermore, the entire spinal holder is made of polyurethane foam integral molding, which has excellent mechanical strength, elasticity, and biocompatibility, withstanding the operating pressure during surgical simulation while providing a tactile feel close to human tissue. This material also has a good low-contrast effect when developed, further improving the development effect of the bionic cervical vertebral component. Most importantly, the integral molding process of the polyurethane material ensures the integrity and stability of the holder structure, avoiding problems such as loosening and displacement that may occur with segmented designs, and improving the accuracy of simulation training.

[0032] Of course, the bionic vertebral body can also be configured with full-size bionic lumbar skeletal lumbar components for L1, L2, L3, L4, L5, and S1, depending on the needs. Within the lumbar canal of the bionic vertebral body, the posterior longitudinal ligament, bionic nerve bundles, epidural fat, ligamentum flavum, and interspinous ligament can be provided, and the supraspinous ligament is provided above the lumbar spinous process. The bionic vertebral body 700 includes multiple vertebral components 710 to bionically simulate the human spine, with intervertebral discs 720 provided between two adjacent vertebral components 710, and the multiple vertebral components 710 and multiple intervertebral discs 720 are arranged according to the curve of the human spine. Both ends of the vertebral components 710 are bonded to the two adjacent intervertebral discs 720 using silicone gel water. The bottom curvature of the internal groove 211 fits the curve of the human spine, and the vertebral body of the vertebral component 710 is located within the internal groove 211. The vertebral portions of the bionic spinal column 700 are bonded to the internal grooves 211 within the spinal column holder 200 using silicone gel water.

[0033] Example 3 Based on Example 1 or Example 2, this embodiment further includes a cavity 111 on the model base 100 to enhance the development effect, with the implantation base 210 positioned above the cavity 111. This cavity 111 is designed to penetrate the model base 100 as much as possible, aiming to enhance the development effect of the bionic vertebral body 700 and simulate stages such as pre-operative X-ray examination. By observing the image of the model under X-ray, the operator can formulate a surgical plan based on the image data, just as in actual clinical practice, and simulate the entire surgical process. Furthermore, a support seat 110 is provided in the center of the model base 100, and the spinal column holder 200 is positioned on the support seat 110. The cavity 111 for enhancing the development effect is located within the support seat 110.

[0034] Example 4 Based on any of Examples 1 to 3, this embodiment further incorporates the spinal column holder 200 forming a space that surrounds the aquatic environment. By using it in combination with a surgical aquatic environment simulation structure, the environment of surgical perfusion fluid is simulated around the spinal column holder 200, enhancing the realism of the surgery. Specifically, the spinal column holder 200 is filled with liquid to simulate the surgical aquatic environment. The spinal column holder 200 is provided with an inlet and an overflow port, and the water source inside and outside the spinal column holder 200 is connected, forming a flowing liquid.

[0035] Furthermore, this embodiment demonstrates two types of structural designs that simulate the surgical water environment. The first structure, a surgical water environment simulation structure, includes a suspended bag of physiological saline combined with a spinal column holder 200. The spinal column holder 200 is provided with a collection tube corresponding to an overflow port, and the model base 100 is provided with a collection chamber that works in conjunction with the collection tube. The second structure is a surgical water environment simulation structure that includes a circulating water tank, in which a circulating pump is placed. The circulating water tank has a power supply unit electrically connected to the circulating pump, and an output tube is connected to the output terminal of the circulating pump, with an input tube provided inside the circulating water tank. The output tube is connected to a fluid delivery tube, and the input tube fits into an overflow port.

[0036] When the surgical water environment simulation structure is installed outside the model base 100, the model base 100 is provided with a reservoir that is connected to an overflow port, and the model base 100 is provided with an overflow hole that communicates with the reservoir. Furthermore, the model base 100 is provided with a connecting sleeve that is connected to an input tube and is connected to the overflow hole. The model base 100 or model case 600 has a connecting hole, and the model base 100 or model case 600 is provided with a first sleeve and a second sleeve on both its inner and outer surfaces, respectively. The first sleeve is fitted to the fluid delivery tube, and the second sleeve is fitted to the output tube.

[0037] When the surgical water environment simulation structure is installed on the model base 100, a stable support frame for combining with the circulating water tank is provided on the model base 100, and the output tube is in communication with the fluid delivery tube. A fitting connecting member is provided at the overflow port, which communicates with the input tube.

[0038] Specifically, the surgical water environment simulation configuration is part of model base 100 and includes a series of structures that simulate saline irrigation. These structures allow for the simulation of fluid flow during surgery, i.e., injection, circulation, and drainage. Within this configuration, a fluid inlet is provided on the embedded end plate and, in conjunction with the spinal holder 200, forms a water environment enclosure. A fluid delivery tube is connected to the fluid inlet and is used to introduce simulated saline or other fluids into the surgical simulation area. The spinal inclination plate 230 is provided with an overflow port to simulate fluid drainage during surgery. When the amount of fluid injected exceeds a certain level, the excess fluid is drained through the overflow port, simulating fluid management in actual surgery.

[0039] Simultaneously, the surgical water environment simulation structure is a system used in conjunction with the surgical water environment simulation configuration and includes components for controlling the flow and circulation of fluids. A circulation pump is installed in the circulating water tank and is responsible for pumping fluid from the tank and transporting it to the surgical area through tubing. The circulation pump also circulates fluid within the water environment enclosed by the spinal column holder 200, simulating the fluid environment during surgery, such as blood and saline solution. The circulation pump is connected to a power supply via a power supply unit, enabling electric control. An output tube is connected to the output end of the circulation pump, transporting fluid from the tank to the fluid inlet in the surgical area. An input tube is used to return fluid from the surgical area to the circulating water tank, enabling fluid circulation and utilization. This simulates continuous fluid supply and recovery during surgery, ensuring the continuous humidification and cleanliness of the surgical environment.

[0040] Furthermore, depending on the installation location of the surgical water environment simulation mechanism, the following two layout methods are provided. The first is an external installation method, in which the tubes are connected and fixed through a water tank, overflow hole, connecting sleeve, connecting hole, first sleeve, and second sleeve. The second is an internal installation method, in which all parts are integrated onto the model base 100 using a circulating water tank, stabilizing support frame, and fitting connecting member, simplifying operation.

[0041] Example 5 Based on any of Examples 1 to 4, this embodiment further includes a mounting tank 112 at the upper end of the cavity 111, the area of ​​which is larger than the area of ​​the cavity 111, and the spinal column holder 200 is placed inside the mounting tank 112. A stabilization component that works in conjunction with the spinal column holder is provided inside the mounting tank 112. This embodiment provides the following two types of structural designs for stabilization components. In the first structure, the stabilization component includes a carbon fiber board located within the mounting chamber 112, and if surgical simulation is required, the carbon fiber board is bonded to the spinal holder 200 with silicone gel water. The support seat 110 is fitted with a stabilization sleeve frame that works in conjunction with the carbon fiber board, the stabilization sleeve frame is provided with stabilization grooves that work in conjunction with the spinal holder 200, and the stabilization sleeve frame is provided with fixing screws that work in conjunction with the support seat 110. In the second structure, the stabilizing component includes a PP plate located within the mounting chamber 112, and if surgical simulation is required, the PP plate is bonded to the spinal holder 200 with silicone gel water. The support seat 110 is provided with multiple stopper screws that work in conjunction with the PP plate, and the support seat 110 is also provided with multiple positioning screws that work in conjunction with the spinal holder 200.

[0042] Specifically, to ensure the stability of the spinal column holder 200 during surgical simulation and prevent movement or deformation due to surgical manipulation, a mounting opening is provided in the aforementioned support seat 110, and stabilization components are used in conjunction with it to prevent positional displacement due to changes in force and angle during manipulation, thereby ensuring the continuity and accuracy of training. In the first structure, a carbon fiber board is bonded to the spinal holder 200 with silicone gel water to provide additional support. The stabilizing sleeve frame is provided with stabilizing grooves and fixing screws to secure the carbon fiber board and ensure close contact with the spinal holder 200. In the second structure, the PP plate is similarly bonded to the spinal column holder 200 with silicone gel solution, and the PP plate is secured with stopper screws to ensure its positional stability. In all designs, the stabilization components achieve stability through their interaction with the mounting chamber 112. The area of ​​the mounting chamber 112 is larger than that of the cavity 111, and the spinal holder 200 is positioned within the mounting chamber 112. The interaction between the stabilization components and the mounting chamber 112 ensures the stability of the spinal holder 200 during surgical simulation.

[0043] Furthermore, during the development and diagnosis stage, it is not necessary to install the stabilization sleeve frame, fixing screws, or positioning screws included in the aforementioned stabilization components. When the surgical stage begins, first open the model case 600 and attach the stabilization sleeve frame, fixing screws, or positioning screws to the support seat 110. Among these, the carbon fiber board and PP board have an excellent low-contrast effect during development, further improving the development effect of the bionic cervical spine component.

[0044] Furthermore, a clamping ring seat 120 is provided on the model base 100, which is aligned with the model case 600. The clamping ring seat 120 forms a butt-fit groove 121 along the outer curve of the model base 100. The model case 600 includes a support ring case 610 that works in conjunction with the butt-fit groove 121. A back case 620 conforming to the curve of the human back is provided at the upper end of the support ring plate, and a clamping groove 621 is provided on the back case 620. The support ring case 610 has multiple fixing grooves 622 evenly spaced along its outer curve, and the butt-fitting groove 121 has multiple locking grooves evenly spaced along the outer curve of the model base 100, with each locking groove corresponding one-to-one with a fixing groove 622, and fixing pins that engage with the locking grooves are installed inside the fixing grooves 622.

[0045] The model base 100 is equipped with transport grooves for easy handling by operators. Specifically, the model base 100 is the base part of the spinal instrument for surgical simulation, providing stable support for the entire simulated spinal structure. The model case 600 is the external part of the surgical simulation spinal instrument, providing a simulated human external environment in spinal surgery simulations. Inside the case, there is a tightening groove 621 that matches the outer epidermal layer 500, which secures the simulated skin layer, enhancing the realism of the surgical simulation, preventing damage to the simulator's internal structure, and ensuring the safety of doctors and trainees. Furthermore, the model case 600 fits tightly with the model base 100, simulating the human posterior structure in actual surgery. This high-precision simulation design allows doctors to experience an environment similar to that of actual surgery during simulated surgery, enabling them to more effectively improve their surgical skills.

[0046] Example 6 Referring to Figures 11 and 12, an embodiment of the present invention provides a human body simulation nerve equipped with a contact alarm mechanism, comprising a simulated nerve body and an alarm mechanism installed on the simulated nerve body. The alarm mechanism includes a sensing coil 6 attached to the simulated nerve body, a power supply electrically connected to the sensing coil, and an external controller that receives and processes the sensing signal and then issues an alarm.

[0047] The simulated nerve body includes an inner tube 1, a sensing coil 6 is wrapped around the outer wall of the inner tube, and the outside of the sensing coil 6 is encased in an outer covering wall 2. The inner tube 1 can be made of a rigid plastic material (rigid silicone, rigid plastic, etc.) or a flexible material such as soft silicone or rubber, and a rigid or flexible material can be selected depending on the specific position and size of the simulated nerve body. For example, when simulating the main spinal nerve, a rigid silicone material can be selected to increase stability, and when simulating a bronchial nerve or other small nerve, a soft material can be selected to increase the similarity of the simulated nerve. The material of the outer covering wall can be a flexible material such as silicone or rubber.

[0048] When the simulated nerve body is the simulated principal nerve body and an alarm mechanism is installed on the principal nerve body, the inner diameter of the inner tube 1 of the simulated principal nerve body is 10 mm, the wall thickness is 0.5-1 mm, and the thickness of the outer covering wall 2 is 1.5 mm. The sensing coil 6 is continuously wound around the outer wall of the inner tube. The sensing coil 6 can be made from copper enameled wire with a wire diameter of 0.1 mm, and the two end wires of the sensing coil 6 are led outwards along the outer wall of the inner tube 1 and electrically connected to the power supply and external controller. In surgical training, setting the alarm distance to 0.5 cm can sufficiently satisfy the feedback accuracy requirements for surgical training. To satisfy this accuracy requirement for the alarm distance, the number of turns of the coil wound around the simulated principal nerve body can be set to 1500 turns / cm, and the power supply voltage can be set to 3.5 volts.

[0049] When a simulated nerve body simulates multiple interconnected simulated principal nerve bodies and simulated bronchial nerve bodies, and when alarm mechanisms are installed on multiple nerve bodies, the inner diameter of the inner tube 1 of the simulated principal nerve body shall be 10 mm, and the wall thickness of the outer covering wall 2 shall be 1.5 mm. For the simulated bronchial nerve body, the inner diameter of the inner tube 1 shall be 5 mm, and the wall thickness of the outer covering wall 2 shall be 2 mm, and all sensing coils 6 shall be wound around the outer wall of the inner tube. The sensing coils 6 can be made from copper enameled wire with a wire diameter of 0.1 mm, and the sensing coils 6 on the inner tube between two adjacent passage nodes, and between a passage node and a passage end, shall all be wound independently. The two end wires of each independently wound sensing coil 6 shall be led out along the outer wall of the inner tube and electrically connected to the power supply and an external controller. Here, the shortest distance between the adjacent ends of any two independently wound sensing coils 6 shall all be 0.5 cm apart. The purpose of spacing the coils is to reduce interference signals between adjacent sensing coils 6. In surgical training, setting the alarm distance to 0.5 cm sufficiently satisfies the feedback accuracy requirements for surgical training. To meet this accuracy requirement for the alarm distance, the number of turns of the coil wrapped around the simulated main nerve body can be set to 1500 turns / cm, and the power supply voltage can be set to 3.5 volts. The number of turns of the coil wrapped around the simulated bronchial nerve body can be set to 2000 turns / cm. The external controller electrically connected to the sensing coil can refer to prior art, and the external controller can be a one-chip microcontroller or microcontroller.

[0050] In particular, any of the schemes in Examples 1 to 5 can be used to place the human body simulation nerves of this example within the lumen of the bionic spinal column 700, thereby forming a combination of new technological schemes.

[0051] Example 7 Referring to Figures 13, 14, and 15, an embodiment of the present invention provides a human body simulation nerve equipped with a contact alarm mechanism, comprising a simulated nerve body and an alarm mechanism installed on the simulated nerve body. The alarm mechanism includes a sensing coil attached to the simulated nerve body, a power supply electrically connected to the sensing coil, and an external controller that receives and processes the sensing signal before issuing an alarm.

[0052] The simulated nerve body includes a tube 3 with an outer diameter of 10 mm, and the sensing coils are evenly arranged inside the tube as multiple coil-type metal sensing probes 5. The material of the tube 3 can be a flexible material such as silicone or rubber, or another rigid material.

[0053] The metal sensing probe 5 is either bonded to the inner wall of the pipe 3, or fixed to the inner wall of the pipe via a holder. The metal sensing probe 5 is drawn out from inside the pipe 3 and electrically connected to an external controller. Here, the holder structure provided in Embodiment 4 can be directly adopted. Here, the metal sensing probe 5 is a component of the metal detector, which further includes a DC power supply, metal probe connection wires, surgical metal instruments, and an integrated circuit board, the integrated circuit board including a voltage comparator, an oscillator circuit, a potentiometer, and an LED warning light. The voltage comparator can be an LM393 chip, and the DC power supply Vcc can be a 5-volt battery. The oscillator circuit includes a resistor R4, a first inductance coil, a second inductance coil, a first capacitor, a second capacitor, a transistor, and a resistor R5. The first inductance coil and the first capacitor are connected in series, with one end connected to Vcc and the other end connected to the base of the transistor. One end of R4 is connected to Vcc and the other end connected to the base of the transistor. The second inductance coil and the second capacitor are connected in parallel, with one end connected to Vcc and the other end connected to the emitter of the transistor. The collector of the transistor is connected in series with resistor R5 and then grounded. One end of the potentiometer is grounded, and the other end is connected to Vcc. The third port of the potentiometer is connected to the reverse-phase input terminal of the voltage comparator. The ungrounded end of resistor R5 is connected to the common-phase input terminal of the voltage comparator, and the output terminal of the voltage comparator is connected in series with resistor R1 and then to Vcc. Resistor R2 is connected in series with the LED warning light, and one end is connected to Vcc, while the other end is connected to the output terminal of the voltage comparator.

[0054] The sensing coil is built into the metal sensing probe and is electrically connected to the integrated circuit board, leaving two pins open. If the simulated nerve body is the simulated principal nerve body, one probe is placed inside the tubular structure of each intervertebral joint on the simulated principal nerve body. When the simulated nerve body simulates multiple interconnected simulated main nerve bodies and simulated bronchial nerve bodies, one sensing probe is placed between two adjacent passage nodes, and between a passage node and its terminal, while two probes are symmetrically positioned on each simulated bronchial nerve body.

[0055] During surgical training, after the circuit is energized, when a surgical instrument approaches or comes into contact with the simulated nerve body, the coil in the oscillation circuit generates a high-frequency magnetic field. When the target object approaches the magnetic field, eddy currents are generated within the target object due to electromagnetic induction. As the target object approaches the simulated nerve body, the induced current increases, affecting the current change in the magnetic field oscillation circuit. This causes a change in the terminal voltage of resistor R5, and the voltage comparator determines the voltages at the common-mode input terminal and the out-of-mode input terminal. The output terminal of the voltage comparator outputs a low level, and the LED warning light illuminates. In particular, any of the schemes in Examples 1 to 5 can be used to place the human body simulation nerves of this example within the lumen of the bionic spinal column 700, thereby forming a combination of new technological schemes.

[0056] Example 8 This embodiment provides a bionic lumbar vertebral skeleton with X-ray development capabilities, which is manufactured by the following steps. S1 Fabrication of bionic lumbar skeletal cancellous bone core material layer: a1 Pre-mixing: Mix 100 parts polyether polyol, 1 part polydimethylsiloxane (PDMS), 30 parts 1,4-butanediol, 0.2 parts catalyst A33, 1 part triethanolamine, 10 parts trimethylolpropane, and 0.8 parts deionized water in a mixing tank until uniformly stirred. Maintain a stirring speed of 1000 rpm. After uniform mixing, this mixture is designated as material A. a2 Addition and mixing of material B: While continuing to stir material A, gradually add 170 parts of material B (polyphenylpolymethylene polyisocyanate), adjust the stirring speed to 500 rpm, and stir for 15 seconds. a3 Foam molding: The mixed liquid material is quickly injected into a mold for the lumbar spine and allowed to react in a sealed environment. The internal temperature of the mold is controlled to 25°C, and the curing time is 24 hours.

[0057] Preparation of the outer layer raw material for S2 cortical bone material: b1 Pre-emulsification of styrene-acrylic emulsion: Mix 20 parts styrene, 10 parts butyl acrylate, 20 parts methyl methacrylate, 1.0 part sodium dodecylbenzenesulfonate, 0.3 parts ammonium persulfate, and 30 parts deionized water in reactor A, and raise the temperature to 40°C with a stirring speed of 500 rpm. After the temperature stabilizes, adjust the stirring speed to 2000 rpm and stir for 20 minutes to form a pre-emulsification. b2 Polymerization of styrene acrylic emulsion: Add 20 parts deionized water, 0.5 parts initiator (ammonium persulfate), 0.5 parts emulsifier (sodium dodecylbenzenesulfonate), and 15 parts developer (KI) to reactor B, and raise the temperature to 80°C while stirring at 400 rpm. Add the preliminary emulsion from step b1 dropwise under a nitrogen atmosphere and carry out emulsion polymerization for 1 hour. After the reaction is complete, cool to room temperature to obtain the emulsion. b3 Preparation of SAN resin emulsion: Dissolve 0.5 parts potassium persulfate (KSP) in 50 parts deionized water to prepare a 1% aqueous KSP solution. Add 50 parts deionized water and 1.0 part sodium dodecylbenzenesulfonate to reactor C and heat to 65°C at 400 rpm. Under a nitrogen atmosphere, add the aqueous KSP solution and the monomer mixture (pre-mixture of 30 parts styrene and 20 parts acrylonitrile) simultaneously at the same dropping rate. After the dropping is complete in 1 hour, continue the reaction for another hour, and cool to room temperature while maintaining stirring to obtain the SAN resin emulsion. b4 SAN resin modification mixing: The emulsion obtained in step b2 is stirred at a constant temperature in reactor B, and 30 parts of the SAN resin emulsion prepared in step b3 are gradually added and mixed uniformly. After the emulsion is cooled to room temperature, 0.5 parts of pigment are added and mixed uniformly to obtain a SAN resin modified styrene acrylic emulsion with X-ray developing properties.

[0058] Fabrication of S3 bionic lumbar vertebral cortical bone: The cortical bone material prepared in step S2 is applied to the surface of the cancellous bone prepared in step S1 by spray coating or immersion process. In the spray coating method, a thin-layer coating is used, with each coat having a thickness of 0.3 mm. The next coat is applied after drying, for a total of 5 coats.

[0059] Example 9 The same manufacturing method as in Example 1 is used, but the difference is that 5 parts of SAN resin emulsion are added.

[0060] Example 10 The same manufacturing method as in Example 1 is used, but the difference is that 10 parts of styrene are added in step b1.

[0061] Example 11 The product is prepared using the same manufacturing method as in Example 1, but the difference is that polyoxyethylene aliphatic alcohol ether is selected as the emulsifier.

[0062] Example 12 The product is prepared using the same manufacturing method as in Example 1, but the difference is that polyoxyethylene alkylphenol ether is selected as the emulsifier.

[0063] Example 13 The same manufacturing method as in Example 1 is used, but the difference is that 10 parts ethyl acrylate, 10 parts butyl acrylate, and 10 parts methyl methacrylate are selected as the acrylic acid ester monomers.

[0064] Example 14 The product is prepared using the same manufacturing method as in Example 1, but the difference is that two types of developer are used in combination: 10 parts potassium iodide (KI) and 5 parts sodium iodide (NaI).

[0065] Example 15 The same manufacturing method as in Example 1 is used, but the difference is that three types of developer are used in combination: 10 parts potassium iodide (KI), 3 parts sodium iodide (NaI), and 2 parts calcium iodide (CaI2).

[0066] Example 16 This embodiment provides a bionic lumbar vertebral skeleton with X-ray development capabilities, which is manufactured by the following steps. Fabrication of S1 bionic lumbar vertebral skeleton cancellous bone: a1 Pre-mixing: 100 parts by weight of polyether polyol, 0.5 parts by weight of polydimethylsiloxane (PDMS), 10 parts by weight of 1,4-butanediol, 0.1 parts by weight of catalyst A33, 0.5 parts by weight of triethanolamine, 0.1 parts by weight of trimethylolpropane, and 0.1 parts by weight of deionized water are uniformly stirred in a mixing tank, maintaining a stirring speed of 1000 rpm. After uniform mixing, this is designated as material A. a2 Addition and mixing of material B: While continuing to stir material A, gradually add 10 parts of material B (polyphenylpolymethylene polyisocyanate), adjust the stirring speed to 300 rpm, and stir for 15 seconds. a3 Foam molding: The mixed liquid material is quickly injected into a mold for the lumbar spine and allowed to react in a sealed environment. The internal temperature of the mold is controlled to 25°C, and the curing time is 24 hours.

[0067] Preparation of S2 cortical bone material b1 Pre-emulsification of styrene-acrylic emulsion: Mix 10 parts styrene, 10 parts ethyl acrylate, 19 parts butyl acrylate, 0.5 parts emulsifier (polyoxyethylene aliphatic alcohol ether), 0.1 parts chain transfer agent (dodecyl mercaptan), and 10 parts deionized water in reactor A, and stir at a stirring speed of 1000 rpm for 10 minutes to form a pre-emulsification. b2 Polymerization of styrene acrylic emulsion: Add 10 parts deionized water, 0.5 parts initiator (ammonium persulfate), 0.5 parts emulsifier, and 1 part developer (sodium iodide, NaI) to reactor B and raise the temperature to 80°C while stirring. Add the preliminary emulsion from step b1 dropwise under a nitrogen atmosphere and carry out emulsion polymerization for 1 hour. After the reaction is complete, cool to room temperature to obtain the emulsion. b3 Preparation of SAN resin emulsion: 30 parts styrene (ST), 20 parts acrylonitrile (AN), 0.5 parts polyoxyethylene aliphatic alcohol ether, 0.5 parts potassium persulfate (KSP), and 50 parts deionized water are added to reactor C, and emulsion polymerization is carried out while stirring at a stirring speed of 1000 rpm for 10 minutes to form a styrene-acrylonitrile copolymer (SAN resin emulsion). b4 SAN resin modification mixing: The emulsion obtained in step b2 is stirred at a constant temperature in reactor B, and 5 parts of the SAN resin emulsion prepared in step b3 are gradually added and mixed uniformly. After the emulsion is cooled to room temperature, 0.1 parts of pigment are added and mixed uniformly to obtain a SAN resin modified styrene acrylic emulsion with X-ray developing properties.

[0068] Fabrication of S3 bionic lumbar vertebral cortical bone: Immersion process: Place the cortical bone material into the container and completely immerse the spongy bone material in the cortical bone material. After 30 seconds, gradually remove from the liquid surface and wait until the emulsion is completely dry. Repeat this process twice to form the developing coating.

[0069] Example 17 This embodiment provides a bionic lumbar vertebral skeleton with X-ray development capabilities, which is manufactured by the following steps. Fabrication of S1 bionic lumbar vertebral skeleton cancellous bone: a1 Pre-mixing: Mix 20 parts by weight of polyether polyol, 1.5 parts by weight of polydimethylsiloxane (PDMS), 40 parts by weight of 1,4-butanediol, 0.5 parts by weight of catalyst A33, 1.5 parts by weight of triethanolamine, 10 parts by weight of trimethylolpropane, and 3.0 parts by weight of deionized water in a mixing tank until uniformly stirred. Maintain a stirring speed of 2000 rpm and mix for 20 minutes. This mixture is then designated as material A. a2 Addition and mixing of material B: While continuing to stir material A, gradually add 170 parts of material B (polyphenylpolymethylene polyisocyanate), adjust the stirring speed to 500 rpm, and stir for 15 seconds. a3 Foam molding: The mixed liquid material is quickly injected into the mold for the lumbar spine and allowed to react in a sealed environment. The internal temperature of the mold is controlled to 55°C, and the curing time is 30 minutes.

[0070] Preparation of S2 cortical bone material b1 Pre-emulsification of styrene-acrylic emulsion: Mix 20 parts styrene, 10 parts ethyl acrylate, 20 parts butyl acrylate, 1.5 parts polyoxyethylene alkylphenol ether, 3.0 parts chain transfer agent, and 40 parts deionized water in reactor A, and stir at a stirring speed of 2000 rpm for 20 minutes to form a pre-emulsification. b2 Polymerization of styrene acrylic emulsion: Add 60 parts deionized water, 3 parts ammonium persulfate, 1.0 part polyoxyethylene alkylphenol ether, and 30 parts calcium iodide (CaI2) to reactor B and raise the temperature to 80°C while stirring. Add the preliminary emulsion from step b1 dropwise under a nitrogen atmosphere and carry out emulsion polymerization for 2 hours. After the reaction is complete, cool to room temperature to obtain the emulsion. b3 Preparation of SAN resin emulsion: 30 parts styrene (ST), 20 parts acrylonitrile (AN), 1.0 part polyoxyethylene alkylphenol ether, 0.5 parts potassium persulfate (KSP), and 100 parts deionized water are added to reactor C, and emulsion polymerization is carried out while stirring at a stirring speed of 2000 rpm for 20 minutes to form a styrene-acrylonitrile copolymer (SAN resin emulsion). b4 SAN resin modification mixing: The emulsion obtained in step b2 is stirred at a constant temperature in reactor B, and 40 parts of the SAN resin emulsion prepared in step b3 are gradually added and mixed uniformly. After the emulsion is cooled to room temperature, 0.1 parts of pigment are added and mixed uniformly to obtain a SAN resin modified styrene acrylic emulsion with X-ray developing properties.

[0071] Fabrication of S3 bionic lumbar vertebral cortical bone: Immersion process: The cancellous bone material is completely immersed in the cortical bone material. After 30 seconds, it is gradually removed from the liquid surface, and after waiting for the emulsion to dry completely, this process is repeated twice to form the developing coating.

[0072] Comparative Example 1 The product is prepared using the same manufacturing method as in Example 1, but the difference is that 5 parts of barium sulfate, a conventional developer, is used as the developer.

[0073] Comparative Example 2 The same manufacturing method as in Example 1 is used, but the difference is that the SAN resin emulsion is not added and no modification is performed. The procedure is as follows. a) Pre-emulsification: Mix 20 parts styrene, 10 parts butyl acrylate, 20 parts methyl methacrylate, 1.0 part sodium dodecylbenzenesulfonate, 0.3 parts ammonium persulfate, and 30 parts deionized water in reactor A, and raise the temperature to 40°C with a stirring speed of 500 rpm. After the temperature stabilizes, adjust the stirring speed to 2000 rpm and stir for 20 minutes to form a pre-emulsification. b) Polymerization of the emulsion: Add 20 parts deionized water, 0.5 parts initiator (ammonium persulfate), 0.5 parts emulsifier (sodium dodecylbenzenesulfonate), and 15 parts developer (KI) to reactor B and raise the temperature to 80°C while stirring at 400 rpm. Add the preliminary emulsion from step a dropwise under a nitrogen atmosphere and carry out emulsion polymerization for 1 hour. After the reaction is complete, adjust the stirring speed to 300 rpm and lower the temperature to 40°C, then add 0.5 parts white pigment (rutile-type titanium dioxide) and adjust the stirring speed to 500 rpm. After stirring for 10 minutes, a white styrene-acrylic emulsion with X-ray developability is obtained. c) Construction process: In the spray coating method, a thin-layer coating is used, with each coat having a thickness of 0.3 mm. The next coat is applied after drying, for a total of 5 coats.

[0074] Comparative Example 3 The same manufacturing method as in Example 1 is used, but the difference lies in the developer addition step. The procedure is as follows: a) Pre-emulsification: Mix 20 parts styrene, 10 parts butyl acrylate, 20 parts methyl methacrylate, 1.0 part sodium dodecylbenzenesulfonate, 0.3 parts ammonium persulfate, and 30 parts deionized water in reactor A, and raise the temperature to 40°C with a stirring speed of 500 rpm. After the temperature stabilizes, adjust the stirring speed to 2000 rpm and stir for 20 minutes to form a pre-emulsification. b) Polymerization of the emulsion: Add 20 parts deionized water, 0.5 parts initiator (ammonium persulfate), and 0.5 parts emulsifier (sodium dodecylbenzenesulfonate) to reactor B and heat to 80°C while stirring at 400 rpm. Add the preliminary emulsion from step a dropwise under a nitrogen atmosphere and carry out emulsion polymerization for 1 hour. After the reaction is complete, adjust the stirring speed to 300 rpm and cool to room temperature to obtain the emulsion. c) Preparation of SAN resin emulsion: First, 0.5 parts potassium persulfate (KSP) is dissolved in 50 parts deionized water to prepare a 1% KSP aqueous solution, which is then set aside. Next, 50 parts deionized water and 1.0 part sodium dodecylbenzenesulfonate are added to reactor C, and the temperature is raised to 65°C with a stirring speed of 400 rpm. Then, under a nitrogen atmosphere, the KSP aqueous solution and the monomer mixture (a pre-mixture of 30 parts styrene and 20 parts acrylonitrile) are added dropwise simultaneously at the same dropping rate. After the dropwise addition is completed in 1 hour, the reaction is continued for another hour, and the mixture is cooled to room temperature while maintaining stirring to obtain the SAN resin emulsion. d) SAN resin modification and mixing: The emulsion obtained in step b is heated to 40°C in reactor B under a stirring speed of 300 rpm, and 30 parts of the SAN resin emulsion prepared in step c) are gradually added to reactor B over 15 minutes. After the dropwise addition is complete, stirring and mixing are continued for another 30 minutes. Subsequently, 15 parts of developer (KI) and 0.5 parts of white pigment (rutile-type titanium dioxide) are added, the stirring speed is adjusted to 500 rpm, and stirring is performed for 10 minutes to obtain a white SAN resin modified styrene acrylic emulsion with X-ray developing properties. e) Construction process: For the spray coating method, a thin-layer coating is used, with each coat having a thickness of 0.3 mm. The next coat is applied after drying, for a total of 5 coats.

[0075] Performance testing 1. Hardness test: The coating hardness test is performed according to the GB / T 6739-2022 standard for coating hardness using the pencil method. A tin plate measuring 120mm x 50mm x 0.3mm was polished, cleaned, and dried. The prepared emulsion was then applied uniformly with a brush and dried at room temperature for 7 days. After that, the coating was tested using a pencil scratch hardness tester. Three scratch tests were performed with pencils of the same hardness, and the damage to the test plate was observed. The hardness of the hardest pencil that did not produce scratches greater than or equal to the coating's hardness was taken as the pencil hardness of the coating. 2. X-ray scan test: The development effect of bionic model lumbar vertebral bones prepared under conditions of 60kV voltage, 10mA current, and 0.2-second exposure was tested using a Cios Select mobile C-arm X-ray system manufactured by Shanghai Siemens Medical Instruments Co., Ltd. [Table 1] JPEG2026057491000002.jpg52170

[0076] Example 8 exhibited the highest hardness, demonstrating that the coating hardness was significantly improved by using SAN resin at the optimal mixing ratio. This is extremely important for constructing cortical bone in bionic human skeletal structures.

[0077] Comparing Example 9 with Example 8, it can be seen that the amount of SAN resin used directly affects the hardness. This is because both styrene and acrylonitrile monomer are "hard monomers," and by adjusting the amount of SAN resin emulsion used, it is possible to control the hardness of bionic cortical bone and adapt it to the elastic modulus of bone in different age groups.

[0078] The data from Examples 10 and 14 further examine the effect of monomer composition on hardness and support a hardness optimization strategy by changing the monomer ratio.

[0079] Compared to Comparative Example 2, Examples 8-17 all exhibited higher hardness, highlighting the innovative application of SAN resin in improving coating hardness and overall performance.

[0080] As can be seen from Figures 16-21, the development effect of Comparative Example 1 (Figure 20), which used the conventional developer BaSO4, is inferior when compared to an actual lumbar vertebral X-ray image (Figure 16). This is because BaSO4 does not dissolve in the aqueous emulsion but is dispersed in the emulsion in particulate form, and its development effect depends on the particle size. The density of BaSO4 is 4.50 g·cm³. -3 Therefore, because it is prone to settling and stratification in the emulsion, the development effect is reduced.

[0081] Ratio 3 (Figure 21) represents the case where the developer is added in reaction step d, at which point the emulsion system is already stable. Adding salts such as potassium iodide or sodium iodide makes the emulsion system prone to demulsification (see Figure 22), and in the brush application process, demulsification leads to uneven coating film formation. Furthermore, gravity makes the developer more likely to settle at the base of the substrate, resulting in uneven development.

[0082] As shown in Figure 22, the turbid emulsion sample of Comparative Example 3 exhibited a layering phenomenon, with a clear aqueous layer on top and a precipitated emulsion on the bottom. This layering is a demulsification phenomenon caused by instability in the emulsion preparation process. Demulsification refers to the phenomenon in which the dispersed phase (oil droplets encapsulated in emulsifier) ​​in an emulsion aggregates and coalesces due to insufficient stability, causing the aqueous phase to separate and the emulsion components to precipitate and layer. This indicates that the emulsion's emulsifying effect and long-term stability are insufficient.

[0083] Figure 23 compares the development effects of the bionic bone from Example 8 that was spray-coated (a), an actual vertebra (b), and a bionic bone that was not treated with development coating (c). While (c) shows almost no development effect, the development effect of (a) is ideal and shows a development effect close to that of an actual vertebra (b).

[0084] Based on the hardness data and X-ray development results, this emulsion exhibits adjustable hardness and good X-ray development properties, making it suitable for use as a bone bionic coating. Furthermore, it can also be used as an industrial X-ray flaw-detecting coating.

[0085] The foregoing are merely preferred embodiments of the present invention and do not limit it. Any modifications, equivalent substitutions, improvements, etc., made in the spirit and principles of the present invention should be included within the scope of protection of the present invention. [Explanation of Symbols]

[0086] 100 Model Base 110 Support seat 111 Cavity 112 Mounting tank 120 Tightening ring seat 121 Butt-fitting groove 200 spinal holder 210 Recessed base 211 Internal groove 220 Sector-shaped plate 230 Inclined plate 240 vertical boards 300 Simulated Muscle Layers 400 fat layer 500 outer epidermal layer 600 Model Cases 610 Support Ring Case 620 Back Case 621 Tightening groove 622 Fixed groove 700 Bionic Spine 710 Vertebral components 720 Intervertebral disc 1. Inner layer tube 2 Covered wall 3. Body 4. Simulated nerve body 5. Metal detection probe 6 Sensing coil

Claims

1. An intelligent spinal bionic model, The system includes a model base (100), a model case (600), a bionic spinal column (700) installed on the model base (100) and having a development effect, and a simulated muscle layer (300) and a simulated skin layer that enclose the bionic spinal column (700). An intelligent spinal bionic model characterized in that a bionic nerve body having a contact alarm mechanism is installed in the cavity inside the bionic spinal column (700).

2. The intelligent spinal bionic model according to claim 1, characterized in that an inverted trapezoidal spinal holder (200) is installed on the model base (100), and a simulated muscle layer (300) equipped with a bionic spinal body (700) is placed inside the spinal holder (200).

3. The spinal column holder (200) includes an embedded base (210) embedded in the model base (100), fan-shaped plates (220) installed at both ends of the embedded base (210), and inclined plates (230) installed on both sides of the embedded base (210), The intelligent spinal bionic model according to claim 2, characterized in that a skin layer receiving surface is provided on the upper end surface of the inclined plate (230), the simulated skin layer is placed on the upper end surface of the simulated muscle layer (300), and both sides thereof hang down to the skin layer receiving surface.

4. The intelligent spinal bionic model according to claim 3, characterized in that the model base (100) is provided with a cavity (111) for development enhancement, and the embedded base (210) is installed above the cavity (111).

5. The intelligent spinal bionic model according to claim 3, characterized in that the spinal holder (200) is filled with a liquid to simulate a surgical water environment, the spinal holder (200) is provided with an inlet and an overflow port, and is used to connect the inside of the spinal holder (200) with an external water source to form a fluid.

6. The bionic spinal column (700) comprises a core material layer and an outer material layer attached to the outside of the core material layer, and the bionic spinal column (700) is a hard layer having a developing effect. The method for manufacturing the bionic spinal column (700) includes the following steps: S1, Manufacturing of a core material layer, in which rigid polyurethane foam raw material is stirred and mixed, then injected into a lumbar skeletal mold and foamed to obtain a core material layer. S2, Production of outer material layer raw materials, wherein a styrene acrylic emulsion and a SAN emulsion are co-mixed to obtain an outer material layer liquid material. S3. A method for manufacturing an intelligent spinal bionic model according to any one of claims 1 to 5, characterized in that an outer material layer liquid material is attached to the outer surface of the core material layer using a spray coating or immersion process, and finally a bionic lumbar spine having a developing function is formed.

7. The specific manufacturing steps for the core material layer are as follows: In S101, 100 parts by weight of polyether polyol, 1 part by weight of polydimethylsiloxane (PDMS), 30 parts by weight of 1,4-butanediol, 0.2 parts by weight of catalyst A33, 1 part by weight of triethanolamine, 10 parts by weight of trimethylolpropane, and 0.8 parts by weight of deionized water are uniformly stirred in a mixing tank, and the stirring speed is maintained at 1000 rpm. In step S102, simultaneously with the stirring in step S101, 170 parts by weight of polyphenyl polymethylene polyisocyanate are slowly added, the stirring speed is adjusted to 500 rpm, and the mixture is stirred at high speed for 15 seconds. The method for manufacturing an intelligent spinal bionic model according to claim 6, characterized in that, in S103, after high-speed stirring, the material is quickly injected into a skeletal mold, a sealed reaction is carried out, the internal temperature of the mold is controlled to 25°C, and the solidification time is set to 24 hours to obtain a solid core material layer.

8. The specific manufacturing steps for the aforementioned outer material layer liquid material are as follows: In S201, 10-20 parts by weight of styrene, 20-30 parts by weight of acrylic acid ester monomer, 0.5-1.5 parts by weight of emulsifier, 0.1-3.0 parts by weight of chain transfer agent, and 10-40 parts by weight of deionized water are mixed in reactor A and stirred to form a preliminary emulsion. In step S202, 10-60 parts by weight of deionized water, 0.5-3 parts by weight of initiator, 0.5-1.0 part by weight of emulsifier, and 1-30 parts by weight of developer are added to reactor B, the temperature is raised to 80°C while stirring, the preliminary emulsion from step S201 is added dropwise under a nitrogen atmosphere, emulsion polymerization is carried out for 1-2 hours, and after the reaction is complete, the mixture is cooled to room temperature to obtain the emulsion. In S203, 30 parts by weight of styrene, 20 parts by weight of acrylonitrile, 1.0 part by weight of emulsifier, 0.5 parts by weight of potassium persulfate, and 100 parts by weight of deionized water are added to reactor C, and a styrene-acrylonitrile copolymer emulsion is formed by emulsion polymerization at an appropriate stirring speed. The method for producing an intelligent spinal bionic model according to claim 6, wherein in step S204, the emulsion obtained in step S202 is stirred at a constant temperature in reactor B, 5-40 parts by weight of the styrene-acrylonitrile copolymer emulsion prepared in step S203 is slowly added, after uniform stirring, the mixture is cooled to room temperature, 0.1-1.0 parts by weight of pigment is added, and after uniform stirring, an outer material layer liquid material having developing properties is obtained.

9. Step S3 is specifically as follows: A method for manufacturing an intelligent spinal bionic model according to claim 6, characterized in that the outer material layer liquid material is attached to the surface of the solid core material layer using a spray coating or immersion process.

10. The bionic neural system includes a simulated neural body and an alarm mechanism installed on the simulated neural body. The intelligent spinal bionic model according to claim 1, characterized in that the alarm mechanism includes a sensing coil (6) attached to the simulated nerve body, a power supply electrically connected to the sensing coil (6), and an external controller that receives and processes a sensing signal and then issues an alarm.

11. The intelligent spinal bionic model according to claim 10, characterized in that the simulated nerve body includes an inner layer tube (1), the sensing coil (6) is wrapped around the outer wall of the inner layer tube (1), and the outside of the sensing coil (6) is covered by an outer layer covering wall (2).

12. If the simulated nerve body has a single pathway, the sensing coil is continuously wrapped around the outer wall of the inner tube (1). The intelligent spinal bionic model according to claim 11, characterized in that, when the simulated nerve body is a plurality of interconnected pathways, the sensing coils (6) on the inner layer tube (1) located between two adjacent pathway nodes and between a pathway node and a pathway terminal are all independently wound.

13. The intelligent spinal bionic model according to claim 12, characterized in that a gap is maintained between the shortest distance between the approaching ends of any two independently wound sensing coils (6).

14. The simulated nerve body includes a tube (3), and the sensing coils are uniformly distributed within the tube (3) in the form of multiple coil-type metal sensing probes (5). The intelligent spinal bionic model according to claim 11, characterized in that the metal sensing probe (5) is adhered to the inner wall of the tube, or the metal sensing probe (5) is fixedly installed on the inner wall of the tube (3) via a holder.

15. The intelligent spinal bionic model according to claim 14, characterized in that the metal sensing probe (5) is drawn out from inside the tube (3) and electrically connected to an external controller.

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