An intelligent bionic spine model

Abstract

The present invention discloses an intelligent bionic spine model, which relates to the technical field of surgical simulation instruments, and comprises: a model base and a model shell, as well as a bionic spine body with a development effect arranged on the model base and a simulated muscle layer and a simulated skin layer wrapped around the outside of the bionic spine body; a bionic nerve body with a touch warning mechanism is arranged in the internal cavity of the bionic spine body. The beneficial effects of the present invention are: the present invention manufactures a bionic spine model for surgical simulation through fine design and material selection, and successfully simulates multiple key links in real spinal surgery, including X-ray development, simulation of the internal structure of the human body, simulation of the surgical water environment, nerve touch warning, etc., providing doctors with a highly simulated surgical training platform, which helps to quickly improve spinal endoscopic surgery skills and clinical experience.

Description

Technical Field

[0001] The invention relates to the technical field of surgical simulation instruments, and in particular to an intelligent bionic spine model. Background Art

[0002] Traditional spinal or partial spinal (such as spinal) surgical training methods mostly rely on anatomical specimen observation and image data learning. Although these methods provide basic knowledge for understanding spinal structure, they have obvious limitations in simulating actual surgical procedures, coping with complex clinical situations, and improving surgical decision-making capabilities. Therefore, seeking training methods that are closer to actual combat has become an urgent need to improve the level of spinal endoscopic surgery. In response to this demand, some simulated spine models have appeared on the market for surgical skills training.

[0003] However, the existing simulation spinal surgery models still have significant deficiencies in simulating real surgical scenes and the human body's internal environment. For example, the design of most current models is directly based on the static anatomical spine, ignoring the crucial X-ray development link before surgery; and the existing models fail to fully simulate the internal environment of the human body in terms of material selection and structural design, especially the dynamic performance of physiological elements such as blood and body fluids. The spine is densely distributed with blood vessels, nerves and various soft tissues. During surgery, delicate operations are often required in an exudate environment. At the same time, flushing with saline to clearly expose the surgical field of view is also one of the routine operations. In addition, most simulation spinal models on the market use a frame structure, which makes it difficult to truly reproduce the surgical texture of human tissue, fluid dynamics, and possible bleeding during surgery. This simplified treatment of the complexity of the internal environment makes it difficult for doctors to get an immersive feeling during simulation training, and it is difficult to fully exercise their ability to accurately operate and respond to emergencies under complex physiological conditions.

[0004] How to solve the above technical problems is the subject faced by the present invention. Summary of the invention

[0005] In order to address the deficiencies of the prior art, the present invention provides a rationally designed, safe and reliable intelligent bionic spine model, which provides doctors with an all-round, three-dimensional surgical skill training tool, helps to improve surgical skills and reduce actual surgical risks.

[0006] In order to achieve the above-mentioned invention object, the present invention provides an intelligent spine bionic model, comprising: a model base and a model shell, a bionic spine body with a developing effect arranged on the model base, and a simulated muscle layer and a simulated skin layer wrapped outside the bionic spine body;

[0007] The internal cavity of the bionic spine body is provided with a bionic nerve body with a touch warning mechanism.

[0008] Wherein, an inverted trapezoidal spine bracket is arranged on the model base, and a bionic muscle body with a bionic spine body inside is placed in the spine bracket.

[0009] The spinal bracket includes an embedded base embedded in the model base, a fan-shaped plate arranged at both ends of the embedded base and an inclined plate arranged on both sides of the embedded base; a vertical plate is arranged at the upper end of the inclined plate; wherein, the upper end surface of the embedded base is provided with an embedded groove matching the lower end surface of the bionic spinal body for fixing the bionic spinal body; the spinal bracket is formed in one piece by foaming polyester-ammonia material, and the upper end surface of the fan-shaped plate is set to fit the curve of the human back; the bionic spinal body can be realized by 3D printing and other methods, and its shape and structure can be set to L1, L2, L3, L4, L5, S1 full-size bionic lumbar skeletal lumbar parts according to actual needs; the bionic spinal body lumbar vertebral canal can also be provided with posterior longitudinal ligament, bionic nerve bundle, epidural fat, yellow ligament, interspinous ligament, etc., and the lumbar spinous process can also be provided with supraspinous ligament.

[0010] The upper surface of the vertical plate at the upper end of the inclined plate is provided with a skin layer receiving surface, and the simulated skin layer is provided on the upper end surface of the bionic muscle body and its two sides hang down to the skin layer receiving surface. The simulated skin layer is two layers, including a bionic fat inner layer and a bionic epidermis layer. The bionic muscle body is cast in one piece;

[0011] The model base is provided with a cavity for enhancing development, and the embedding base is arranged above the cavity.

[0012] The spinal bracket is provided with liquid for simulating the surgical water environment; the spinal bracket is provided with a liquid inlet and an overflow port for connecting the inside of the spinal bracket with an external water source to form a flowing liquid.

[0013] In order to better achieve the above-mentioned purpose of the invention, the present invention also provides a bionic spine body, the bionic spine 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, the bionic spine body is a hard layer with a developing effect;

[0014] The method for preparing the bionic vertebral body comprises the following steps:

[0015] S1. Preparation of the core material layer: Stirring and mixing the rigid polyurethane foam raw materials, pouring them into a lumbar vertebrae skeleton mold and foaming them to obtain a core material layer;

[0016] S2, preparation of raw materials for the outer material layer: blending styrene acrylic emulsion and styrene-acrylonitrile copolymer emulsion to obtain liquid material for the outer material layer;

[0017] S3. Preparation of bionic lumbar vertebrae: using a spraying or dipping process, the liquid material of the outer material layer is attached to the outer surface of the core material layer, and finally a bionic lumbar vertebrae with development is formed.

[0018] The specific preparation steps of the core material layer are as follows:

[0019] 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 stirred evenly in a mixing barrel, and the stirring speed is maintained at 1000 rpm;

[0020] S102, while stirring in step S101, slowly add 170 parts by weight of polyphenyl polymethylene polyisocyanate, adjust the stirring speed to 500 rpm, and stir rapidly for 15 seconds;

[0021] S103, after rapid stirring, quickly pour into the bone mold and seal the reaction, the temperature inside the mold is controlled at 25°C, the curing time is 24 hours, and a solid core material layer is obtained.

[0022] The specific preparation steps of the outer material layer liquid material are as follows:

[0023] S201, in a reactor A, 10-20 parts by weight of styrene, 20-30 parts by weight of an acrylic ester monomer, 0.5-1.5 parts by weight of an emulsifier, 0.1-3.0 parts by weight of a chain transfer agent and 10-40 parts by weight of deionized water are mixed and stirred to form a pre-emulsion;

[0024] S202, adding 10-60 parts by weight of deionized water, 0.5-3 parts by weight of initiator, 0.5-1.0 parts by weight of emulsifier and 1-30 parts by weight of developer into reactor B, stirring and heating to 80° C., and dropwise adding the pre-emulsion of step S201 under nitrogen protection, and performing emulsion polymerization for 1-2 hours. After the reaction is completed, cooling to room temperature to obtain an emulsion;

[0025] S203, adding 30 parts by weight of styrene, 20 parts by weight of acrylonitrile, 1.0 parts by weight of emulsifier, 0.5 parts by weight of potassium persulfate, and 100 parts by weight of deionized water into the reactor C, and forming a styrene-acrylonitrile copolymer emulsion by an emulsion polymerization method at a suitable stirring speed;

[0026] S204, stirring the emulsion obtained in step S202 at a constant temperature in reactor B, and slowly adding 5-40 parts by weight of the styrene-acrylonitrile copolymer emulsion prepared in step S203, stirring evenly, cooling to room temperature, adding 0.1-1.0 parts by weight of pigment, stirring evenly to obtain an outer material layer liquid material with a developing function.

[0027] The step S3 specifically includes: using a spraying or dipping process to attach the liquid material of the outer material layer to the surface of the solid core material layer.

[0028] The bionic spine with X-ray imaging function provided by the present invention has very good practical effects:

[0029] (1) Significant improvement in the development effect: By adding the water-soluble developer KI during the emulsion synthesis process, the developer and the emulsion are evenly mixed. This mixing method allows the developer to be distributed in the emulsion in a finer form. Compared with the traditional coarse-grained developer, this fine liquid distribution form significantly enhances the contrast and clarity of the X-ray development. Therefore, more effective contrast can be formed during the imaging process, significantly improving the doctor's ability to identify bone structure and lesion details, which is crucial for accurate diagnosis and treatment planning.

[0030] (2) Enhanced environmental protection and biocompatibility: Compared with traditional developing materials that rely on high-concentration inorganic developing agents (such as barium, iodine, etc.), the water-soluble developing agent KI used in the present invention has obvious advantages in terms of safety and biocompatibility. Low-toxic water-soluble developing agents pose less risk to the environment and patient health, and meet the strict requirements of modern medical materials for environmental protection and human safety.

[0031] (3) Improvement of mechanical properties of coating: The addition of SAN resin in the present invention not only improves the developing performance of the emulsion, but also enhances the mechanical properties of the material by increasing hardness and wear resistance. This makes the modified styrene acrylic emulsion of the present invention particularly suitable for simulating bone materials of people of different ages and different diseases, such as bones of children, adults, the elderly, and osteoporosis patients.

[0032] (4) Extensive and flexible application: In addition to the application of medical bionic bones, the colorless and transparent characteristics of SAN resin-modified styrene acrylic emulsion and its adjustable color make it also have wide application potential in fields such as industrial non-destructive testing. Different color options can be adjusted according to specific application requirements, providing more customized solutions.

[0033] In order to better achieve the purpose of the invention, the present invention also provides a simulated neural body with a touch warning mechanism; the bionic neural body includes a simulated neural body and a warning mechanism arranged on the simulated neural body;

[0034] The warning mechanism includes: an induction coil attached to the simulated nerve body, and

[0035] A power supply electrically connected to the induction coil and an external controller for receiving the induction signal and processing it to issue an early warning.

[0036] The simulated nerve body comprises an inner tube, the induction coil is wound on the outer wall of the inner tube, and the outside of the induction coil is coated with an outer coating wall.

[0037] When the simulated nerve body is a single branch pathway (or only the main nerve is simulated), the induction coil is continuously wound around the outer wall of the inner tube;

[0038] When the simulated nerve body is a multi-branch interconnected pathway, the induction coils on the inner tube between two adjacent pathway nodes and between a pathway node and a pathway end are all independently wound.

[0039] The shortest distance between adjacent ends of any two independently wound induction coils remains spaced apart.

[0040] The simulated nerve body comprises a tube body, and the induction coil is evenly distributed in the tube body in the form of a plurality of coil-type metal induction probes.

[0041] The metal sensing probe is bonded to the inner wall of the tube body, or the metal sensing probe is fixed to the inner wall of the tube body through a bracket.

[0042] The metal sensing probe is led out from the inside of the tube body and is electrically connected to an external controller.

[0043] The present invention arranges the above-mentioned early warning mechanism on the human body simulation pathway, realizes the early warning mechanism of the human body simulation conduction pathway based on the electromagnetic induction principle of the metal detection device, can detect the distance between the human body simulation conduction pathway and the surgical instrument under non-visual conditions, obtain corresponding surgical feedback, and greatly improve the efficiency of surgical training.

[0044] The beneficial effects of the present invention are: the present invention has produced a bionic spine model for surgical simulation through careful design and material selection, successfully simulating multiple key links in real spinal surgery, including X-ray development, simulation of the internal structure of the human body, simulation of the surgical water environment, nerve touch warning, etc., providing doctors with a highly simulated surgical training platform, which helps to quickly improve spinal endoscopic surgical skills and clinical experience. BRIEF DESCRIPTION OF THE DRAWINGS

[0045] Figure 1 Schematic diagram of the structure of embodiments 1 to 5 of the present invention.

[0046] Figure 2 Schematic diagrams of end faces of embodiments 1 to 5 of the present invention.

[0047] Figure 3 for Figure 2 Medium AA section view.

[0048] Figure 4 Exploded views of components of embodiments 1 to 5 of the present invention.

[0049] Figure 5 Schematic diagram of the structure of the bionic spine of Examples 1 to 5 of the present invention.

[0050] Figure 6 Schematic diagram of the structure of the model base of embodiments 1 to 5 of the present invention.

[0051] Figure 7 Schematic diagram of the structure of the model shell of embodiments 1 to 5 of the present invention.

[0052] Figure 8 Schematic diagram of the structure of the spinal column bracket of embodiments 1 to 5 of the present invention.

[0053] Fig. 9 Schematic diagrams of end views of spinal column supports according to embodiments 1 to 5 of the present invention.

[0054] Fig.10 for Fig. 9 BB section view in .

[0055] Fig.11 This is a schematic diagram of the cross-sectional structure of the simulated neural body and the induction coil according to Example 6 of the present invention.

[0056] Fig.12 Schematic diagram of the planar structure of the simulated neural body and the induction coil in Example 6 of the present invention

[0057] Fig.13 This is a schematic diagram of the cross-sectional structure of the simulated nerve body and probe distribution according to Example 7 of the present invention.

[0058] Fig.14 A schematic diagram of the simulated neural body and the distribution of probes in Example 7 of the present invention

[0059] Fig.15 This is a circuit diagram of the metal detector in Example 7 of the present invention.

[0060] Fig.16 This is the real bone X-ray development effect.

[0061] Fig.17 This is the X-ray development effect of Example 8 of the present invention.

[0062] Fig.18 This is the X-ray development effect of Example 14 of the present invention.

[0063] Fig.19 This is the X-ray development effect of Example 15 of the present invention.

[0064] Fig. 20 This is the X-ray development effect of comparative example 1 of the present invention.

[0065] Fig.21This is the X-ray development effect of comparative example 3 of the present invention.

[0066] Fig. 22 The following are photos comparing the appearance of the emulsions of Example 1 and Comparative Example 3 of the present invention.

[0067] Fig.23 : These are X-ray development effect diagrams, where a is Example 1, b is real bone, and c is no developer used.

[0068] Wherein, the accompanying drawings are marked as follows:

[0069] 100, model base; 110, lifting seat; 111, cavity; 112, placement groove; 120, fastening ring seat; 121, docking groove; 200, spine bracket; 210, embedded base; 211, embedded groove; 220, fan-shaped plate; 230, inclined plate; 240, vertical plate; 300, simulated muscle layer; 400, fat layer; 500, epidermis; 600, model shell; 610, support ring shell; 620, back shell; 621, clamping groove; 622, firm groove; 700, bionic spine body; 710, vertebral component; 720, intervertebral disc;

[0070] 1. Inner tube; 2. Coating wall; 3. Tube body; 4. Simulated nerve body; 5. Metal induction probe; 6. Induction coil. DETAILED DESCRIPTION

[0071] In order to clearly illustrate the technical features of this solution, this solution is described below through a specific implementation method.

[0072] Example 1

[0073] See also Figure 1-Figure 10 The embodiment of the present invention provides an intelligent spine bionic model, comprising: a model base 100 and a model shell 600, a bionic spine body 700 with a developing effect arranged on the model base 100, and a simulated muscle layer 300 and a simulated skin layer wrapped outside the bionic spine body 700;

[0074] The internal cavity of the bionic spine body 700 is provided with a bionic nerve body with a touch warning mechanism.

[0075] The model base 100 is provided with an inverted trapezoidal spine bracket 200, and the simulated muscle layer 300 with a bionic spine body 700 is placed inside the spine bracket 200 and is packaged and solidified by a model shell 600 provided on the model base 100. For the specific structure, see Figure 1The upper end surface of the model shell 600 is provided with a simulated surgical operation port, and a clamping groove 621 for compressing the simulated skin layer is provided around the simulated operation port, and a cover can be provided on the simulated surgical operation port. In addition, a fastening ring seat 120 is provided on the model base 100, and the fastening ring seat 120 is provided with a docking groove 121 along the outer curve of the model base 100; the model shell 600 includes a supporting ring shell 610 matched with the docking groove 121, and a back shell 620 that fits the back curve of the human body is provided at the top of the supporting ring shell 610; through the design of the clamping groove 621 and the fixing groove 622, the model shell 600 can be tightly fixed on the model base 100 to ensure that it will not move or deform during the surgical simulation process.

[0076] The spine bracket 200 includes an embedded base 210 embedded on the model base 100, a fan-shaped plate 220 arranged at both ends of the upper end surface of the embedded base 210, and an inclined plate 230 on both sides; wherein, the embedded base 210 is provided with an embedded groove 211 that matches with the bionic spine body 700. The embedded base 210 is the part of the spine bracket 200 that matches with the support seat 110, and is usually located at the center of the support seat 110; the fan-shaped plates 220 are arranged 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 they are plate-like structures that match with the support seat 110; the inclined plates 230 are provided with vertical plates 240 to support the simulated muscle layer 300 and fat layer 400 outside the simulated spine. The function of the spine vertical plates 240 is to provide support that matches with the bionic spine body 700 and simulate the appearance of the human spine. The spine bracket 200 is also provided with an embedded groove 211 for fixing the bionic spine body 700. The design of the embedded groove 211 can ensure the stability of the bionic spine body 700 so that it will not loosen or fall off.

[0077] The upper end surface of the inclined plate 230 is provided with a vertical plate 240, and the upper end surface of the vertical plate 240 is provided with a skin layer receiving surface. The simulated skin layer is arranged on the upper end surface of the simulated muscle layer 300 and its two sides hang down to the skin layer receiving surface of the vertical plate.

[0078] Example 2

[0079] On the basis of Example 1, in this embodiment, the simulated muscle layer 300 is further cast in one piece; the simulated skin layer may include an internal fat layer 400 and an outer skin layer 500, which together with the simulated muscle layer form a multi-layer biological tissue structure to be closer to the real human body and provide a more realistic surgical simulation experience. In addition, the clamping groove 621 provided on the model shell 600 cooperates with the outer skin layer 500 to ensure that each layer fits tightly and simulates the real human body structure. In addition, the spinal bracket is integrally formed by foaming polyurethane material as a whole. This material has good mechanical strength, elasticity and biocompatibility, can withstand the operating pressure during the surgical simulation, and provides a touch similar to human tissue. At the same time, the material has a good low-contrast effect when developing, thereby further improving the development effect of the bionic cervical vertebrae. More importantly, the one-piece molding process of the polyester-ammonia material ensures the integrity and stability of the bracket structure, avoids the problems of looseness and dislocation that may be caused by the split design, thereby improving the accuracy of the simulation training.

[0080] Of course, the bionic spine body can also be equipped with L1, L2, L3, L4, L5, S1 full-size bionic lumbar vertebrae and lumbar vertebrae according to the needs; the bionic spine body can also be equipped with posterior longitudinal ligament, bionic nerve bundle, epidural fat, yellow ligament, interspinous ligament, and supraspinous ligament on the lumbar spinous process. The bionic spine body 700 can include a plurality of vertebrae 710 for bionic simulation of the human spine, and an intervertebral disc 720 is arranged between two adjacent vertebrae 710, and the plurality of vertebrae 710 and the plurality of intervertebral discs 720 are arranged according to the curve of the human spine, and the two ends of the vertebrae 710 are bonded with two adjacent intervertebral discs 720 of the vertebrae 710 using silicone gel water; the bottom curvature of the embedded groove 211 fits the curve of the human spine, and the vertebral body of the vertebrae 710 is located in the embedded groove 211. The vertebrae of the bionic spine body 700 are bonded to the embedded grooves 211 in the spine bracket 200 through silicone gel water.

[0081] Example 3

[0082] On the basis of Example 1 or Example 2, this embodiment further provides a cavity 111 for enhancing development on the model base 100, and the embedded base 210 is arranged above the cavity 111. The cavity 111 runs through the model base 100 as much as possible, aiming to enhance the development effect of the bionic spine body 700 and simulate the X-ray examination before surgery and other links. The operator can formulate a surgical plan based on the image data by observing the image of the model under X-ray, just like in actual clinical practice, thereby simulating the entire surgical process. In addition, a lifting seat 110 is provided at the center of the model base 100, and the spinal bracket 200 is arranged on the lifting seat 110; the cavity 111 for enhancing development is arranged in the lifting seat 110.

[0083] Example 4

[0084] On the basis of any one of Embodiments 1 to 3, this embodiment further forms a water environment surrounding space on the spinal bracket 200, and when used in conjunction with the surgical water environment simulation structure, the surgical flushing fluid environment can be simulated around the spinal bracket 200 to enhance the surgical simulation experience. Specifically, a liquid for simulating the surgical water environment is provided inside the spinal bracket 200; and a liquid inlet and an overflow port are provided on the spinal bracket 200, which are used to connect the inside of the spinal bracket 200 with an external water source to form a flowing liquid.

[0085] In addition, this embodiment provides two specific structural designs of simulated surgical water environments, as follows:

[0086] First, the surgical water environment simulation structure includes a saline hanging bag matched with the spinal bracket 200, a collecting hose matched with the overflow port is provided on the spinal bracket 200, and a collecting chamber matched with the collecting hose is provided on the model base 100.

[0087] Secondly, the surgical water environment simulation structure includes a circulating water tank, a circulating water pump is provided in the circulating water tank, a power supply electrically connected to the circulating water pump is provided on the circulating water tank, an output hose is provided at the output end of the circulating water pump, an input hose is provided in the circulating water tank, the output hose is connected to the inlet hose, and the input hose cooperates with the overflow port.

[0088] When the surgical water environment simulation structure is arranged on the outside of the model base 100, a water storage tank matched with the overflow port is provided on the model base 100, an overflow hole connected with the water storage tank is provided on the model base 100, and a connecting plug-in sleeve matched with the overflow hole and connected with the input hose is provided on the model base 100; a connecting hole is provided on the model base 100 or the model shell 600, and a first plug-in sleeve and a second plug-in sleeve are respectively provided on the inner and outer sides of the model base 100 or the model shell 600, and the first plug-in sleeve is plug-fitted with the input hose, and the second plug-in sleeve is plug-fitted with the output hose.

[0089] When the surgical water environment simulation structure is arranged on the model base 100, a circulating water tank and a stabilizing frame are arranged on the model base 100, the output hose is connected with the inlet hose, and a plug-in connector connected with the input hose is arranged on the overflow port.

[0090] Specifically, the surgical water environment simulation component is a part of the model base 100, which includes a series of structures for simulating saline flushing. These structures allow the flow of liquid during the simulated operation, including the infusion, circulation and discharge of the liquid. Among them, the drum inlet is opened on the embedded end plate, and cooperates with the spinal bracket 200 to form a water environment surrounding space. The drum hose is connected to the drum inlet, which is used to introduce simulated saline or other liquids into the simulated surgical area. The spinal inclined plate 230 is provided with an overflow port for simulating the discharge of liquid during the operation. When the liquid infusion volume exceeds a certain limit, the overflow port can ensure that the excess liquid is discharged, simulating the liquid management in real surgery.

[0091] At the same time, the surgical water environment simulation structure is a system used in conjunction with the surgical water environment simulation component, which includes components for controlling the flow and circulation of liquid. Among them, the circulating water pump is installed in the circulating water tank, which is responsible for extracting the liquid from the water tank and transporting it to the operating area through a hose, and the circulating water pump drives the water body to circulate in the water environment surrounded by the spinal bracket 200 to simulate the liquid environment such as blood, saline, etc. during the operation. The circulating water pump is connected to the power supply through the power supply unit to achieve electric control. The output hose is connected to the output end of the circulating water pump, which is used to transport the liquid from the water tank to the drum inlet of the operating area. The input hose is used to return the liquid from the operating area to the circulating water tank to achieve the recycling of the liquid. In this way, the continuous supply and recovery of liquid during surgery can be simulated to ensure the continuous moistening and cleanliness of the operating environment.

[0092] In addition, according to the different installation positions of the surgical water environment simulation mechanism, the device provides two layout methods: first, the external mode, through the water storage tank, overflow hole, connecting plug, connecting hole, first plug and second plug to achieve the connection and fixation of the hose; second, the built-in mode, using the circulating water tank with a stabilizing frame and plug-in connecting parts to integrate all components on the model base 100 to simplify the operation.

[0093] Example 5

[0094] On the basis of any one of Embodiments 1 to 4, a placement groove 112 is provided at the upper end of the cavity 111, and the area of ​​the placement groove 112 is larger than the area of ​​the cavity 111, and the spinal bracket 200 is placed in the placement groove 112, and a stabilizing component cooperating with the spinal bracket is provided in the placement groove 112; this embodiment provides two structural designs of stabilizing components, which are as follows:

[0095] In the first structure, the stabilizing component includes a carbon fiber plate arranged in the placement groove 112. When surgical simulation is required, the carbon fiber plate is bonded to the spinal bracket 200 by silicone gel water. A stabilizing sleeve that cooperates with the carbon fiber plate is mounted on the support seat 110. The stabilizing sleeve is provided with a stabilizing groove that cooperates with the spinal bracket 200. The stabilizing sleeve is provided with fastening screws that cooperate with the support seat 110.

[0096] In the second structure, the stabilization component includes a PP plate arranged in the placement groove 112. When surgical simulation is required, the PP plate cover is bonded to the spinal bracket 200 by silicone gel water. The lifting seat 110 is provided with a plurality of limit screws cooperating with the PP plate, and the lifting seat 110 is provided with a plurality of positioning screws cooperating with the spinal bracket 200.

[0097] Specifically, in order to ensure the stability of the spinal bracket 200 during the simulated surgery and prevent movement or deformation caused by surgical operations, a placement port is provided on the basis of the above-mentioned support seat 110, and a stabilizing component is provided for use, thereby avoiding displacement caused by operating force or angle changes, and ensuring the continuity and accuracy of training. Among them, in the first structure, the carbon fiber plate is bonded to the spinal bracket 200 by silicone gel water to provide additional support. The stabilizing sleeve is provided with a stabilizing groove and a fastening screw for fixing the carbon fiber plate to ensure its close combination with the spinal bracket 200; and in the second structure, the PP plate is also bonded to the spinal bracket 200 by silicone gel water, and the limit screw is used to fix the PP plate to ensure the stability of its position. However, whether it is the first or second design, the stabilizing component achieves stability by cooperating with the placement groove 112. The area of ​​the placement slot 112 is larger than the area of ​​the cavity 111 , and the spinal bracket 200 is placed in the placement slot 112 . The stability of the spinal bracket 200 in the simulated surgery is ensured by the cooperation between the stabilizing component and the placement slot 112 .

[0098] In the imaging diagnosis stage, the stabilizing sleeve, fastening screws or positioning screws in the above-mentioned stabilizing assembly may not be installed, and when in the surgical stage, the model housing 600 is first opened, and the stabilizing sleeve, fastening screws or positioning screws are installed on the lifting seat 110. The carbon fiber plate and PP plate have a good low-contrast effect during imaging, thereby further improving the imaging effect of the bionic cervical vertebrae.

[0099] Furthermore, a fastening ring seat 120 is provided on the model base 100 to match the model shell 600, and a docking groove 121 is provided on the fastening ring seat 120 along the outer curve of the model base 100. The model shell 600 includes a supporting ring shell 610 matched with the docking groove 121, and a back shell 620 that fits the back curve of the human body is provided at the top of the supporting ring plate, and a clamping groove 621 is provided on the back shell 620;

[0100] The support ring shell 610 is evenly provided with a plurality of fixing grooves 622 along the outer curve of the support ring shell 610, and the docking groove 121 is evenly provided with a plurality of locking grooves along the outer curve of the model base 100, and the tightening grooves match the fixing grooves 622 one by one, and the fixing grooves 622 are provided with fixing nails matching the locking grooves.

[0101] The model base 100 is provided with a carrying groove for easy carrying by personnel. Specifically, the model base 100 is the basic part of the surgical simulation spinal tool, and its function is to provide stable support for the entire simulated spinal structure. The model shell 600 is the appearance part of the surgical simulation spinal tool, which provides a simulated human external environment for simulated spinal surgery. The shell is provided with a clamping groove 621 that cooperates with the outer skin layer 500, which is used to fix the simulated skin layer, increase the realism of the surgical simulation, and protect the internal structure of the simulator from damage, while ensuring the safety of doctors and trainers. The model shell 600 simulates the human back structure in real surgery by closely cooperating with the model base 100. This highly simulated design enables doctors to experience an environment similar to real surgery in simulated surgery, thereby more effectively improving surgical skills.

[0102] Example 6

[0103] See also Fig.11 and Fig.12 , an embodiment of the present invention provides a human simulated nerve with a touch warning mechanism, including a simulated nerve body and a warning mechanism arranged on the simulated nerve body;

[0104] The early warning mechanism includes: an induction coil 6 attached to the simulated nerve body, a power supply electrically connected to the induction coil, and an external controller for receiving the induction signal and processing it to issue an early warning.

[0105] The simulated nerve body includes an inner tube 1, an induction coil 6 is wound on the outer wall of the inner tube, and the outside of the induction coil 6 is covered with an outer coating wall 2. The inner tube 1 can be made of hard plastic material such as hard silicone, hard plastic, or soft silicone, rubber and other flexible materials. The hard or flexible material can be selected according to the position and size of the specific simulated nerve body. For example, when simulating the main nerve of the spine, a harder silicone material can be selected to enhance stability. For branch nerves and or other smaller nerves, some softer materials can be selected to enhance the similarity of the simulated nerves. The material of the outer coating wall can be flexible materials such as silicone, rubber, etc.

[0106] When the simulated nerve body is a simulated main nerve body, and an early warning mechanism is set on the main nerve body, the inner diameter of the inner tube 1 of the simulated main nerve body is 10mm, the wall thickness is 0.5-1mm, the thickness of the outer coating wall 2 is 1.5mm, and the induction coil 6 is continuously wound on the outer wall of the inner tube. The induction coil 6 can be made of copper enameled wire with a wire diameter of 0.1mm. The two end wires of the induction coil 6 are led to the outside along the outer wall of the inner tube 1 and are electrically connected to the power supply and the external controller. In surgical teaching and training, setting the early warning distance to 0.5cm is sufficient to meet the feedback accuracy requirements of surgical training. Under the condition of meeting the accuracy requirements of this early warning distance, the number of turns of the coil wound on the simulated main nerve body can be set to 1500 turns / cm, and its power supply voltage can be set to 3.5 volts.

[0107] When the simulated nerve body is a simulated main nerve body and a simulated branch nerve body that simulate multiple branches, and an early warning mechanism is set on the multiple branch nerve bodies, for the simulated main nerve body, the inner diameter size of the inner tube 1 of the simulated main nerve body is 10mm, and the wall thickness of the outer coating wall 2 is 1.5mm; for the simulated branch nerve body, the inner diameter size of the inner tube 1 of the simulated branch nerve body is 5mm, and the wall thickness of the outer coating wall 2 is 2mm. The induction coil 6 is wound on the outer wall of the inner tube. The induction coil 6 can be made of copper enameled wire with a wire diameter of 0.1mm. The induction coils 6 on the inner tube between two adjacent passage nodes and between the passage node and the passage end are independently wound. The two end wires of any independently wound induction coil 6 are led to the outside along the outer wall of the inner tube and are electrically connected to the power supply and the external controller. Among them, the closest distance between the ends of any two independently wound induction coils 6 is 0.5cm. The purpose of leaving the interval is to reduce the interference signal between adjacent induction coils 6. In surgical teaching and training, setting the warning distance to 0.5 cm is sufficient to meet the feedback accuracy requirements of surgical training. While meeting the accuracy requirements of this warning distance, the number of turns of the coil wrapped around the simulated main nerve body can be set to 1500 turns / cm, and its power supply voltage can be set to 3.5 volts. The number of turns of the coil wrapped around the simulated branch nerve body can be set to 2000 turns / cm. The external controller electrically connected to the induction coil can refer to the existing technology, and the external controller is a single-chip microcomputer or a microcontroller.

[0108] In particular, any one of the solutions in Examples 1 to 5 can be provided with the human body simulation nerve of this embodiment in the inner cavity of the bionic spine body 700 to form a new technical solution combination.

[0109] Example 7

[0110] See also Fig.13 , Fig.14 and Fig.15, an embodiment of the present invention provides a human simulated nerve with a touch warning mechanism, including a simulated nerve body and a warning mechanism arranged on the simulated nerve body;

[0111] The early warning mechanism includes: an induction coil attached to the simulated nerve body, a power supply electrically connected to the induction coil, and an external controller for receiving the induction signal and processing it to issue an early warning.

[0112] The simulated nerve body comprises a tube body 3 with an outer diameter of 10 mm, and the induction coil is evenly distributed in the tube body in the form of a plurality of coil-type metal induction probes 5. The material of the tube body 1 can be a flexible material such as silicone, rubber or other hard materials.

[0113] The metal sensing probe 5 is bonded to the inner wall of the tube body 3, or fixed to the inner wall of the tube body through a bracket. The metal sensing probe 5 is led out from the inside of the tube body 3 and electrically connected to an external controller. The bracket can directly adopt the bracket structure provided in the fourth embodiment.

[0114] Among them, the metal sensing probe 5 is a partial component of the metal detector, which also includes a DC power supply, a metal probe connecting line, metal instruments for surgery, an integrated circuit board, the integrated circuit board includes a voltage comparator, an oscillation 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 oscillation circuit includes an R4 resistor, a first inductor, a second inductor, a first capacitor, a second capacitor, a transistor, and an R5 resistor. One point of the first inductor and the first capacitor connected in series is connected to Vcc, and the other end is connected to the base of the transistor. One end of R4 is connected to Vcc., and the other end is connected to the base of the transistor. The second point of the inductor is connected in parallel with the second capacitor, and one end is connected to Vcc, and the other end is connected to the emitter of the transistor. The collector of the transistor is connected in series with the 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 input end of the voltage comparator. The non-grounded end of the R5 resistor is connected to the non-inverting input end of the voltage comparator. The output end of the voltage comparator is connected in series with the R1 resistor and then connected to Vcc. One end of the R2 resistor connected in series with the LED warning light is connected to Vcc, and the other end is connected to the output end of the voltage comparator.

[0115] The induction coil is built into the metal induction probe, and two pins are left to be electrically connected to the integrated circuit board.

[0116] If the simulated nerve body is a simulated main nerve body, a probe is arranged in the tube body at each intervertebral connection on the simulated main nerve body.

[0117] If the simulated nerve body is a simulated main nerve body and a simulated branch nerve body that simulate multiple branches, a sensing probe is set at each two adjacent pathway nodes and at the pathway node and the pathway end, and two probes are symmetrically arranged on each simulated branch nerve body.

[0118] In surgical training and teaching, after the circuit is powered on, when the surgical instrument approaches or touches the simulated nerve body, the coil in the oscillation circuit generates a high-frequency magnetic field. When the target object approaches the magnetic field, an induced current eddy current is generated in the target object due to electromagnetic induction. As the target object approaches the simulated nerve body, the induced current increases, which in turn affects the change of the current in the magnetic field oscillation circuit. The port voltage of resistor R5 will change, and the voltage comparator determines the voltage of the same direction and reverse input terminals, and then the output terminal of the voltage comparator outputs a low level, and the LED warning light is on.

[0119] In particular, any one of the solutions in Examples 1 to 5 can be provided with the human body simulation nerve of this embodiment in the inner cavity of the bionic spine body 700 to form a new technical solution combination.

[0120] Example 8

[0121] This embodiment provides a bionic lumbar vertebra skeleton with X-ray imaging function, which is prepared by the following preparation steps:

[0122] Preparation of S1 bionic lumbar vertebral cancellous bone core layer:

[0123] a1 premixing: stir 100 parts of polyether polyol, 1 part of polydimethylsiloxane PDMS, 30 parts of 1,4-butanediol, 0.2 parts of catalyst A33, 1 part of triethanolamine, 10 parts of trimethylolpropane and 0.8 parts of deionized water in a mixing barrel at a stirring speed of 1000 rpm until evenly mixed, and this is material A;

[0124] a2 Add material B and mix: While keeping material A stirring, slowly add 170 parts of material B polyphenyl polymethylene polyisocyanate, the stirring speed needs to be adjusted to 500 rpm, and stir for 15 seconds;

[0125] a3 Foaming molding: Pour the mixed liquid material quickly into the lumbar vertebrae bone mold and seal the reaction. The temperature inside the mold is controlled at 25°C and the curing time is 24 hours.

[0126] Preparation of S2 cortical bone material outer layer raw material liquid:

[0127] b1 Pre-emulsification of styrene-acrylic emulsion: 20 parts of styrene, 10 parts of butyl acrylate, 20 parts of methyl methacrylate, 1.0 part of sodium dodecylbenzene sulfonate, 0.3 part of ammonium persulfate and 30 parts of deionized water were mixed in reactor A, and the temperature was raised to 40°C at a stirring speed of 500 rpm. After the temperature stabilized, the stirring speed was adjusted to 2000 rpm and the stirring time was 20 minutes to form a pre-emulsion;

[0128] b2 Styrene-acrylic emulsion polymerization: add 20 parts of deionized water, 0.5 parts of initiator ammonium persulfate, 0.5 parts of emulsifier sodium dodecylbenzene sulfonate and 15 parts of developer KI into reactor B, stir at 400 rpm and heat to 80°C, and add the pre-emulsion of step b1 dropwise under nitrogen protection, and carry out emulsion polymerization for 1 hour. After the reaction is completed, cool to room temperature to obtain an emulsion;

[0129] b3 Preparation of SAN resin emulsion: First, 0.5 parts of potassium persulfate KSP was dissolved in 50 parts of deionized water to prepare a 1% concentration of KSP aqueous solution for standby use, then 50 parts of deionized water and 1.0 part of sodium dodecylbenzene sulfonate were added to reactor C, and the temperature was raised to 65°C at a stirring speed of 400 rpm. Subsequently, under nitrogen protection, the KSP aqueous solution and the pre-mixed monomer mixture of 30 parts of styrene and 20 parts of acrylonitrile were added dropwise at the same dropping speed. After the addition was completed in 1 hour, the reaction was continued for 1 hour, and finally the mixture was cooled to room temperature while stirring to obtain SAN resin emulsion;

[0130] b4 Mixed SAN resin modification: The emulsion obtained in step b2 is stirred at a constant temperature in reactor B, 30 parts of the SAN resin emulsion prepared in step b3 are slowly added thereto, stirred evenly, the emulsion is cooled to room temperature, 0.5 parts of pigment are added, and stirred evenly to obtain a SAN resin-modified styrene-acrylic emulsion with X-ray development function.

[0131] S3 bionic lumbar vertebrae cortical bone preparation:

[0132] The cortical bone material prepared in step S2 is coated on the surface of the cancellous bone prepared in step S1 by spraying or dipping:

[0133] The spraying process is to use a thin spraying process, with a coating thickness of 0.3 mm each time. The next spraying is carried out after drying, and the number of spraying times is 5 times.

[0134] Example 9

[0135] The same preparation method as in Example 1 was used, except that 5 parts of SAN resin emulsion was added.

[0136] Example 10

[0137] The preparation was carried out in the same manner as in Example 1, except that 10 parts of styrene were added in step b1.

[0138] Embodiment 11

[0139] The preparation was carried out in the same manner as in Example 1, except that polyoxyethylene fatty alcohol ether was selected as the emulsifier.

[0140] Example 12

[0141] The preparation method is the same as that of Example 1, except that polyoxyethylene alkylphenol ether is used as the emulsifier.

[0142] Embodiment 13

[0143] The same preparation method as in Example 1 was used to prepare the product, except that the acrylic acid ester monomers were 10 parts of ethyl acrylate, 10 parts of butyl acrylate and 10 parts of methyl methacrylate.

[0144] Embodiment 14

[0145] The preparation was carried out in the same manner as in Example 1, except that 10 parts of potassium iodide KI and 5 parts of sodium iodide NaI were used as the developer.

[0146] Embodiment 15

[0147] The preparation method is the same as that of Example 1, except that the developer is a combination of 10 parts of potassium iodide KI, 3 parts of sodium iodide NaI and 2 parts of calcium iodide CaI2.

[0148] Example 16

[0149] This embodiment provides a bionic lumbar vertebra skeleton with X-ray imaging function, which is prepared by the following preparation steps:

[0150] S1 bionic lumbar vertebrae cancellous bone preparation:

[0151] a1 Premixing: Mix 10 parts of polyether polyol with 0.5 parts of polydimethylsiloxane PDMS, 10 parts of 1,4-butanediol, 0.1 parts of catalyst A33, 0.5 parts of triethanolamine, 0.1 parts of trimethylolpropane and 0.1 parts of deionized water in a mixing bucket. Keep the stirring speed at 1000 rpm and mix well to obtain material A.

[0152] a2 Add material B and mix: While keeping material A stirring, slowly add 10 parts of material B polyphenyl polymethylene polyisocyanate, the stirring speed needs to be adjusted to 300 rpm, and stir for 15 seconds.

[0153] a3 Foaming molding: Pour the mixed liquid material quickly into the lumbar vertebrae bone mold and seal the reaction. The temperature inside the mold is controlled at 25°C and the curing time is 24 hours.

[0154] Preparation of S2 cortical bone material:

[0155] b1 Pre-emulsification of styrene acrylic emulsion: In reactor A, 10 parts of styrene, 10 parts of ethyl acrylate, 19 parts of butyl acrylate, 0.5 parts of emulsifier polyoxyethylene fatty alcohol ether, 0.1 parts of chain transfer agent dodecyl mercaptan and 10 parts of deionized water were mixed and stirred to form a pre-emulsion at a stirring speed of 1000 rpm for 10 minutes.

[0156] b2 Styrene acrylic emulsion polymerization: add 10 parts of deionized water, 0.5 parts of initiator ammonium persulfate, 0.5 parts of emulsifier and 1 part of developer sodium iodide NaI into reactor B, stir and heat to 80°C, and add the pre-emulsion of step b1 dropwise under nitrogen protection, and carry out emulsion polymerization for 1 hour. After the reaction is completed, cool to room temperature to obtain an emulsion.

[0157] b3 Preparation of SAN resin emulsion: 30 parts of styrene ST, 20 parts of acrylonitrile AN, 0.5 parts of polyoxyethylene fatty alcohol ether, 0.5 parts of potassium persulfate KSP and 50 parts of deionized water were added into reactor C to form styrene-acrylonitrile copolymer SAN resin emulsion by emulsion polymerization at a suitable stirring speed of 1000 rpm for 10 minutes.

[0158] b4 Mixed SAN resin modification: The emulsion obtained in step b2 is stirred at a constant temperature in reactor B, 5 parts of the SAN resin emulsion prepared in step b3 are slowly added thereto, stirred evenly, the emulsion is cooled to room temperature, 0.1 parts of pigment are added, and stirred evenly to obtain a SAN resin-modified styrene-acrylic emulsion with X-ray development function.

[0159] S3 bionic lumbar vertebrae cortical bone preparation:

[0160] The dipping process is to pour the cortical bone material into a container, immerse all the cancellous bone material in the cortical bone material, slowly pull it out of the liquid surface after 30 seconds, and repeat the dipping twice after the emulsion slowly dries to form a developing coating.

[0161] Embodiment 17

[0162] This embodiment provides a bionic lumbar vertebra skeleton with X-ray imaging function, which is prepared by the following preparation steps:

[0163] S1 bionic lumbar vertebrae cancellous bone preparation:

[0164] a1 Premixing: Mix 20 parts of polyether polyol, 1.5 parts of polydimethylsiloxane PDMS, 40 parts of 1,4-butanediol, 0.5 parts of catalyst A33, 1.5 parts of triethanolamine, 10 parts of trimethylolpropane, and 3.0 parts of deionized water in a mixing barrel and stir evenly. Keep the stirring speed at 2000 rpm for 20 minutes to obtain material A.

[0165] a2 Add material B and mix: While keeping material A stirring, slowly add 170 parts of polyphenyl polymethylene polyisocyanate B material. The stirring speed needs to be adjusted to 500 rpm and continue stirring for 15 seconds.

[0166] a3 Foaming molding: Pour the mixed liquid material quickly into the lumbar vertebrae bone mold and seal the reaction. The temperature inside the mold is controlled at 55°C and the curing time is 30 minutes.

[0167] Preparation of S2 cortical bone material:

[0168] b1 Pre-emulsification of styrene acrylic emulsion: 20 parts of styrene, 10 parts of ethyl acrylate, 20 parts of butyl acrylate, 1.5 parts of polyoxyethylene alkylphenol ether, 3.0 parts of chain transfer agent and 40 parts of deionized water were mixed in reactor A and stirred to form a pre-emulsion at a stirring speed of 2000 rpm for 20 minutes.

[0169] b2 Styrene-acrylic emulsion polymerization: Add 60 parts of deionized water, 3 parts of ammonium persulfate, 1.0 part of polyoxyethylene alkylphenol ether and 30 parts of calcium iodide CaI2 into reactor B, stir and heat to 80°C, and add the pre-emulsion of step b1 dropwise under nitrogen protection, and carry out emulsion polymerization for 2 hours. After the reaction is completed, cool to room temperature to obtain an emulsion.

[0170] b3 Preparation of SAN resin emulsion: 30 parts of styrene ST, 20 parts of acrylonitrile AN, 1.0 part of polyoxyethylene alkylphenol ether, 0.5 part of potassium persulfate KSP and 100 parts of deionized water were added into reactor C, and styrene-acrylonitrile copolymer SAN resin emulsion was formed by emulsion polymerization method at a suitable stirring speed. The stirring speed was 2000 rpm and the stirring time was 20 minutes.

[0171] b4 Mixed SAN resin modification: The emulsion obtained in step b2 is stirred at a constant temperature in reactor B, 40 parts of the SAN resin emulsion prepared in step b3 are slowly added thereto, stirred evenly, the emulsion is cooled to room temperature, 1.0 part of pigment is added, and stirred evenly to obtain a SAN resin-modified styrene-acrylic emulsion with X-ray development function.

[0172] S3 bionic lumbar vertebrae cortical bone preparation:

[0173] Dipping process: immerse all the cancellous bone material in the cortical bone material, slowly pull it out of the liquid surface after 30 seconds, and repeat the dipping twice after the emulsion slowly dries to form a developing coating.

[0174] Comparative Example 1

[0175] The same preparation method as in Example 1 was used, except that 5 parts of a conventional developer, barium sulfate, was used as the developer.

[0176] Comparative Example 2

[0177] The preparation was carried out in the same manner as in Example 1, except that no SAN resin emulsion was added for modification. The implementation steps are as follows:

[0178] a) Pre-emulsification: 20 parts of styrene, 10 parts of butyl acrylate, 20 parts of methyl methacrylate, 1.0 part of sodium dodecylbenzene sulfonate, 0.3 part of ammonium persulfate and 30 parts of deionized water were mixed in reactor A, and the temperature was raised to 40° C. at a stirring speed of 500 rpm. After the temperature stabilized, the stirring speed was adjusted to 2000 rpm for 20 minutes to form a pre-emulsion.

[0179] b) Emulsion polymerization: 20 parts of deionized water, 0.5 parts of initiator ammonium persulfate, 0.5 parts of emulsifier sodium dodecylbenzene sulfonate and 15 parts of developer KI were added to reactor B, the temperature was raised to 80°C at a stirring speed of 400 rpm, and the pre-emulsion of step a was added dropwise under nitrogen protection, and emulsion polymerization was carried out for 1 hour. After the reaction was completed, the stirring speed was adjusted to 300 rpm, the temperature was lowered to 40°C, and 0.5 parts of white pigment rutile titanium dioxide was added and the stirring speed was adjusted to 500 rpm. After stirring for 10 minutes, a white styrene-acrylic emulsion with X-ray development function was obtained.

[0180] c Construction process: Use thin spraying process, the coating thickness of each spraying is 0.3mm, and the next spraying is carried out after drying. The number of spraying times is 5 times.

[0181] Comparative Example 3

[0182] The preparation is carried out in the same manner as in Example 1, except that the process of adding the developer is different. The implementation steps are as follows:

[0183] a) Pre-emulsification: 20 parts of styrene, 10 parts of butyl acrylate, 20 parts of methyl methacrylate, 1.0 part of sodium dodecylbenzene sulfonate, 0.3 part of ammonium persulfate and 30 parts of deionized water were mixed in reactor A, and the temperature was raised to 40° C. at a stirring speed of 500 rpm. After the temperature stabilized, the stirring speed was adjusted to 2000 rpm for 20 minutes to form a pre-emulsion.

[0184] b) Emulsion polymerization: 20 parts of deionized water, 0.5 parts of initiator ammonium persulfate, and 0.5 parts of emulsifier sodium dodecylbenzene sulfonate were added to the reactor B, and the temperature was raised to 80° C. at a stirring speed of 400 rpm, and the pre-emulsion of step a was added dropwise under nitrogen protection, and emulsion polymerization was carried out for 1 hour. After the reaction was completed, the stirring speed was adjusted to 300 rpm, and the temperature was lowered to room temperature to obtain an emulsion;

[0185] c Preparation of SAN resin emulsion: First, 0.5 parts of potassium persulfate KSP was dissolved in 50 parts of deionized water to prepare a 1% KSP aqueous solution for standby use, then 50 parts of deionized water and 1.0 part of sodium dodecylbenzene sulfonate were added to reactor C, and the temperature was raised to 65°C at a stirring speed of 400 rpm. Subsequently, under nitrogen protection, the KSP aqueous solution and the pre-mixed monomer mixture of 30 parts of styrene and 20 parts of acrylonitrile were added dropwise at the same dropping speed. After the addition was completed in 1 hour, the reaction was continued for 1 hour, and finally the mixture was cooled to room temperature while stirring to obtain SAN resin emulsion;

[0186] d) Modification by mixing SAN resin: the emulsion obtained in step b is heated to 40° C. in reactor B at a stirring rate of 300 rpm, 30 parts of SAN resin emulsion prepared in step c) is slowly added into reactor B within 15 minutes, and stirring and mixing is continued for 30 minutes after the dropwise addition is completed; 15 parts of developer KI and 0.5 parts of white pigment rutile titanium dioxide are added, and the stirring speed is adjusted to 500 rpm. After stirring for 10 minutes, a white SAN resin modified styrene acrylic emulsion with X-ray developing function is obtained.

[0187] eConstruction process: Use thin spraying process, the coating thickness of each spraying is 0.3mm, and the next spraying is carried out after drying. The number of spraying times is 5 times.

[0188] Performance Testing

[0189] 1. Hardness test:

[0190] The test of coating hardness is carried out according to the pencil method for measuring paint film hardness standard GB / T 6739-2022. After grinding, cleaning and drying the surface of a tinplate with a size of 120 mm × 50 mm × 0.3 mm, the prepared emulsion is evenly applied to the surface of the test plate with a paint brush. After drying at room temperature for 7 days, the test is carried out on a pencil scratch hardness tester. The scratch test is carried out three times with a pencil of the same hardness, and the damage of the sample is observed. The hardness of the hardest pencil that does not cause scratches on the coating is used to represent the pencil hardness of the coating.

[0191] 2. X-ray scanning test:

[0192] The Cios Select mobile C-arm X-ray machine of Shanghai Siemens Medical Devices Co., Ltd. was used to test the imaging effect of the prepared bionic lumbar vertebrae under the conditions of 60kV voltage, 10mA current and exposure for 0.2s.

[0193] Table 1 Hardness test data

[0194]

[0195] The hardness in Example 8 is the highest, indicating that the hardness of the coating can be significantly enhanced by using the optimal ratio of SAN resin, which is very critical for the construction of cortical bone in the bionic human skeletal structure.

[0196] By comparing Example 9 with Example 8, it can be seen that the amount of SAN resin used has a direct effect on hardness. This is because both styrene and acrylonitrile monomers are "hard monomers". Therefore, the hardness of the bionic cortical bone can be regulated by adjusting the amount of SAN resin emulsion to match the modulus of bones in different age groups.

[0197] The data of Example 10 and Example 14 further verified the effect of monomer composition on hardness and supported the strategy of optimizing hardness by changing the monomer ratio.

[0198] Compared to Comparative Example 2, Examples 8-17 all show higher hardness, which emphasizes the innovative use of SAN resin in improving the hardness and overall performance of the coating.

[0199] from Figure 16-21 It can be seen that the real lumbar vertebrae X-ray image Fig.16 Comparison, adding the traditional developer BaSO4 development effect of comparative example 1, Fig. 20 Poor, this is because BaSO4 is insoluble in the aqueous phase emulsion, resulting in BaSO4 being dispersed in the emulsion in the form of particles. Its development effect depends on the particle size. The density of BaSO4 is 4.50 g·cm -3 It is very easy to settle and stratify in the emulsion, resulting in poor development effect.

[0200] Comparative Example 3 Fig.21 The developer is added in the reaction step d. At this time, the emulsion system is already stable. Adding potassium iodide or sodium iodide salts will easily cause the emulsion system to break. Fig. 22 As shown, the brush coating process also leads to uneven coating film formation due to emulsion demulsification, and gravity causes the developer to easily deposit at the bottom of the bone, resulting in uneven development.

[0201] Fig. 22It is shown that the white emulsion sample of Comparative Example 3 has a stratification phenomenon, with the upper layer being a layer of clear water and the bottom layer being a precipitated emulsion. This stratification is caused by demulsification due to the instability of the emulsion preparation process. Demulsification refers to the aggregation and merging of oil droplets wrapped by the dispersed phase emulsifier in the emulsion due to insufficient stability, and then the separation of the water phase, resulting in the deposition of emulsion components and the formation of stratification. This phenomenon indicates that the emulsification effect and long-term stability of the emulsion are not good.

[0202] Fig.23 The bionic bone a of spraying Example 8, the real vertebra b, and the bionic bone c without spraying the developing coating are compared and developed. It can be seen that c has almost no developing effect, while the developing effect of a is ideal, close to the developing effect of the real vertebra b.

[0203] Based on the hardness data and X-ray development effect, it can be concluded that the emulsion has controllable hardness and good X-ray development effect, and can be used as a bone bionic coating. In addition, it can also be used as an industrial X-ray flaw detection coating.

[0204] The above are only preferred embodiments of the present invention and are not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present invention should be included in the protection scope of the present invention.

Claims

1. An intelligent spine bionic model, characterized in that: include: A model base (100) and a model shell (600), as well as a bionic spine body (700) with a developing effect arranged on the model base (100), and a simulated muscle layer (300) and a simulated skin layer wrapped outside the bionic spine body (700); The internal cavity of the bionic spine body (700) is provided with a bionic nerve body having a touch warning mechanism; The bionic neural body comprises a simulated neural body and an early warning mechanism arranged on the simulated neural body; the early warning mechanism comprises: The induction coil (6) is attached to the simulated nerve body. A power supply electrically connected to the induction coil (6) and an external controller for receiving the induction signal and processing it to issue an early warning; The simulated nerve body comprises an inner tube (1), the induction coil (6) is wound on the outer wall of the inner tube (1), and the outer surface of the induction coil (6) is coated with an outer coating wall (2); when the simulated nerve body is a single-branch pathway, the induction coil is continuously wound on the outer wall of the inner tube (1); when the simulated nerve body is a multi-branch interconnected pathway, the induction coil (6) on the inner tube (1) between two adjacent pathway nodes and between a pathway node and a pathway end are all independently wound; or, The simulated nerve body comprises a tube body (3), the induction coil is in the form of a plurality of coil-type metal induction probes (5) uniformly distributed inside the tube body (3); the metal induction probes (5) are bonded to the inner wall of the tube body, or the metal induction probes (5) are fixed to the inner wall of the tube body (3) via a bracket; The bionic spine body (700) comprises a core material layer and an outer material layer attached to the outside of the core material layer, and the bionic spine body (700) is a hard layer with a developing effect; The method for preparing the bionic vertebral column (700) comprises the following steps: S1. Preparation of the core material layer: Stirring and mixing the rigid polyurethane foam raw materials, pouring them into a lumbar vertebrae skeleton mold and foaming them to obtain a core material layer; S2, preparation of raw materials for the outer material layer: blending styrene acrylic emulsion and styrene-acrylonitrile copolymer emulsion to obtain liquid material for the outer material layer; S3. Preparation of bionic lumbar vertebrae: using a spraying or dipping process, the liquid material of the outer material layer is attached to the outer surface of the core material layer, and finally a bionic lumbar vertebrae with development is formed; Among them, the hardness of bionic cortical bone was regulated by adjusting the amount of styrene-acrylonitrile copolymer emulsion to match the modulus of bones in different age groups; The specific preparation steps of the core material layer are: 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 stirred evenly in a mixing barrel, and the stirring speed is maintained at 1000 rpm; S102, while stirring in step S101, slowly add 170 parts by weight of polyphenyl polymethylene polyisocyanate, adjust the stirring speed to 500 rpm, and stir rapidly for 15 seconds; S103, after rapid stirring, quickly pouring into a bone mold, and sealing the reaction, the temperature inside the mold is controlled at 25° C., and the curing time is 24 hours to obtain a solid core material layer; The specific preparation steps of the outer material layer liquid material are: S201, in a reactor A, 10-20 parts by weight of styrene, 20-30 parts by weight of an acrylic ester monomer, 0.5-1.5 parts by weight of an emulsifier, 0.1-3.0 parts by weight of a chain transfer agent and 10-40 parts by weight of deionized water are mixed and stirred to form a pre-emulsion; S202, adding 10-60 parts by weight of deionized water, 0.5-3 parts by weight of initiator, 0.5-1.0 parts by weight of emulsifier and 1-30 parts by weight of water-soluble developer into reactor B, stirring and heating to 80° C., and dropwise adding the pre-emulsion of step S201 under nitrogen protection, and performing emulsion polymerization for 1-2 hours. After the reaction is completed, cooling to room temperature to obtain an emulsion; the water-soluble developer is one, two or three of potassium iodide KI, sodium iodide NaI and calcium iodide CaI2; S203, adding 30 parts by weight of styrene, 20 parts by weight of acrylonitrile, 1.0 parts by weight of emulsifier, 0.5 parts by weight of potassium persulfate, and 100 parts by weight of deionized water into the reactor C, and forming a styrene-acrylonitrile copolymer emulsion by an emulsion polymerization method at a suitable stirring speed; S204, stirring the emulsion obtained in step S202 at a constant temperature in reactor B, and slowly adding 5-40 parts by weight of the styrene-acrylonitrile copolymer emulsion prepared in step S203, stirring evenly, cooling to room temperature, adding 0.1-1.0 parts by weight of pigment, stirring evenly to obtain an outer material layer liquid material with a developing function.

2. The intelligent spine bionic model according to claim 1, characterized in that: An inverted trapezoidal spine bracket (200) is arranged on the model base (100), and a simulated muscle layer (300) with a bionic spine body (700) arranged inside is placed in the spine bracket (200).

3. The intelligent spine bionic model according to claim 2, characterized in that: The spinal column bracket (200) comprises an embedding base (210) embedded in the model base (100), fan-shaped plates (220) arranged at both ends of the embedding base (210), and inclined plates (230) arranged at both sides of the embedding base (210); The upper end surface of the inclined plate (230) is provided with a skin layer receiving surface, and the simulated skin layer is provided on the upper end surface of the simulated muscle layer (300) with both sides drooping down to the skin layer receiving surface.

4. The intelligent spine bionic model according to claim 3, characterized in that: The model base (100) is provided with a cavity (111) for enhancing development, and the embedding base (210) is arranged above the cavity (111).

5. The intelligent spine bionic model according to claim 3, characterized in that: The spinal column bracket (200) is provided with liquid for simulating a surgical water environment.

6. The intelligent spine bionic model according to claim 5, characterized in that: The spinal column bracket (200) is provided with a liquid inlet and an overflow port, which are used to connect the interior of the spinal column bracket (200) with an external water source to form a flowing liquid.

7. The intelligent spine bionic model according to any one of claims 1 to 6, characterized in that: The simulated muscle layer (300) is integrally formed by casting.

8. The intelligent spine bionic model according to any one of claims 1 to 6, characterized in that: The shortest distance between adjacent ends of any two independently wound induction coils (6) remains spaced apart.

9. The intelligent spine bionic model according to any one of claims 1 to 6, characterized in that: The metal sensing probe (5) is led out from the inside of the tube body (3) and is electrically connected to an external controller.

Images