Hip injection training anthropomorphic dummy

Abstract

The invention provides a hip injection training anthropomorphic dummy, and relates to the technical field of medical instruments. The hip injection training simulation human comprises a basic structure, a monitoring structure and a scoring module used for displaying data, and is characterized in that the basic structure comprises an epidermal layer, a fat layer and a muscle layer, and all the layers are bonded and fixed through silica gel adhesives; the monitoring structure comprises angle monitoring, force monitoring and depth monitoring. According to the hip injection training dummy provided by the invention, the efficiency and effect of medical education and training are remarkably improved through the design of the basic structure, the monitoring structure and the scoring module.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly to a hip injection training simulator. Background Art

[0002] The simulator for hip injection practice is a teaching tool specifically designed for medical education and training, and is usually referred to as a hip injection training model. It is made by imitating the shape, structure and tissue characteristics of the human hip, and has a realistic touch and appearance. The simulator is internally provided with materials that simulate different tissues such as human muscles and fat layers, and can simulate the real injection resistance and feeling, helping medical students and practitioners practice hip injection techniques. They can repeatedly perform injection operation exercises without using real human bodies, familiarize themselves with the key points such as the correct injection site, needle insertion angle, depth and strength, so as to improve the proficiency and accuracy of injection skills, reduce the pain and risks brought to patients due to unskilled operation, and enhance the safety and quality of medical services.

[0003] In the current field of medical education and training, the simulator for hip injection practice is an important tool for improving the practical skills of medical staff. However, the existing hip injection practice simulators on the market mainly focus on the simulation at the material level. These simulators use special materials to imitate the texture and elasticity of tissues such as human hip muscles and fat as much as possible, so as to create a realistic feel for the trainees. In the actual training process, the trainees mainly rely on their own feelings to complete each injection operation. Under the oral guidance of teachers, they try to grasp the injection strength, needle insertion angle and penetration depth. Due to the lack of objective and accurate quantitative standards, it is difficult for the trainees to accurately understand the guiding intention of the teachers, and it is also difficult to accurately control the strength, angle and depth during each operation. They may try repeatedly, but still cannot clearly judge whether their operations meet the specifications, and can only grope forward. This leads to a slow progress and low efficiency in the training process, making it difficult for the trainees to master relatively proficient injection skills by spending a lot of time and energy, and it is difficult to achieve a qualitative improvement in a short time, nor can it meet the growing medical practice needs. Summary of the Invention

[0004] In view of the deficiencies of the prior art, the present invention provides a hip injection training simulator, which solves the problem of low efficiency of the existing training methods.

[0005] To achieve the above object, the present invention is realized by the following technical solutions: A hip injection training simulator, comprising a basic structure, a monitoring structure and a scoring module for displaying data, wherein the basic structure includes an epidermis layer, a fat layer and a muscle layer, and each layer is adhesively fixed by a silicone adhesive;

[0006] The epidermis layer has a thickness of 1.5-2 mm and is made of self-healing silicone Dow Corning SE 1700 material with a Shore hardness of 22A, a tensile strength of 8 MPa, and a tear strength of 25 kN / m, and the surface of the epidermis layer is sprayed with an anti-adhesion coating of polytetrafluoroethylene nanoparticle material;

[0007] The fat layer is 3-5 cm thick and is made of viscoelastic memory gel Ecoflex 00-30 mixed with silicone thickener material, with an elastic modulus of 5 kPa and a loss factor of 0.3. A honeycomb nylon mesh is pre-embedded in the fat layer with a pore size of 2 mm.

[0008] The muscle layer is a 1 cm upper layer of thermoplastic polyurethane material, and a 1 cm lower layer of a composite layer of a self-healing elastomer composite material, with a Shore hardness of 50A and a puncture resistance of 3-4N, and microencapsulated DCPD is mixed into the thermoplastic polyurethane;

[0009] The monitoring structure includes angle monitoring, force monitoring and depth monitoring;

[0010] The angle monitoring uses an infrared optical tracking array, with 8 sets of infrared transmitting-receiving pairs of tubes buried outside the injection area, with a wavelength of 850nm, and the surface of the needle is coated with an infrared reflective coating, and the needle insertion angle is calculated by blocking the light path;

[0011] The force monitoring uses an embedded flexible sensor carbon nanotube-silicone piezoresistive film, which is arranged between the epidermis and the fat layer, and adopts a dynamic baseline correction algorithm to eliminate resistance drift during the self-healing process of the material;

[0012] The depth monitoring uses capacitive interlayer detection, and serpentine copper electrodes are laid at the junction of the fat layer and the muscle layer, with a line width of 0.2mm and a spacing of 1mm. A 1MHz high-frequency signal is used. When the needle approaches, the capacitance between the electrodes changes, and the depth is calculated by the change in capacitance.

[0013] Preferably, the needle insertion angle in the angle monitoring is calculated by the light path blocking time difference:

[0014]

[0015] Among them, arcsin is the angle between the needle and the vertical direction, v is the preset needle insertion speed in mm / s, and Δt is the time difference.

[0016] Preferably, the time difference calibration in the angle monitoring is performed by measuring the reference time difference Δt0 at a known angle, and the error introduced by the change in the transmittance of silica gel needs to be compensated and corrected in real time:

[0017]

[0018] Among them, T0 is the infrared transmittance when not punctured.

[0019] Preferably, in the force monitoring, the puncture force has a linear relationship with the resistance change rate:

[0020]

[0021] F is the puncture force with the unit of N, is the resistance change rate, k is the sensitivity, and F0 is the pre-tightening force compensation used to eliminate the baseline drift caused by material deformation.

[0022] Preferably, in the force monitoring, to prevent the resistance drift during the recovery of the self-healing material, sliding window filtering is adopted:

[0023]

[0024] Among them, the sliding window filtering algorithm processes the data through a fixed-length time window (such as 1 second, including 50 sampling points). Each sampling point corresponds to a timestamp, and i represents the serial number of the sampling point within the window. The baseline value F 基线，i In the non-punctured state, the piezoresistive film will generate background noise due to factors such as environmental temperature and material deformation, and these noise values are called baseline values. represents the average value of all baseline values within the time window, N is the number of sampling points within the time window (the typical value is 50, corresponding to 1 second of data), and F 校准 is the calibrated puncture force with the unit of N.

[0025] Preferably, in the depth monitoring, the needle depth is proportional to the square root of the capacitance change rate:

[0026]

[0027] Among them, d is the needle depth with the unit of mm, C is the calibration constant, is the capacitance change rate.

[0028] 7. A hip injection training simulation man according to claim 6, wherein: in the depth monitoring, since the dielectric constant of the silicone is affected by temperature, compensation is required:

[0029] d 校准 = d·[1 - α·(T - T0)]

[0030] d 校准 is the needle depth after temperature compensation, d is the needle depth without compensation, T is the real-time temperature, T0 is the reference temperature with the unit of °C, usually 25 °C. Through the temperature coefficient α and the temperature deviation (T - T0), the influence of temperature on depth measurement is quantified and eliminated.

[0031] Preferably, the scoring module calculates the operation score based on the real-time data of angle, force, and depth; provides independent scores and comprehensive scores for angle deviation, force stability, and depth accuracy respectively; displays the scoring level and error prompts through a graphical interface, stores the data and scores of each training, and also needs to support the playback and analysis of the data.

[0032] The present invention provides a hip injection training simulator, which has the following beneficial effects:

[0033] The present invention provides a hip injection training simulator. The basic structure of the present invention precisely simulates the characteristics of human hip tissues using multi-layer materials. The epidermis layer uses self-healing silicone, the fat layer uses viscoelastic memory gel, and the muscle layer combines thermoplastic polyurethane and self-repairing elastomer to ensure that the simulator has a realistic touch and puncture resistance, while supporting rapid self-healing and long-term use. The monitoring structure uses an infrared optical tracking array, a carbon nanotube-silica piezoresistive film, and capacitive interlayer detection technology to accurately measure the needle insertion angle, puncture force, and needle tip depth in real time. Combining dynamic calibration and temperature compensation algorithms, it eliminates the errors caused by material characteristics and environmental interference to ensure data accuracy. The scoring module provides multi-dimensional scoring and comprehensive feedback based on the real-time data of angle, force, and depth, and intuitively displays the operation score and error prompts through a graphical interface to help trainees quickly master the key points of injection techniques. The overall design not only improves the objectivity and efficiency of training, but also reduces the operation risk, meets the high standards of medical practice, and has significant practicality and promotion value. Brief Description of the Drawings

[0034] Figure 1 It is a schematic diagram of the external structure of the hip simulator of the present invention. Detailed Embodiments

[0035] Next, the technical solutions in the embodiments of the present invention will be clearly and completely described in conjunction with the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present invention.

[0036] As Figure 1 shown, the embodiment of the present invention provides a hip injection training simulator, which includes a basic structure, a monitoring structure, and a scoring module for displaying data. The basic structure includes an epidermis layer, a fat layer, and a muscle layer, and each layer is adhesively fixed through a silicone adhesive.

[0037] The epidermis layer has a thickness of 1.5 - 2 mm and is made of self-healing silicone Dow Corning SE 1700 material. It has a Shore hardness of 22A, a tensile strength of 8 MPa, and a tear strength of 25 kN / m. The surface of the epidermis layer is sprayed with an anti-sticking coating of polytetrafluoroethylene nanoparticle material (to prevent the silicone from sticking to the needle after multiple punctures). The self-healing mechanism of the epidermis layer is as follows: The silicone molecular chain contains dynamic disulfide bonds, and after puncture, the molecular chain automatically recombines within 4 hours at a temperature of 35 - 40 °C;

[0038] The fat layer has a thickness of 3 - 5 cm and is made of viscoelastic memory gel Ecoflex 00 - 30 mixed with an organosilicon thickener material. It has an elastic modulus of 5 kPa and a loss factor of 0.3 (simulating the rheological properties of human fat). A honeycomb-shaped nylon mesh with a pore size of 2 mm is embedded in the fat layer to limit the excessive flow of the gel after puncture and cooperate with the self-healing of the epidermis layer. The overall structure restores its initial shape within 6 hours;

[0039] The muscle layer is a composite layer with 1 cm of thermoplastic polyurethane material on the upper layer and 1 cm of self-repairing elastomer composite material on the lower layer. It has a Shore hardness of 50A and a puncture resistance of 3 - 4 N (simulating the penetration feeling of the gluteus maximus muscle). Microencapsulated DCPD (dicyclopentadiene) is mixed into the thermoplastic polyurethane, and the repair agent is released after the needle punctures and ruptures at 25 °C. The repair time is 8 hours;

[0040] The monitoring structure includes angle monitoring, force monitoring, and depth monitoring.

[0041] Angle monitoring uses an infrared optical tracking array. Eight groups of infrared transmitting-receiving pairs of tubes are buried around the injection area, with a wavelength of 850 nm. The surface of the needle is coated with an infrared reflective coating. The angle of the needle entering the skin is calculated by the occlusion of the optical path. The sensor does not contact the needle, avoiding interference with the self-healing material, and the sensor can penetrate the silicone layer (the transmittance of the silicone to 850 nm infrared light > 90%);

[0042] The angle of the needle entering the skin is calculated by the time difference of the occlusion of the optical path:

[0043]

[0044] where arcsin is the angle between the needle and the vertical direction, v is the preset needle insertion speed in mm / s, and Δt is the time difference.

[0045] The calibration of the time difference measures the reference time difference Δt0 through a known angle (such as 0° vertical needle insertion). Due to the error introduced by the change in the light transmittance of the silicone, real-time dynamic compensation and correction are required:

[0046]

[0047] where T0 is the infrared transmittance when not punctured.

[0048] Force monitoring uses an embedded flexible sensor, a carbon nanotube-silicone piezoresistive film, which is set between the epidermis layer and the adipose layer. A dynamic baseline correction algorithm is adopted to eliminate the resistance drift during the self-healing process of the material. (Range: 0 - 10 N, sensitivity: 0.05 N, linearity R 2 > 0.99, bending life > 500,000 times);

[0049] The puncture force has a linear relationship with the resistance change rate:

[0050]

[0051] F is the puncture force in N, is the resistance change rate, k is the sensitivity, and F0 is the pre-tightening force compensation used to eliminate the baseline drift caused by material deformation.

[0052] To prevent the resistance drift during the recovery of the self-healing material, sliding window filtering is adopted:

[0053]

[0054] Among them, the sliding window filtering algorithm processes the data through a time window with a fixed length (such as 1 second, including 50 sampling points). Each sampling point corresponds to a timestamp, and i represents the serial number of the sampling point within the window. The baseline value F 基线，i is the background noise generated by the piezoresistive film due to factors such as environmental temperature and material deformation in the non-punctured state, and these noise values are called baseline values. represents the average value of all baseline values within the time window, N is the number of sampling points within the time window (typical value 50, corresponding to 1 second of data), and F 校准 is the calibrated puncture force in N.

[0055] Depth monitoring uses capacitive interlayer detection. A serpentine copper electrode is laid at the junction of the adipose layer and the muscle layer, with a line width of 0.2 mm and a spacing of 1 mm. A 1 MHz high-frequency signal is adopted to avoid the influence of the change in the dielectric constant of silicone. When the needle (conductive) approaches, the capacitance between the electrodes changes, and the depth is calculated through the capacitance change amount.

[0056] The needle depth is proportional to the square root of the capacitance change rate:

[0057]

[0058] Among them, d is the needle depth in mm, C is the calibration constant, is the capacitance change rate.

[0059] Since the dielectric constant of silicone is affected by temperature, compensation is required:

[0060] d 校准 = d·[1 - α·(T - T0)]

[0061] d 校准 is the needle depth after temperature compensation, d is the needle depth before compensation, T is the real-time temperature, T0 is the reference temperature, with the unit of °C, usually 25°C. Through the temperature coefficient α and the temperature deviation (T - T0), the influence of temperature on depth measurement is quantified and eliminated.

[0062] The scoring module includes calculating the operation score based on the real-time data of angle, force, and depth; providing independent scores and comprehensive scores for angle deviation, force stability, and depth accuracy respectively; displaying the scoring level and error prompts through a graphical interface, storing the data and scores of each training, and at the same time, it needs to support the playback and analysis of the data. Since in the medical field, the angle, force, and depth of hip injection all have standard parameters, the technical level of the training personnel can be judged by comparing the standard parameters with the detected parameters or through simple calculations, which belongs to conventional prior art means. Therefore, no detailed description is made here, such as Figure 1 The upper direction area shown is the position for displaying data, and the relevant processing hardware can be embedded and set at the center inside the hip simulator. Micropores are provided on the surface of each layer of the basic structure. After the liquid is injected, the liquid can drain through the micropores, and the material of the basic structure design can ensure that the training personnel can use it multiple times and is more durable.

[0063] The hip injection training simulator of the present invention's technology significantly improves the effectiveness of medical education and training through innovative design and has many core advantages. The basic structure uses multi-layer materials to accurately simulate the characteristics of human hip tissues. The epidermis uses self-healing silicone, which can automatically repair after puncture, ensuring the durability of the simulator for long-term use; the fat layer uses viscoelastic memory gel to simulate the rheological properties of human fat, and combines with a honeycomb nylon mesh to restrict the flow of the gel, ensuring rapid restoration of the structure after puncture; the muscle layer combines thermoplastic polyurethane and self-repairing elastomer to simulate the puncture resistance of the gluteus maximus muscle and automatically repairs after needle puncture, further extending the service life. The monitoring structure uses an infrared optical tracking array to measure the needle insertion angle in real time. The sensor does not contact the needle, avoiding interference with the self-healing material. At the same time, a dynamic compensation algorithm is used to eliminate the error caused by the change in the light transmittance of the silicone; force monitoring uses an embedded carbon nanotube-silicone piezoresistive film, combined with a dynamic baseline correction algorithm to eliminate the resistance drift during the self-healing process of the material, ensuring the accuracy of force measurement; depth monitoring uses capacitive interlayer detection technology to avoid the influence of changes in the dielectric constant of the silicone through high-frequency signals, and combines with a temperature compensation algorithm to ensure the accuracy of depth measurement. The scoring module provides multi-dimensional scoring and comprehensive feedback based on the real-time data of angle, force, and depth, intuitively displays the operation score and error prompts through a graphical interface, helps trainees quickly master the key points of injection techniques, and at the same time supports data storage and playback analysis, facilitating the tracking and improvement of training effects. The overall design not only improves the objectivity and efficiency of training, but also reduces the operation risk, meets the high standards of medical practice, and has significant practicality and promotion value. Through a realistic simulation experience, accurate data monitoring, and an intuitive feedback mechanism, this technology can effectively improve the proficiency and accuracy of the injection skills of medical staff, providing a strong guarantee for the quality of medical services.

[0064] Although the embodiments of the present invention have been shown and described, it will be understood by those of ordinary skill in the art that various changes, modifications, substitutions, and variations can be made to these embodiments without departing from the principles and spirit of the present invention. The scope of the present invention is defined by the appended claims and their equivalents.

Claims

1. A hip injection training simulator, comprising a basic structure, a monitoring structure and a scoring module for displaying data, characterized in that: The base structure includes an epidermis layer, a fat layer, and a muscle layer, and each layer is adhesively fixed by a silicone adhesive; The epidermis layer has a thickness of 1.5 - 2 mm, is made of self-healing silicone Dow Corning SE 1700 material, has a Shore hardness of 22A, a tensile strength of 8 MPa, a tear strength of 25 kN / m, and a non-stick coating of polytetrafluoroethylene nanoparticle material is sprayed on the surface of the epidermis layer; The fat layer has a thickness of 3 - 5 cm, is made of a viscoelastic memory gel Ecoflex 00 - 30 mixed with a silicone thickener material, has an elastic modulus of 5 kPa, a loss factor of 0.3, and a honeycomb-shaped nylon mesh with a pore size of 2 mm is embedded in the fat layer; The muscle layer is a composite layer with an upper layer of 1 cm of thermoplastic polyurethane material and a lower layer of 1 cm of self-healing elastomer composite material, has a Shore hardness of 50A, a puncture resistance of 3 - 4 N, and microencapsulated DCPD is mixed in the thermoplastic polyurethane; The monitoring structure includes angle monitoring, force monitoring, and depth monitoring; The angle monitoring uses an infrared optical tracking array. 8 groups of infrared transmitting-receiving pairs of tubes are buried around the injection area, with a wavelength of 850 nm, and the surface of the needle is coated with an infrared reflective coating. The needle insertion angle is calculated by light path occlusion; The force monitoring uses an embedded flexible sensor carbon nanotube-silicone piezoresistive film. The carbon nanotube-silicone piezoresistive film is set between the epidermis layer and the fat layer, and a dynamic baseline correction algorithm is used to eliminate the resistance drift during the self-healing process of the material; The depth monitoring uses capacitive interlayer detection. A serpentine copper electrode is laid at the junction of the fat layer and the muscle layer, with a line width of 0.2 mm and a spacing of 1 mm, and a 1 MHz high-frequency signal is used. When the needle approaches, the capacitance between the electrodes changes, and the depth is calculated through the change in capacitance; 2. The hip injection training simulator according to claim 1, characterized in that: In the angle monitoring, the needle insertion angle is calculated by the time difference of light path occlusion: Among them, arcsin is the angle between the needle and the vertical direction, v is the preset needle insertion speed, with the unit of mm / s, and Δt is the time difference.

3. The hip injection training simulator according to claim 2, characterized in that: In the angle monitoring, the time difference calibration is carried out by measuring the reference time difference Δt0 of the known angle. The error introduced by the change in the light transmittance of the silicone needs to be compensated in real time and dynamically corrected: Among them, T0 is the infrared transmittance when not punctured.

4. A hip injection training simulator according to claim 1, characterized in that: In the force monitoring, the puncture force has a linear relationship with the rate of change of resistance; F is the piercing force with the unit of N, is the resistance change rate, k is the sensitivity, and F0 is the pre-tightening force compensation used to eliminate the baseline drift caused by material deformation.

5. A hip injection training simulator according to claim 4, characterized in that: In the force monitoring, to prevent the resistance drift during the recovery process of the self-healing material, a sliding window filter is used; Among them, the sliding window filtering algorithm processes data through a time window of a fixed length (such as 1 second, including 50 sampling points). Each sampling point corresponds to a timestamp, and i represents the serial number of the sampling point within the window, and the baseline value F 基线，i In the non-puncturing state, the piezoresistive film will generate background noise due to factors such as environmental temperature and material deformation, and these noise values are called baseline values. 基线，i represents the average value of all baseline values within the time window. N is the number of sampling points within the time window (typical value 50, corresponding to 1 second of data), and F 校准 is the calibrated puncturing force, with the unit of N.

6. The hip injection training simulation man according to claim 1, characterized in that: In the depth monitoring, the depth of the needle is proportional to the square root of the rate of change of capacitance; where d is the needle depth in mm, C is the calibration constant, and is the capacitance change rate.

7. A hip injection training simulation mannequin according to claim 6, characterized in that: In the depth monitoring, because the dielectric constant of the silicone is affected by temperature, compensation is required; d 校准 = d·[1 - α·(T - T0)] d 校准 is the needle depth after temperature compensation, d is the needle depth before compensation, T is the real-time temperature, T0 is the reference temperature, with the unit of °C, usually 25 °C. Through the temperature coefficient α and the temperature deviation (T - T0), the influence of temperature on depth measurement is quantified and eliminated.

8. A hip injection training simulator according to claim 1, wherein: The scoring module includes calculating the operation score based on the real-time data of the angle, force, and depth; providing independent scores and comprehensive scores for the angle deviation, force stability, and depth accuracy respectively; displaying the scoring level and error prompt through a graphical interface, storing the data and scores of each training, and at the same time supporting the playback and analysis of the data.

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