An apparatus for simulating esophageal and anorectal dynamic peristalsis

Abstract

The application discloses a device for simulating esophageal and anorectal dynamic peristalsis, comprising a gas bag, a gas pump and a control system. The specific implementation is as follows: the gas bag is arranged, and a plurality of independent gas bags with different shapes and sizes are reasonably arranged in the device according to the physiological structure characteristics of the esophagus and the anorectum, so as to simulate the digestive tract walls at different positions, and the adjacent gas bags are connected through flexible materials; the gas pump is connected with a gas circuit, and each gas bag is connected to a corresponding matched gas pump through an independent gas circuit, and the gas pump is used for adjusting the gas pressure, flow and duration output to the gas bag according to the control signal issued by the control system. The device for simulating esophageal and anorectal dynamic peristalsis disclosed by the application comprehensively and truly simulates the dynamic peristalsis process of positions such as the esophagus and the anorectum, and has important significance for improving the medical education quality, promoting the scientific research progress and driving the medical equipment innovation.

Description

Technical Field

[0001] This invention belongs to the field of digestive peristalsis simulation technology, specifically relating to a device for simulating the peristaltic dynamics of the esophagus and anorectum. Background Technology

[0002] In the fields of medical training, teaching, research, and medical equipment development, a deep understanding of the peristaltic mechanisms of the human digestive system, particularly the esophagus and anorectum, is crucial. The peristalsis in these areas directly relates to vital functions such as normal swallowing, preventing acid reflux, and waste excretion, and is of great significance for the diagnosis, treatment, and prevention of digestive system diseases. However, due to the complexity of the human internal environment and individual differences, conducting related research and teaching directly on human subjects presents numerous limitations.

[0003] However, most devices currently available on the market that simulate digestive tract functions focus on structural simulation or the realization of a single function, making it difficult to comprehensively and realistically simulate the peristaltic process of the esophagus, rectum, and other parts of the digestive tract. For example, traditional digestive tract models mostly use static display methods and cannot dynamically simulate the peristaltic process; while some advanced mechanical peristaltic pumps can achieve material transportation, their peristaltic mode is singular and lacks accurate simulation of the complex peristaltic characteristics of the human digestive tract.

[0004] Therefore, developing a device that can more realistically simulate the peristaltic dynamics of the esophagus and anorectum is of great significance for improving the quality of medical education, promoting scientific research progress, and driving innovation in medical equipment. Summary of the Invention

[0005] The main objective of this invention is to provide a device that simulates the peristaltic motion of the esophagus and anorectum, comprehensively and realistically simulating the peristaltic process of the esophagus, anorectum, and other parts of the body. This is of great significance for improving the quality of medical education, promoting scientific research progress, and driving innovation in medical equipment.

[0006] To achieve the above objectives, the present invention provides a device for simulating the peristaltic motion of the esophagus and anorectum, comprising an air bladder, an air pump, and a control system, wherein the simulation is specifically implemented as follows:

[0007] The air sac layout is designed to simulate the digestive tract walls of different parts by rationally arranging multiple independent air sacs of different shapes and sizes inside the device, based on the physiological structural characteristics of the esophagus and anorectum. Adjacent air sacs are connected by flexible materials.

[0008] The air pump is connected to the air circuit. Each airbag is connected to the corresponding matching air pump through an independent air circuit. The air pump is used to adjust the gas pressure, flow rate and duration output to the airbag according to the control signal issued by the control system.

[0009] The control system sends corresponding instructions to each air pump based on the preset peristalsis mode or externally input control signals. Upon receiving the control instructions, the air pumps start working. When peristalsis simulation begins, the air pumps inflate the corresponding air bladders, causing them to gradually expand. As gas is continuously injected, the air bladders exert pressure on the surrounding simulated tissues, simulating the expansion and peristalsis of the digestive tract wall. When the preset expansion level or time is reached, the air pumps stop inflating and begin deflating, causing the air bladders to gradually contract, simulating the contraction phase of the peristalsis process.

[0010] As a further preferred technical solution to the above technical solution, the control system coordinates the inflation and deflation operations of each air pump, including controlling the inflation sequence, inflation time difference, and inflation pressure parameters between different airbags, so as to realize the transmission, reflection, and superposition effects of peristaltic waves.

[0011] As a further preferred technical solution to the above technical solution, during the simulation process, the sensor monitors and records parameters of the airbag in real time, including the degree of inflation, peristalsis speed and pressure changes.

[0012] As a further preferred technical solution to the above technical solution, the following settings are made for esophageal peristalsis simulation:

[0013] According to the preset length of the esophagus, a ring-shaped air sac with a thickness of N mm is set at the head to simulate the upper esophageal sphincter. Then, a first preset number of ring-shaped air sacs with a thickness of A mm are continuously arranged in the first length to simulate the skeletal muscle area of ​​the upper esophagus.

[0014] In the subsequent second length, a second preset number of annular air bladders with a thickness of Bmm are continuously arranged to simulate the mixed presence of skeletal muscle and smooth muscle in the mid-esophagus;

[0015] In the next segment of the third length, a third predetermined number of annular air bladders with a thickness of Cmm are continuously arranged to simulate the smooth muscle region of the lower esophagus. Finally, a single annular air bladder with a thickness of Dmm is arranged at the tail end to simulate the lower esophageal sphincter. The inner diameter of each air bladder is 3cm when it is not inflated, simulating the maximum esophageal dilation diameter. Each air bladder component is equipped with a resilient septum, and an elastic membrane is arranged around the inner ring of each annular air bladder, connected to the central ring of the inner ring of each air bladder to simulate the esophageal mucosa. Each air bladder is equipped with an independent pressure sensor, inflation structure, and deflation structure, and is controlled by the control system to provide data feedback.

[0016] As a further preferred technical solution to the above technical solution, the following settings are made for simulating anorectal peristalsis:

[0017] According to the preset length of the anorectum, in the fourth length starting from the head, a fourth preset number of ring-shaped air sacs with a thickness of Emm are continuously arranged to simulate the mixed area of ​​the rectal circular muscles.

[0018] In the subsequent fifth length, a fifth preset number of annular airbags with a thickness of Fmm are continuously arranged to simulate the subcutaneous, superficial, deep, and mixed areas of the external anal sphincter and the internal anal sphincter. The inner diameter of the airbags in the mixed rectal muscle area is 5cm when uninflated, simulating the diameter of the rectum when it is full. The inner diameter of the airbags in the anal sphincter segment is 4cm when uninflated, simulating the diameter of the anus when defecating. Each airbag is equipped with a flexible septum, and an elastic membrane is arranged around the inner ring of the annular airbag, connected to the central ring of each airbag's inner ring, to simulate the rectal mucosa and anal canal mucosa. Each airbag is equipped with an independent pressure sensor, inflation structure, and deflation structure, and is controlled by the control system and provides data feedback.

[0019] As a further preferred technical solution of the above technical solution, during the debugging of the device, a pressure measuring conduit for debugging needs to be inserted inside to inflate and deflate each airbag, and record the pressure sensor readings of the airbags under the corresponding pressure of the pressure measuring conduit, so that the inner ring of the airbag provides the corresponding squeezing force when inflating and deflating the airbags in subsequent use.

[0020] After calibrating the pressure compensation of each airbag in the above manner, configure the operating logic, inflate the corresponding airbag to simulate the contraction of this muscle segment, deflate to simulate expansion, and the front and rear airbags cooperate with each other, inflating sequentially from front to back, and deflating after reaching the specified pressure, continuously forming a peristaltic wave.

[0021] First, the air pressure is input based on clinical data to adjust the closure of the upper and lower esophageal sphincters. The esophageal balloons in each segment contract to the resting diameter of the esophagus. Simulating the start of swallowing, the balloon corresponding to the upper esophageal sphincter depresses and expands, followed by the balloon corresponding to the lower esophageal sphincter. Once the balloon corresponding to the upper esophageal sphincter expands to the specified size, it immediately inflates and closes. The balloons in each esophageal segment inflate sequentially from front to back, depressuring after reaching the specified value to form a peristaltic wave. The inflation and deflation time intervals between each channel are set to 2-5 cm / s according to the arrangement distance. The time from the start of swallowing to the arrival of the esophageal peristaltic wave at the end of the esophagus is designated as the first time. The inflation and contraction of the balloon corresponding to the lower esophageal sphincter is set after the swallowing relaxation window, i.e., after the opening of the balloon corresponding to the upper esophageal sphincter. Once the balloon corresponding to the lower esophageal sphincter has finished inflating and contracting, one swallowing process is simulated.

[0022] While simulating swallowing, a peristaltic wave of appropriate amplitude is added to simulate non-propulsive uncoordinated contractions and intermittent normal peristalsis at 3-5 times per minute, as well as pressure changes in the position of the diaphragm, making the simulation more realistic.

[0023] The beneficial effects of this invention are as follows:

[0024] 1. Improving the Quality of Medical Education: Traditional medical teaching often relies on physical models or static images to demonstrate the peristaltic process of the digestive tract. This invention simulates the real peristaltic process, allowing students to visually observe the dynamic changes in the esophagus, rectum, and other parts of the body, deepening their understanding of digestive physiological mechanisms, thereby improving the quality and effectiveness of medical education.

[0025] 2. Promoting Scientific Research Progress: Understanding changes in peristaltic function is crucial for the diagnosis, treatment, and prevention of digestive tract diseases. This invention provides a controllable and repeatable peristalsis simulation platform, facilitating researchers to conduct peristalsis experiments under various conditions, explore peristaltic characteristics in different disease states, and provide strong support for research on digestive tract diseases.

[0026] 3. Supporting Medical Device R&D: Accurate simulation of the dynamics of target areas is a crucial step in evaluating device performance during the R&D process of medical devices. This invention can serve as a prototype or test platform in medical device R&D, helping engineers verify the device's performance in a simulated environment, optimize device design, and improve the device's practicality and reliability.

[0027] 4. Achieving High-Level Simulation: This invention employs multiple air pumps to control the inflation and deflation of multiple air bladders. By precisely adjusting the operating parameters of the air pumps, peristaltic waveforms of different intensities, frequencies, and directions can be simulated, achieving a high degree of simulation of the peristaltic dynamics of the esophagus, rectum, and other parts of the digestive tract. This simulation method not only conforms to physiological reality but also meets various teaching, research, and testing needs.

[0028] 5. Enhanced ease of operation and maintainability: The device of this invention adopts a modular design, with tight connections between components that are easy to replace. It also features an intuitive and user-friendly control interface and detailed operating instructions, enabling users to easily learn and quickly master the operation. Furthermore, the device has low maintenance costs, facilitating long-term use and maintenance. Attached Figure Description

[0029] Figure 1 This is a schematic diagram of the structure of a device for simulating the peristaltic motion of the esophagus and anorectum according to the present invention.

[0030] Figure 2 This is a schematic diagram of a device for simulating the peristaltic motion of the esophagus and anorectum according to the present invention.

[0031] Figure 3 This is a schematic diagram of a device for simulating the peristaltic motion of the esophagus and anorectum according to the present invention.

[0032] Figure 4This is a schematic diagram illustrating the debugging of a device for simulating the peristaltic motion of the esophagus and anorectum according to the present invention. Detailed Implementation

[0033] The following description is intended to disclose the present invention and enable those skilled in the art to implement it. The preferred embodiments described below are merely examples, and other obvious variations will occur to those skilled in the art. The basic principles of the invention defined in the following description can be applied to other embodiments, modifications, improvements, equivalents, and other technical solutions that do not depart from the spirit and scope of the invention.

[0034] In the preferred embodiments of the present invention, those skilled in the art should note that the esophagus, anorectum, and host computer involved in the present invention can be considered as prior art.

[0035] Preferred embodiment.

[0036] like Figure 1-4 As shown, this invention discloses a device for simulating the peristaltic motion of the esophagus and anorectum, including an airbag, an air pump, and a control system (i.e., the host computer and communication board in the figure). The specific implementation of the simulation is as follows:

[0037] The air sac layout involves rationally arranging multiple independent air sacs of different shapes and sizes inside the device, based on the physiological structural characteristics of the esophagus and anorectum, to simulate the digestive tract walls of different parts, and adjacent air sacs are connected by flexible materials (to simulate the continuity and flexibility of the digestive tract).

[0038] The air pump is connected to the air circuit. Each airbag is connected to the corresponding matching air pump through an independent air circuit. The air pump is used to adjust the gas pressure, flow rate and duration output to the airbag according to the control signal issued by the control system.

[0039] The control system receives control signals and performs air pump inflation and deflation operations. Based on a preset peristalsis mode or externally input control signals (such as signals from a computer program, teaching demonstration system, or medical equipment testing platform), the control system sends corresponding instructions to each air pump (these instructions include when to start inflation, when to stop inflation, when to start deflation, and the deflation rate, etc.). Upon receiving the control instructions, the air pumps begin to work. When peristalsis simulation begins, the air pumps inflate the corresponding air bladders, causing the air bladders to gradually inflate. As gas is continuously injected, the air bladders exert pressure on the surrounding simulated tissues, simulating the expansion and peristalsis of the digestive tract wall. When the preset degree of inflation or time is reached, the air pumps stop inflating and begin deflation, causing the air bladders to gradually contract, simulating the contraction phase of the peristalsis process.

[0040] Specifically, the control system coordinates the inflation and deflation operations of each air pump, including controlling parameters such as the inflation sequence, inflation time difference, and inflation pressure between different air bags, so as to realize the transmission, reflection and superposition effects of peristaltic waves (meanwhile, the control parameters are adjusted according to the simulated digestive tract parts and disease states), so as to simulate different peristaltic characteristics, such as Figure 2 shown).

[0041] More specifically, during the simulation process, sensors monitor and record parameters of the air bags including the degree of expansion, peristalsis speed and pressure changes in real time (these sensor data can not only be used to evaluate the authenticity and accuracy of the simulation effect, but also provide feedback information for the optimization of control algorithms. By continuously adjusting the control parameters and algorithms, the simulation accuracy and stability can be further improved).

[0042] Further, as shown in Figure 3 , the configuration for esophageal dynamic peristalsis simulation is as follows:

[0043] According to the preset length of the esophagus (preferably 26 cm), (a sleeve is provided externally to fix the internal structure) one annular air bag with a thickness of N mm is arranged at the head (typical value N=10, range 1<N<20) to simulate the upper esophageal sphincter (UES). Then, within the first length (preferably 8 cm), a first preset number (preferably 16) of annular air bags with a thickness of A mm (preferably 5 mm) are continuously arranged to simulate the skeletal muscle region of the upper esophagus (with relatively dense arrangement);

[0044] Subsequently, within the second length (preferably 8 cm), a second preset number (preferably 10) of annular air bags with a thickness of B mm (preferably 8 mm) are continuously arranged to simulate the mixed region of skeletal muscle and smooth muscle in the middle esophagus;

[0045] In the next third length (preferably 8 cm), a third preset number (preferably 8) of annular air bags with a thickness of C mm (preferably 10 mm) are continuously arranged to simulate the smooth muscle region (mainly) of the lower esophagus. Finally, one annular air bag with a thickness of D mm (preferably 10 mm) is arranged at the tail end to simulate the lower esophageal sphincter (the above air bags in each segment can be adjusted and configured according to the required simulation accuracy, such as refining the simulation of a certain segment of muscle and adjusting in combination with clinical examples). The inner diameter of each above-mentioned air bag in the uninflated state is 3 cm, which simulates the maximum expansion diameter of the esophagus. Tough spacers are arranged between each air bag to prevent displacement when the air bags expand, and a circle of elastic film is arranged on the inner ring of the annular air bags and connected to the central ring of the inner ring of each air bag to simulate the esophageal mucosa (lubricant can be applied on the surface when necessary to avoid stasis caused by different contraction sizes of front and rear air bags); each air bag is equipped with an independent pressure sensor, an inflation structure and a deflation structure, which are controlled by the control system and feed back data.

[0046] The principles of anorectal motility simulation and esophageal motility simulation are the same, but their device length, balloon thickness, number, and layout are different, such as... Figure 3 As shown, the settings for simulating anorectal peristalsis are as follows:

[0047] According to the preset length of the anorectal region (preferably 15cm), (with an external sleeve to fix the internal structure) in the fourth length (preferably 12cm) starting from the head, a fourth preset number (preferably 11) of ring-shaped air bladders with a thickness of Emm (preferably 10mm) are continuously arranged to simulate the rectal circular muscle mixing area of ​​the rectum.

[0048] In the subsequent fifth length (preferably 3cm), a fifth preset number (preferably 3) of annular airbags with a thickness of Fmm (preferably 10mm) are continuously arranged to simulate the subcutaneous, superficial, deep, and mixed areas of the external anal sphincter and the internal anal sphincter (the configuration of each airbag segment can be adjusted according to the required accuracy of the simulation, such as refining the simulation of a certain muscle segment and adjusting in conjunction with clinical examples). The inner diameter of the airbags in the mixed rectal muscle area is 5cm when not inflated, simulating the diameter when the rectum is full. The inner diameter of the airbags in the anal sphincter segment is 4cm when not inflated, simulating the diameter when the anus is defecating. Each airbag component is equipped with a flexible septum (to prevent displacement when the airbag expands). An elastic film is arranged around the inner ring of the annular airbag and connected to the central ring of each airbag inner ring to simulate the rectal mucosa and anal canal mucosa (a lubricant can be applied to the surface if necessary to avoid jerking caused by different contraction sizes of the front and rear airbags). Each airbag is equipped with an independent pressure sensor, inflation structure, and deflation structure, and is controlled by the control system and provides data feedback.

[0049] Furthermore, such as Figure 4 As shown, during device debugging, a pressure testing conduit needs to be inserted inside to inflate and deflate each airbag, and the pressure sensor readings of the airbags are recorded at the corresponding pressure of the pressure testing conduit, so that the inner ring of the airbag can provide the corresponding squeezing force when inflating and deflating the airbags in subsequent use.

[0050] After calibrating the pressure compensation of each airbag in the above manner, configure the operating logic, inflate the corresponding airbag to simulate the contraction of this muscle segment, deflate to simulate expansion, and the front and rear airbags cooperate with each other, inflating sequentially from front to back, and deflating after reaching the specified pressure, continuously forming a peristaltic wave.

[0051] (Taking a normal adult as an example) First, input the air pressure based on clinical data to adjust the closure of the upper and lower esophageal sphincters. The balloons in each segment of the esophagus contract to the resting diameter of the esophagus. Simulating the start of swallowing, the balloon corresponding to the upper esophageal sphincter depresses and expands, followed by the balloon corresponding to the lower esophageal sphincter depresses and expands. After the balloon corresponding to the upper esophageal sphincter expands to the specified size, it immediately inflates and closes. The balloons in each segment of the esophagus inflate sequentially from front to back, and depressurize after reaching the specified value, forming a peristaltic wave. The time interval between inflation and deflation of each channel is set to 2-5 cm / s according to the arrangement distance. The time from the start of swallowing to the arrival of the esophageal peristaltic wave at the end of the esophagus is set as the first time (approximately 9 seconds). The inflation and contraction of the balloon corresponding to the lower esophageal sphincter is set after the swallowing relaxation window, that is, after the opening of the balloon corresponding to the upper esophageal sphincter (10 seconds). After the balloon corresponding to the lower esophageal sphincter has finished inflating and contracting, the simulation of one swallowing process is completed (a continuous swallowing mode can also be configured based on clinical data).

[0052] While simulating swallowing, a peristaltic wave of appropriate amplitude is added to simulate non-propulsive uncoordinated contractions and intermittent normal peristalsis at 3-5 times per minute, as well as pressure changes in the position of the diaphragm, making the simulation more realistic.

[0053] The above is a simulation of the normal swallowing process. The esophageal motility simulation device can also adjust various parameters to simulate various functional esophageal diseases.

[0054] 1. Gastroesophageal reflux disease (GERD): mainly caused by relaxation of the lower esophageal sphincter and incomplete closure of the lower esophageal sphincter. According to clinical parameters, the air pressure of the lower esophageal sphincter position balloon in the device can be adjusted in the resting and swallowing states to make it relax the inner wall and not be able to close completely.

[0055] 2. Achalasia: Due to neuromuscular dysfunction of the esophageal cardia and incomplete relaxation of the lower esophageal sphincter, food cannot pass smoothly and becomes stagnant, gradually reducing esophageal tone and peristalsis, and causing esophageal dilation. Based on clinical parameters, the inflation pressure and deflation process of the lower esophageal sphincter balloon in the device can be adjusted to match the swallowing relaxation window after the UES segment balloon relaxes and opens, while the lower esophageal sphincter balloon remains tightly closed or partially relaxed, preventing the food bolus from passing normally.

[0056] 3. Functional esophageal spasm: The main manifestation is spasmodic contraction of esophageal smooth muscle. Based on clinical data, the inflation pressure and inflation / deflation process of the esophageal body segment balloon in the device during swallowing simulation can be adjusted (mainly the middle and lower esophagus are composed of smooth muscle segments, and the parameters can be adjusted appropriately according to the proportion of smooth muscle). After the UES segment balloon relaxes and opens, it does not form the peristaltic wave coordination in the normal mode, but inflates synchronously, keeping the esophageal body balloon in a tightly closed or incompletely relaxed state, and simulating muscle spasm through small-amplitude rapid inflation and deflation, so that the food bolus cannot pass through normally.

[0057] 4. Esophageal scleroderma: Primarily caused by esophageal stenosis and motility disorders due to degeneration, hardening, and atrophy of esophageal smooth muscle, as well as hyperplasia of submucosal connective tissue and mucosal atrophy. Based on clinical data, the inflation pressure and inflation / deflation process of the esophageal body segment balloons in the device can be adjusted during resting and swallowing simulations (mainly for the middle and lower esophagus segments composed of smooth muscle; parameters can be adjusted appropriately according to the proportion of smooth muscle). After the UES segment balloons relax and open, instead of forming the peristaltic wave pattern as in normal mode, the spacing between the peaks and troughs of the peristaltic waves in each balloon of the esophageal body is increased, the amplitude of relaxation and contraction is reduced, the peak movement speed is slowed, and the opening diameter of the esophageal body balloons is reduced, simulating esophageal atrophy and hardening, thus preventing the food bolus from passing normally.

[0058] In addition to the above-mentioned esophageal diseases, the inflation and deflation sequence and pressure of each balloon can be adjusted to simulate swallowing coordination disorders, and the inflation and deflation pressure of local balloons can be adjusted to simulate various diseases such as local muscle relaxation, hardening, and esophageal atrophy caused by foreign bodies in the esophagus and local lesions.

[0059] The anorectal motility simulation device (taking a normal adult as an example) first inputs air pressure based on clinical data, adjusts the closure of the anal sphincter, and causes each air bladder in the rectal segment to contract to the resting internal diameter of the rectum. When the simulated defecation begins, the air bladder corresponding to the anal sphincter releases pressure and relaxes in preparation. Then, the air bladder corresponding to the rectal circular muscle expands to a specified size and immediately inflates and closes. Inflation proceeds sequentially from front to back, and pressure is released after reaching a specified value, forming a peristaltic wave (because the speed of fecal movement is related to many factors such as fecal volume, texture, and intestinal pressure, the speed of this peristaltic wave needs to be adjusted according to the actual simulation requirements). The pressure release and contraction of the air bladder corresponding to the anal sphincter is set to simulate the relaxation and opening of the internal and external anal sphincter muscles when the feces reach the anus after the peristaltic wave of the rectal circular muscle air bladder arrives. When the fecal expulsion process is simulated, the air bladder corresponding to the anal sphincter inflates and contracts, and a normal defecation process is simulated.

[0060] The above is a simulation of the normal defecation process. The anorectal peristalsis simulation device can also adjust various parameters to simulate various anorectal functional diseases:

[0061] 1. Anal sphincter achalasia: Due to dysfunction of the internal anal sphincter, it cannot relax normally during defecation, resulting in difficulty in defecation. According to clinical parameters, the inflation pressure and deflation process of the anal sphincter position bladder of the device can be adjusted to match the defecation process. When the peristaltic wave simulated by the bladder in the rectal circular muscle segment arrives, the anal sphincter position bladder remains tightly closed or incompletely relaxed, so that the stool cannot pass through normally.

[0062] 2. Anal sphincter relaxation: Anal sphincter relaxation prevents the anus from closing properly, causing fecal incontinence. According to clinical parameters, the inflation pressure and deflation process of the anal sphincter position bladder of the device can be adjusted to keep the anal sphincter position bladder in a partially closed state, so that the feces cannot be retained in the rectum normally.

[0063] In addition to the above-mentioned anorectal diseases, the inflation and deflation sequence and pressure of each airbag can be adjusted to simulate muscle coordination disorder during defecation, and the inflation and deflation pressure of local airbags can be adjusted to simulate various diseases such as local muscle relaxation, hardening, and anorectal atrophy caused by foreign bodies and local lesions in the anorectal region.

[0064] It is worth mentioning that, to facilitate the observation and analysis of the simulation effects, the device may also be equipped with a visualization system. This system can visually present the inflation and contraction process of the airbag through a simulated cavity made of transparent material or virtual reality technology. Simultaneously, sensor data can be displayed on a screen in real time for users to conduct further analysis and research.

[0065] The device for simulating esophageal and anorectal peristalsis designed in this invention has demonstrated significant technical effects and advantages in multiple aspects, including medical education, scientific research, and medical equipment development. These advantages are specifically reflected in the following aspects:

[0066] 1. Highly realistic simulation effect:

[0067] The device adopts a multi-airbag structure, and each airbag can be controlled independently. By precisely adjusting the inflation and deflation process of multiple air pumps, it can simulate complex and varied peristaltic waveforms, including key parameters such as peristaltic speed, force, frequency, and direction, which highly restores the real state of peristaltic dynamics in the human digestive tract.

[0068] The simulation process is continuous and smooth, and can demonstrate physiological phenomena such as the propagation, reflection, and superposition of peristaltic waves, providing medical learners with an intuitive and vivid visual experience.

[0069] 2. Improve teaching quality and effectiveness:

[0070] In the field of medical training and teaching, this device serves as a teaching aid, helping students better understand the physiological mechanisms of gastrointestinal motility and deepen their understanding of digestive system diseases.

[0071] Through hands-on practice and observation, students can intuitively experience the dynamic changes in the peristaltic process, enhancing their learning interest and enthusiasm, thereby improving teaching effectiveness.

[0072] 3. Promote scientific research progress and innovation:

[0073] In the field of scientific research, this device provides researchers with a controllable and repeatable peristalsis simulation platform, facilitating peristalsis experimental research under various conditions.

[0074] Researchers can adjust device parameters to simulate peristaltic characteristics under different disease states, explore the mechanisms of disease development, and provide new ideas and methods for the diagnosis, treatment and prevention of digestive tract diseases.

[0075] 4. Support the research and development and optimization of medical equipment:

[0076] In the research and development of medical devices, this device can be used as a prototype or test platform to verify the working effect and performance of medical devices in a simulated environment.

[0077] By comparing the results with real peristaltic processes, the accuracy, reliability, and safety of medical devices can be evaluated, providing data support for the optimization and improvement of the devices.

[0078] 5. Easy to operate and simple to maintain:

[0079] The device adopts a modular design, with tight connections between components that are easy to replace, reducing maintenance costs.

[0080] Equipped with an intuitive and easy-to-use control interface and detailed operating instructions, users can quickly get started and master the operation methods without professional training.

[0081] 6. Broad application prospects:

[0082] This device is not only suitable for medical education, scientific research and medical equipment development, but can also be extended to medical training, simulated surgery, rehabilitation therapy and many other aspects, and has broad market application prospects and social value.

[0083] It is worth mentioning that the technical features of the esophagus, anorectum, and host computer involved in this patent application should be regarded as prior art. The specific structure, working principle, and possible control methods and spatial arrangement of these technical features can be adopted using conventional choices in the field and should not be regarded as the inventive point of this patent. This patent will not be further elaborated in detail.

[0084] For those skilled in the art, modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this invention should be included within the protection scope of this invention.

Claims

1. A device for simulating the peristaltic motion of the esophagus and anorectum, characterized in that, Including airbags, air pumps, and control systems, the simulation implementation is as follows: The air sac layout is designed to simulate the digestive tract walls of different parts by rationally arranging multiple independent air sacs of different shapes and sizes inside the device, based on the physiological structural characteristics of the esophagus and anorectum. Adjacent air sacs are connected by flexible materials. The air pump is connected to the air circuit. Each airbag is connected to the corresponding matching air pump through an independent air circuit. The air pump is used to adjust the gas pressure, flow rate and duration output to the airbag according to the control signal issued by the control system. The control system sends corresponding instructions to each air pump based on the preset peristalsis mode or externally input control signals. Upon receiving the control instructions, the air pumps start working. When peristalsis needs to be simulated, the air pumps inflate the corresponding air bladders, causing the air bladders to gradually inflate. As gas is continuously injected, the air bladders exert pressure on the surrounding simulated tissues, simulating the expansion and peristalsis of the digestive tract wall. When the preset degree of inflation or time is reached, the air pumps stop inflating and begin deflating, causing the air bladders to gradually contract, simulating the contraction phase during the peristalsis process. Configure the esophageal peristalsis simulation: According to the preset length of the esophagus, a ring-shaped air sac with a thickness of N mm is set at the head to simulate the upper esophageal sphincter. Then, a first preset number of ring-shaped air sacs with a thickness of A mm are continuously arranged in the first length to simulate the skeletal muscle area of ​​the upper esophagus. In the subsequent second length, a second preset number of annular air bladders with a thickness of Bmm are continuously arranged to simulate the mixed presence of skeletal muscle and smooth muscle in the mid-esophagus; In the next segment of the third length, a third predetermined number of annular air bladders with a thickness of Cmm are continuously arranged to simulate the smooth muscle region of the lower esophagus. Finally, a single annular air bladder with a thickness of Dmm is arranged at the tail end to simulate the lower esophageal sphincter. The inner diameter of each air bladder is 3cm when it is not inflated, simulating the maximum esophageal dilation diameter. Each air bladder component is equipped with a resilient septum, and an elastic membrane is arranged around the inner ring of each annular air bladder, connected to the central ring of the inner ring of each air bladder to simulate the esophageal mucosa. Each air bladder is equipped with an independent pressure sensor, inflation structure, and deflation structure, and is controlled by the control system to provide data feedback.

2. The device for simulating esophageal and anorectal peristalsis according to claim 1, characterized in that, The control system coordinates the inflation and deflation operations of each air pump, including controlling the inflation sequence, inflation time difference, and inflation pressure parameters between different airbags, in order to achieve the transmission, reflection, and superposition effects of peristaltic waves.

3. The device for simulating esophageal and anorectal peristalsis according to claim 2, characterized in that, During the simulation, sensors monitor and record parameters of the airbag in real time, including the degree of inflation, peristalsis speed, and pressure changes.

4. The device for simulating esophageal and anorectal peristalsis according to claim 3, characterized in that, Configure settings for anorectal peristalsis simulation: According to the preset length of the anorectum, in the fourth length starting from the head, a fourth preset number of ring-shaped air sacs with a thickness of Emm are continuously arranged to simulate the mixed area of ​​the rectal circular muscles. In the subsequent fifth length, a fifth preset number of annular airbags with a thickness of Fmm are continuously arranged to simulate the subcutaneous, superficial, deep, and mixed areas of the external anal sphincter and the internal anal sphincter. The inner diameter of the airbags in the mixed rectal muscle area is 5cm when uninflated, simulating the diameter of the rectum when it is full. The inner diameter of the airbags in the anal sphincter segment is 4cm when uninflated, simulating the diameter of the anus when defecating. Each airbag is equipped with a flexible septum, and an elastic membrane is arranged around the inner ring of the annular airbag, connected to the central ring of each airbag's inner ring, to simulate the rectal mucosa and anal canal mucosa. Each airbag is equipped with an independent pressure sensor, inflation structure, and deflation structure, and is controlled by the control system and provides data feedback.

5. The device for simulating esophageal and anorectal peristalsis according to claim 4, characterized in that, During device commissioning, a pressure testing conduit needs to be inserted inside to inflate and deflate each airbag. The pressure sensor readings of the airbags are recorded at the corresponding pressure of the pressure testing conduit, so that the inner ring of the airbag can provide the corresponding squeezing force when inflating and deflating the airbags in subsequent use. After calibrating the pressure compensation of each airbag in the above manner, configure the operating logic, inflate the corresponding airbag to simulate the contraction of this muscle segment, deflate to simulate expansion, and the front and rear airbags cooperate with each other, inflating sequentially from front to back, and deflating after reaching the specified pressure, continuously forming a peristaltic wave. First, the air pressure is input based on clinical data to adjust the closure of the upper and lower esophageal sphincters. The esophageal balloons in each segment contract to the resting diameter of the esophagus. Simulating the start of swallowing, the balloon corresponding to the upper esophageal sphincter depresses and expands, followed by the balloon corresponding to the lower esophageal sphincter. Once the balloon corresponding to the upper esophageal sphincter expands to the specified size, it immediately inflates and closes. The balloons in each esophageal segment inflate sequentially from front to back, depressuring after reaching the specified value to form a peristaltic wave. The inflation and deflation time intervals between each channel are set to 2-5 cm / s according to the arrangement distance. The time from the start of swallowing to the arrival of the esophageal peristaltic wave at the end of the esophagus is designated as the first time. The inflation and contraction of the balloon corresponding to the lower esophageal sphincter is set after the swallowing relaxation window, i.e., after the opening of the balloon corresponding to the upper esophageal sphincter. Once the balloon corresponding to the lower esophageal sphincter has finished inflating and contracting, one swallowing process is simulated. While simulating swallowing, a peristaltic wave of appropriate amplitude is added to simulate non-propulsive uncoordinated contractions and intermittent normal peristalsis at 3-5 times per minute, as well as pressure changes in the position of the diaphragm, making the simulation more realistic.

Images