Anesthesia intubation device with self-adaptive diameter

Abstract

The invention relates to the technical field of medical instruments, in particular to a diameter-adaptive anesthesia intubation device which comprises a trachea cannula, an adjusting module and a control module. The adjusting module comprises a radial actuating assembly and a detection assembly, the radial actuating assembly is embedded in the trachea cannula, the detection assembly is arranged on the trachea cannula, and the detection assembly is used for detecting the contact pressure between the trachea cannula and the airway wall; the control module is electrically connected with the radial actuating assembly and the detection assembly, and the control module is used for controlling the radial actuating assembly to adjust the tube diameter of the trachea cannula according to the contact pressure detected by the detection assembly. The device has the effect of reducing the risk of airway injury or untight ventilation sealing.

Description

Technical Field

[0001] This application relates to the technical field of medical devices, and in particular to an anesthesia intubation device with an adaptive diameter. Background Technology

[0002] Currently, endotracheal intubation is a crucial medical procedure for establishing an artificial airway and ensuring reliable ventilation for patients, and it is widely used in anesthesia, emergency care, and critical care. Clinically, endotracheal tubes are generally of a fixed diameter. Before the procedure, doctors need to estimate the airway size based on factors such as the patient's age, gender, and body type to select the appropriate tube size.

[0003] However, due to significant individual differences in airway anatomy among patients (such as congenital stenosis, pathological edema, tumor compression, traumatic deformities, etc.), designing a fixed tube diameter often leads to a series of problems in clinical practice: if the selected tube diameter is too large, it is prone to mechanical damage to the glottis and tracheal mucosa during insertion, which may lead to edema, bleeding, postoperative hoarseness, and in severe cases, even long-term scarring tracheal stenosis; if the selected tube diameter is too small, air leakage is likely to occur between the tube and the tracheal wall, which not only affects the efficiency of positive pressure ventilation but also increases the risk of aspiration of gastric contents, endangering the patient's life. Size mismatch also often requires doctors to repeatedly try different sizes of tubes, which undoubtedly prolongs the surgical preparation time and increases the risk of complications such as hypoxemia during the procedure.

[0004] Therefore, because the diameter of endotracheal tubes is fixed, they cannot adapt to the individual differences in the patient's airway, which may lead to airway damage or poor ventilation seal. There is an urgent need for an anesthesia intubation device with an adaptive diameter. Summary of the Invention

[0005] To reduce the risk of airway damage or poor ventilation seal, this application provides an anesthesia intubation device with an adaptive diameter.

[0006] This application provides an anesthesia cannulation device with an adaptive diameter, which adopts the following technical solution:

[0007] An anesthesia cannulation device with an adaptive diameter, comprising:

[0008] Endotracheal intubation;

[0009] The adjustment module includes a radial actuation component and a detection component. The radial actuation component is embedded in the endotracheal tube, and the detection component is disposed on the endotracheal tube. The detection component is used to detect the contact pressure between the endotracheal tube and the airway wall.

[0010] The control module is electrically connected to the radial actuation component and the detection component, respectively. The control module is used to control the radial actuation component to adjust the diameter of the endotracheal tube according to the contact pressure detected by the detection component.

[0011] By employing the above technical solution, the detection component can detect the contact pressure between the endotracheal tube and the airway wall. After acquiring this contact pressure data, the control module can control the radial actuation component to adjust the diameter of the endotracheal tube based on this data. This allows for targeted adjustment of the tube diameter according to different contact pressure conditions of the airway wall, achieving an adaptive adjustment function to adapt to individual differences in airway structure. This helps avoid damage or poor sealing caused by a fixed tube diameter mismatch with the airway. Simultaneously, this adaptive adjustment reduces reliance on operator experience, improves the success rate of first-time intubation, and shortens operation time. Moreover, in special circumstances, such as emergency needs or system malfunctions, the device can promptly adjust the tube diameter to ensure patient airway safety.

[0012] Optionally, the endotracheal tube includes a fixed section and several telescopic sections connected in sequence. The radial actuation component, the detection component, and the telescopic sections are equal in number and are arranged in a one-to-one correspondence. The control module can control any of the telescopic sections to deform through the radial actuation component to adjust the diameter of the telescopic section. The telescopic section is used to be inserted into the airway.

[0013] By adopting the above technical solution, the radial actuation components, detection components, and telescopic sections are equal in number and configured in a one-to-one correspondence. This allows the control module to adjust the tube diameter by controlling the phase change of any telescopic section through the radial actuation components. This facilitates independent adjustment of the tube diameter of each telescopic section based on the characteristics of different locations in the airway, achieving precise segmental matching of the entire airway morphology. This helps avoid problems caused by mismatches between fixed-diameter cannulas and different individuals or dynamically changing airways. For example, it can reduce the concentrated mechanical stress on local areas of the airway, reducing the risk of airway damage; it can also improve airway sealing efficiency, preventing leakage and aspiration; and it reduces reliance on operator experience, increasing the success rate of first-time cannulation and shortening operation time.

[0014] Optionally, the telescopic section includes an inner tube wall and an outer tube wall that are coaxial and interconnected, with a receiving cavity formed between the inner tube wall and the outer tube wall. The detection component is disposed on the outer tube wall, and the radial actuation component includes a plurality of shape memory alloy elements. The plurality of shape memory alloy elements are disposed in the receiving cavity and electrically connected to the control module respectively. The control module drives the outer tube wall to deform by heating the shape memory alloy elements, thereby expanding the diameter of the outer tube wall.

[0015] By adopting the above technical solution and utilizing the characteristics of shape memory alloy electrothermal drive, precise and reliable control of pipe diameter adjustment is achieved. Furthermore, the double-walled structure cleverly provides space for the actuation element, resulting in a compact structure that is easy to integrate.

[0016] Optionally, a plurality of the shape memory alloy elements constitute a continuous actuation network, which covers the inner tube wall in an array or continuous braided form.

[0017] By adopting the above technical solution, the separated actuation points are integrated into a continuous actuation surface, which enables the driving force to be transmitted to the outer tube wall more smoothly and evenly, avoiding local stress concentration and providing a foundation for achieving higher precision conformal bonding.

[0018] Optionally, some of the outer tube walls adopt an integrated flexible design.

[0019] By adopting the above technical solution and working in conjunction with a continuous actuation network, the entire adaptive region can achieve continuous gradient deformation without physical steps. This helps to eliminate the risk of sealing dead angles and secretion retention that may be caused by segment gaps, and enables the outer surface of the cannula to form a continuous curved surface without physical steps. This allows for more precise matching of the geometry of the airway inner wall, reducing local pressure and improving sealing.

[0020] Optionally, the adjustment module includes a cooling component, one end of which passes through the fixed section and is disposed within the receiving cavity. The cooling component is thermally connected to the shape memory alloy element and electrically connected to the control module. The control module is used to control the operation of the cooling component to cool the shape memory alloy element.

[0021] By adopting the above technical solution, when the shape memory alloy element is heated, the telescopic section undergoes a phase change and contracts, causing the tube diameter to expand. When the tube diameter needs to shrink, the cooling component can quickly remove the heat from the shape memory alloy element, allowing it to rapidly return to its original length, thereby shrinking the telescopic section tube diameter. This enables rapid adjustment of the tube diameter to better adapt to changes in airway morphology, improve the real-time response capability of the endotracheal intubation device to different airway environments, and help avoid damage to the airway caused by the shape memory alloy element being continuously in a high-temperature state, thus improving the safety of use.

[0022] Optionally, the cooling assembly includes a cooling pipe and a drive component. The cooling pipe is embedded in the inner wall of the receiving cavity and connected to the drive component. The cooling pipe is in contact with the shape memory alloy element. The drive component is electrically connected to the control module and is used to deliver cooling liquid into the cooling pipe.

[0023] By adopting the above technical solution, the control module can control the drive component to deliver cooling liquid to the cooling pipe embedded in the telescopic section and in contact with the shape memory alloy element. Since the cooling pipe is thermally connected to the shape memory alloy element, the cooling liquid can carry away the heat of the shape memory alloy element, making it cool down quickly. This allows the diameter of the telescopic section to shrink, which can quickly change the diameter of the endotracheal tube to adapt to changes in the airway, improve the response speed of the endotracheal tube diameter adjustment, and can also shrink the diameter in time when needed to avoid excessive compression of the airway and reduce the risk of airway damage.

[0024] Optionally, the shape memory alloy element is configured to automatically return to its initial state when the control module is powered off or fails, so that the telescopic section returns to its minimum pipe diameter.

[0025] By adopting the above technical solution, when the control module loses power or fails, the shape memory alloy element automatically returns to its initial state due to its inherent characteristics. Since the shape memory alloy element is embedded within the telescopic section, its return to its original state causes a corresponding change in the telescopic section, allowing it to return to its minimum diameter. This helps prevent the endotracheal tube from becoming too large and obstructing the airway in extreme cases such as when the control module malfunctions. It ensures that the tube can be easily removed or at least does not obstruct the airway, buying time for subsequent treatment and ensuring patient safety.

[0026] Optionally, the detection component includes multiple pressure sensors, which are evenly distributed along the circumference of the endotracheal tube, and each pressure sensor is electrically connected to the control module.

[0027] By adopting the above technical solution, multiple pressure sensors are evenly distributed along the circumference of the endotracheal tube and electrically connected to the control module. They can collect the contact pressure and airflow resistance parameters between the endotracheal tube and the tracheal wall in real time, providing high-fidelity real-time input to the control module. The control module can then calculate the airway geometry based on these data and output control signals to drive the actuator layer to adjust the tube diameter, achieving precise segmented matching of the entire airway morphology and improving the endotracheal tube's adaptive adjustment capability to the airway.

[0028] Optionally, the end of the endotracheal tube is provided with a cuff, and the adjustment module includes an inflation component that is connected to the cuff. The inflation component is used to introduce gas into the cuff after the endotracheal tube has been adjusted.

[0029] By adopting the above technical solution, after the endotracheal intubation is adjusted, the inflation component can introduce gas into the cuff, so that the cuff can seal the tiny gaps caused by airway irregularities with extremely low pressure, achieving micro-pressure sealing. This helps to reduce the risk of tracheal mucosal ischemia and damage caused by traditional high-pressure cuffs, ensure more reliable ventilation, and prevent air leakage and aspiration.

[0030] In summary, this application includes at least one of the following beneficial technical effects:

[0031] 1. The detection component detects the contact pressure between the endotracheal tube and the airway wall in real time. The control module controls the radial actuation component to adjust the diameter of the endotracheal tube according to the pressure, so as to achieve adaptive adjustment, adapt to individual airway structure, and solve the problem of mismatch between fixed diameter tubes and different individuals and dynamically changing airways.

[0032] 2. When the control module loses power or fails, the shape memory alloy element automatically returns to its initial state, so that the telescopic section returns to the minimum pipe diameter, avoiding the risk of airway blockage and solving the problem of lack of real-time sensing and closed-loop feedback control capabilities.

[0033] 3. The design of the cuff and inflation assembly achieves a micro-pressure ultimate seal, which helps reduce the risk of tracheal mucosal ischemia and damage caused by traditional high-pressure cuffs, ensuring more reliable ventilation and preventing air leakage and aspiration. Attached Figure Description

[0034] Figure 1 This is a schematic diagram of the overall structure of an anesthesia intubation device with an adaptive diameter according to an embodiment of this application.

[0035] Figure 2 This is a schematic diagram of an anesthesia intubation device with an adaptive diameter after the expansion of the telescopic section in an embodiment of this application.

[0036] Figure 3 It is along Figure 2 A cross-sectional view along line AA in the middle.

[0037] Explanation of reference numerals in the attached figures:

[0038] 1. Endotracheal tube; 11. Fixed section; 12. Telescopic section; 121. Inner tube wall; 122. Outer tube wall; 123. Receiving cavity; 13. Cuff; 2. Adjustment module; 21. Radial actuation assembly; 211. Shape memory alloy element; 22. Detection assembly; 221. Pressure sensor; 23. Cooling assembly; 231. Cooling pipeline; 232. Drive component; 24. Inflation assembly; 241. Inflation pipe; 242. Inflation interface; 3. Control module. Detailed Implementation

[0039] The following is in conjunction with the appendix Figure 1-3 This application will be described in further detail.

[0040] This application discloses an anesthesia intubation device with an adaptive diameter.

[0041] It should be noted that, in the description of this invention, the terms "center," "longitudinal," "lateral," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this invention.

[0042] Reference Figure 1 and Figure 2 An adaptive diameter anesthesia intubation device includes an endotracheal tube 1, an adjustment module 2, and a control module 3. The adjustment module 2 is connected to the endotracheal tube 1 and electrically connected to the control module 3, so that the control module 3 can adjust the diameter of the endotracheal tube 1 through the adjustment module 2, so that the endotracheal tube 1 adapts to different patients' airways, thereby helping to improve the safety and effectiveness of the endotracheal tube 1.

[0043] Reference Figure 2 and Figure 3 The endotracheal tube 1 is the main component used to insert into the patient's airway and establish a ventilation pathway. The endotracheal tube 1 includes a fixed section 11 and several telescopic sections 12 connected in sequence. The fixed section 11 has a fixed diameter and mainly serves as a guide and support during intubation. The fixed section 11 has a conventional tubular shape to meet functional requirements such as gas delivery. In this embodiment, both the fixed section 11 and the telescopic sections 12 are integrally molded from medical-grade silicone with a Shore A hardness of 40-60.

[0044] The telescopic section 12 is the core component for achieving adaptive diameter adjustment and is used for insertion deep into the patient's airway. In this embodiment, three telescopic sections 12 are provided. Each telescopic section 12 includes an inner tube wall 121 and an outer tube wall 122 that are coaxial and interconnected. The inner tube wall 121 is disposed inside the outer tube wall 122, and the inner tube wall 121 and the outer tube wall 122 are connected at both ends of each telescopic section 12 by a flexible ring structure, allowing the outer tube wall 122 to undergo radial displacement relative to the inner tube wall 121 under the drive of the radial actuation component 21.

[0045] A receiving cavity 123 is formed between the inner tube wall 121 and the outer tube wall 122. The three outer tube walls 122 adopt an integrated flexible design to form a continuous, smooth curved surface. The outer tube walls 122 are made of a flexible material with high compliance and good biocompatibility, forming the surface that comes into direct contact with the human airway.

[0046] The adjustment module 2 includes a radial actuation component 21, a detection component 22, a cooling component 23, and an air injection component 24. The number of radial actuation components 21 and detection components 22 is equal to the number of telescopic sections 12 and they are set in a one-to-one correspondence.

[0047] The radial actuation assembly 21 includes multiple shape memory alloy elements 211, which are disposed within the receiving cavity 123 and electrically connected to the control module 3. These multiple shape memory alloy elements form a continuous actuation network, which covers the inner tube wall 121 in an array or continuously woven pattern. In this embodiment, the actuation network covers the inner tube wall 121 in an array, and the shape memory alloy elements 211 are made of nickel-titanium shape memory alloy wire with a diameter of 0.1-0.2 mm.

[0048] The shape memory alloy element 211 is in a state of expansion and contraction at room temperature. When the control module 3 heats the shape memory alloy element 211, the shape memory alloy element 211 will undergo phase change and contraction, which will pull the expansion section 12 to deform, so that the diameter of the expansion section 12 will actively and uniformly expand.

[0049] It should be noted that the shape memory alloy element 211 is configured to automatically return to its initial state when the control module 3 is powered off or fails, so that the telescopic section 12 returns to its minimum diameter. The specific principle utilizes the inherent physical properties of shape memory alloys. Its "memory" state (i.e., the contracted state after being heated by electricity) requires continuous energy to maintain, while its natural state at room temperature (martensitic phase) is expansion and elongation. When the control module 3 is powered off or fails, it will actively or passively cut off all power to the shape memory alloy element 211. After losing its heat source, the shape memory alloy element 211 will automatically and physically return to its original, expanded natural state, thereby driving the entire tube to automatically retract to its initial, minimum diameter state, avoiding the risk of airway blockage.

[0050] In other embodiments, the shape memory alloy element 211 may also be replaced by other alloy materials with shape memory function, or by an electroactive polymer (EAP) drive element to achieve pipe diameter adjustment.

[0051] The cooling assembly 23 includes a cooling pipe 231 and a drive component 232. The cooling pipe 231 is embedded in the inner wall of the receiving cavity 123 and is located close to the outer pipe wall 122. The cooling pipe 231 is in contact with the shape memory alloy element 211, and one end of the cooling pipe 231 passes through the fixed section 11 and is connected to the drive component 232.

[0052] The drive unit 232 is electrically connected to the control module 3. In this embodiment, the drive unit 232 is a miniature pump to facilitate the delivery of cooling liquid into the cooling pipe 231. The cooling liquid is a sterile, room-temperature liquid, such as physiological saline.

[0053] When rapid reduction of the tube diameter is required, the control module 3 controls the drive unit 232 to work, pumping physiological saline into the cooling pipe 231 instantaneously, so that the physiological saline flows in the cooling pipe 231, thereby causing heat exchange between the cooling pipe 231 and the shape memory alloy element 211, actively and quickly removing the heat from the shape memory alloy element 211, so that it cools down quickly and returns to its original length, thereby reducing the tube diameter.

[0054] In this embodiment, by setting the cooling component 23, the response time of the shape memory alloy element 211 can be shortened from tens of seconds to within 1-2 seconds. In other embodiments, an additional infusion tube can be designed, and the drive component 232 can be connected to the cooling pipe 231 through the infusion tube to realize the delivery of coolant; or the cooling pipe 231 can be omitted, and a microfluidic cooling channel can be directly opened in the telescopic section 12, and the drive component 232 can be connected to the microfluidic cooling channel through the infusion tube to deliver coolant into the microfluidic cooling channel.

[0055] The detection component 22 includes multiple pressure sensors 221, which are embedded in the outer tube wall 122 and arranged in a ring array around the axis of the outer tube wall 122. Each ring array consists of 8 to 12 independent pressure sensors 221 evenly distributed, enabling real-time synchronous monitoring of the contact pressure of the tube segment over 360 degrees. All sensors synchronously acquire data at a frequency of 50 to 100 Hz, which is sufficient to capture the dynamic pressure changes between the tube wall and the airway wall during intubation, providing high-fidelity real-time input for the control algorithm. In this embodiment, the pressure sensors 221 are MEMS pressure sensors.

[0056] Multiple pressure sensors 221 are electrically connected to the control module 3, thereby enabling the pressure sensors 221 to transmit the detected contact pressure data to the control module 3 so that the control module 3 can make corresponding adjustment decisions.

[0057] The endotracheal tube 1 is end-effectorally provided with a cuff 13, which is made of a very thin polyurethane material (10-20 micrometers thick) and is located behind all adjustable tube segments. In this embodiment, the cuff 13 has "high capacity" and "low pressure" characteristics. The "high capacity" characteristic allows the cuff 13 to conform to the airway wall with a large contact area after inflation, while the "low pressure" characteristic means that only a very low gas pressure is required for it to deploy.

[0058] The gas injection assembly 24 includes a gas injection pipe 241 and a gas injection port 242. In this embodiment, one end of the gas injection pipe 241 is connected to the gas injection port 242, and the other end of the gas injection pipe 241 is embedded in the inner tube wall 121 and adapted to the telescopic section 12. The end of the gas injection pipe 241 embedded in the inner tube wall 121 is connected to the sheath 13. The gas injection port 242 is used to connect to an external gas source, so that a small amount of low-pressure gas can be injected into the sheath 13 when needed. In other embodiments, the gas injection pipe 241 may also be directly connected to the sheath 13.

[0059] Once the endotracheal tube 1 is in place and the diameter is adjusted, the endotracheal tube 1 has achieved shape matching and initial isolation with most of the airway walls through active adjustment. At this time, the cuff 13 only needs to be filled with a very small amount of gas to seal the tiny gaps caused by the irregularity of the airway with extremely low pressure (less than 20 cmH2O), achieving "ultimate micro-pressure seal" and fundamentally eliminating the risk of tracheal mucosal ischemia and damage caused by traditional high-pressure cuffs.

[0060] It should be noted that, to accommodate the radial deformation of the expansion section 12, the cooling pipe 231 and the air injection pipe 241 are both made of flexible corrugated pipe structure or highly ductile material. The wires connecting the various shape memory alloy elements 211 and the pressure sensor 221 are provided with sufficient length allowance and are arranged in a wavy pattern to ensure that the internal pipes and circuits are not damaged by excessive stretching during the entire stroke of the pipe diameter expansion and contraction.

[0061] The control module 3 employs a microcontroller integrating a microprocessor, power management unit, and drive circuitry, enabling it to receive sensor data and issue control commands. In this embodiment, the control module 3 selectively heats multiple shape memory alloy elements 211 via a multi-channel PWM drive circuit.

[0062] The implementation principle of the adaptive diameter anesthesia intubation device in this application embodiment is as follows: In the initial state or when no power is applied, the shape memory alloy element 211 is in the low-temperature martensitic phase, exhibiting a long and flexible state, at which time each telescopic section 12 is in its minimum natural diameter. The doctor inserts the endotracheal tube 1, which is in its minimum diameter state, into the patient's airway. After the tube is in place, the control module 3 is activated. The control module 3 begins to heat the shape memory alloy element 211.

[0063] As the temperature rises, the shape memory alloy element 211 undergoes a phase transformation into the austenitic phase, generating a contraction force that drives the outer tube wall 122 to expand radially, thereby increasing the diameter of the outer tube wall 122. During the expansion process, the pressure sensor 221 monitors the contact pressure between the outer tube wall 122 and the air passage wall in real time and feeds back the contact pressure distribution map along the length of the air passage to the control module 3.

[0064] The control module 3 has a preset contact pressure safety threshold (e.g., 25-30 cmH2O). For a certain expansion segment 12, as long as the pressure values ​​measured by all pressure sensors 221 on it are below this threshold, the control module 3 continues to heat the corresponding shape memory alloy element 211, causing it to continue to expand. When the pressure detected by any pressure sensor 221 on the expansion segment 12 reaches or slightly exceeds the threshold, the control module 3 immediately stops heating the shape memory alloy element 211 of that segment, fixing its diameter at the current size. This process is performed independently for all expansion segments 12, ultimately achieving segmented shape adaptation, so that the entire insertion part of the cannula will segmentally and precisely conform to the shape of the patient's airway wall. Finally, a small amount of low-pressure gas is injected into the cuff 13 at the end through the inflation assembly 24 to seal any possible tiny gaps, achieving a final, non-invasive airway seal.

[0065] If the diameter of a certain telescopic section 12 needs to be reduced during the adjustment process, or if the entire endotracheal tube 1 needs to be restored to its minimum diameter before extubation, the control module 3 will stop heating the relevant shape memory alloy element 211 and simultaneously activate the drive unit 232 to pump cooling liquid into the cooling pipe 231. The cooling liquid quickly absorbs the heat from the shape memory alloy element 211, causing it to cool down rapidly and return to the martensitic phase, losing its contractile force. The telescopic section 12 retracts to its minimum diameter due to the elasticity of the corrugated pipe wall.

[0066] In the event of an emergency such as a power outage or failure of the control module 3, heating of the shape memory alloy element 211 will immediately stop. It will cool naturally under the influence of body temperature and surrounding tissues and return to its initial martensitic state, thereby allowing each telescopic section 12 to automatically return to its minimum diameter, making it easy for doctors to quickly and safely pull out the entire device.

[0067] It should be noted that the diameter adjustment range of the endotracheal tube 1 in this application is within 30%-50%. For example, the maximum adjustable diameter of the endotracheal tube 1 with a basic outer diameter of 6 mm is 9 mm.

[0068] The above are all preferred embodiments of this application, and are not intended to limit the scope of protection of this application. Therefore, all equivalent changes made in accordance with the structure, shape and principle of this application should be covered within the scope of protection of this application.

Claims

1. An anesthesia cannulation device with an adaptive diameter, characterized in that, include: Endotracheal intubation (1); The adjustment module (2) includes a radial actuation component (21) and a detection component (22). The radial actuation component (21) is embedded in the endotracheal tube (1), and the detection component (22) is disposed on the endotracheal tube (1). The detection component (22) is used to detect the contact pressure between the endotracheal tube (1) and the airway wall. The control module (3) is electrically connected to the radial actuation component (21) and the detection component (22) respectively. The control module (3) is used to control the radial actuation component (21) to adjust the diameter of the endotracheal tube (1) according to the contact pressure detected by the detection component (22).

2. The adaptive diameter anesthesia cannulation device according to claim 1, characterized in that: The endotracheal tube (1) includes a fixed section (11) and several telescopic sections (12) connected in sequence. The radial actuation component (21), the detection component (22) and the telescopic sections (12) are equal in number and are set in a one-to-one correspondence. The control module (3) can control any of the telescopic sections (12) to deform through the radial actuation component (21) to adjust the diameter of the telescopic section (12). The telescopic section (12) is used to be inserted into the airway.

3. The adaptive diameter anesthesia cannulation device according to claim 2, characterized in that: The telescopic section (12) includes an inner tube wall (121) and an outer tube wall (122) that are coaxial and connected to each other. A receiving cavity (123) is formed between the inner tube wall (121) and the outer tube wall (122). The detection component (22) is disposed on the outer tube wall (122). The radial actuation component (21) includes a plurality of shape memory alloy elements (211). The plurality of shape memory alloy elements (211) are disposed in the receiving cavity (123) and electrically connected to the control module (3) respectively. The control module (3) drives the outer tube wall (122) to deform by heating the shape memory alloy elements (211) so that the diameter of the outer tube wall (122) expands.

4. The adaptive diameter anesthesia cannulation device according to claim 3, characterized in that: Multiple shape memory alloy elements (211) constitute a continuous actuation network, which covers the inner tube wall (121) in an array or continuous braided form.

5. The adaptive diameter anesthesia cannulation device according to claim 4, characterized in that: Several of the outer tube walls (122) adopt an integrated flexible design.

6. The adaptive diameter anesthesia cannulation device according to claim 3, characterized in that: The adjustment module (2) includes a cooling component (23), one end of which passes through the fixed section (11) and is disposed in the receiving cavity (123). The cooling component (23) is thermally connected to the shape memory alloy element (211) and electrically connected to the control module (3). The control module (3) is used to control the operation of the cooling component (23) to cool down the shape memory alloy element (211).

7. The adaptive diameter anesthesia cannulation device according to claim 6, characterized in that: The cooling assembly (23) includes a cooling pipe (231) and a drive (232). The cooling pipe (231) is embedded in the inner wall of the receiving cavity (123) and connected to the drive (232). The cooling pipe (231) is in contact with the shape memory alloy element (211). The drive (232) is electrically connected to the control module (3). The drive (232) is used to deliver cooling liquid into the cooling pipe (231).

8. The adaptive diameter anesthesia cannulation device according to claim 3, characterized in that: The shape memory alloy element (211) is configured to automatically return to its initial state when the control module (3) is powered off or fails, so that the telescopic section (12) returns to its minimum diameter.

9. The adaptive diameter anesthesia cannulation device according to claim 1, characterized in that: The detection component (22) includes multiple pressure sensors (221), which are evenly distributed around the circumference of the endotracheal tube (1) and are electrically connected to the control module (3).

10. The adaptive diameter anesthesia cannulation device according to claim 1, characterized in that: The end of the endotracheal tube (1) is provided with a cuff (13). The adjustment module (2) includes an air injection component (24), which is connected to the cuff (13). The air injection component (24) is used to introduce gas into the cuff (13) after the endotracheal tube (1) has been adjusted.

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