Blood transfusion and infusion warming tube and temperature control method thereof

Abstract

The application discloses a blood transfusion and infusion heating tube and a temperature control method thereof. The heating tube comprises a heating tube body, a heating module, a vibration motor and a controller. The heating tube body comprises a heating tube pipeline for transmitting blood or liquid. The heating module is arranged on the outer wall of the heating tube body and is used for heating the heating tube body and acquiring the heating temperature of the heating tube pipeline during the heating process. The vibration motor is fixed in the heating tube body and is fixedly connected with the heating module, and is used for driving the heating module to vibrate synchronously when vibrating, so that the bubbles generated by blood transfusion or infusion are gathered in the infusion cavity. The controller is electrically connected with the heating module and the vibration motor, respectively, and is used for controlling the heating module and the vibration motor to work during infusion or blood transfusion, and receiving the heating temperature of the heating tube pipeline acquired by the heating module in a preset period. By using the system, the small bubbles in the liquid are actively eliminated, the risk of gas embolism is effectively reduced, and the structure is simple.

Description

Technical Field

[0001] This invention relates to the technical field of medical devices, and in particular to a blood transfusion and infusion heating tube and its temperature control method. Background Technology

[0002] Intravenous infusion / transfusion is one of the most basic and commonly used treatment methods in clinical medicine, used to replenish body fluids, electrolytes, nutrients, or blood products. In cold environments, during large-volume rapid infusion / transfusion, or when refrigerated medications are administered, the direct entry of low-temperature fluids into the patient's body can easily cause chills, vasospasm, limb numbness, and even adverse cardiac events. Therefore, it is necessary to warm the infused fluids.

[0003] Currently, existing infusion warming devices involve structures such as a housing, a heating element, and a bubble detector. This device heats the infusion tubing using the heating element to increase the fluid temperature, while simultaneously using a bubble detector to monitor the presence of bubbles in the infusion tubing in real time, thus determining the presence of bubbles and preventing them from being introduced into the patient's body.

[0004] However, the aforementioned existing technical solutions still have the following technical defects: the device can only passively detect bubbles and cannot actively eliminate the tiny bubbles generated during the heating process. When bubbles are detected, medical staff still need to manually flick or shake the infusion tube to remove them, resulting in low defoaming efficiency, difficulty in maintaining a consistent effect, and the inability to achieve real-time, automatic bubble removal during infusion / transfusion, posing a safety hazard of air embolism. Summary of the Invention

[0005] This invention provides a blood transfusion and infusion heating tube and its temperature control method. By setting a vibration motor fixedly connected to the heating module, the heating tube body is driven to vibrate at high frequency and micro amplitude during the heating process, so that the tiny bubbles generated by infusion or blood transfusion actively gather in the infusion chamber. At the same time, the heating temperature is adjusted by the controller in a closed loop, thereby achieving precise temperature control and active defoaming, eliminating the risk of cold stimulation and air embolism. The structure is simple.

[0006] In a first aspect, the present invention provides a blood transfusion and infusion heating tube, comprising: a heating tube body, a heating module, a vibration motor, and a controller;

[0007] The heating tube body includes a heating pipe, which is used to transport blood or liquid;

[0008] The heating module is located on the outer wall of the heating pipe body and is used to heat the heating pipe body and obtain the heating temperature of the heating pipe during the heating process.

[0009] The vibration motor is fixed inside the heating tube and is fixedly connected to the heating module. It is used to drive the heating module to vibrate synchronously during vibration so that the air bubbles generated by blood transfusion or infusion can gather in the infusion chamber.

[0010] The controller is electrically connected to the heating module and the vibration motor respectively. It is used to control the operation of the heating module and the vibration motor during infusion or blood transfusion. It receives the heating temperature of the heating pipe obtained by the heating module within a preset cycle. If the heating temperature does not reach the preset temperature range, it adjusts the heating temperature of the heating module until the heating temperature reaches the preset temperature range.

[0011] Optionally, the wall thickness of the heating tube body is 0.5mm-1.5mm, the length is 50cm-150cm, and the inner diameter is 2mm-5mm.

[0012] Optionally, the heating module includes a heating element and a temperature sensor; the vibration motor is fixedly connected to the heating element;

[0013] The heating element is located on the outer wall of the heating tube body and is used to heat the heating tube body; the temperature sensor is located at the bottom of the outer wall of the heating tube body and is used to obtain the heating temperature of the heating tube body.

[0014] Optionally, the heating element may be made of a PTC heating element or a nylon film heating element; the temperature sensor may be made of a platinum resistance thermometer or an NTC thermistor.

[0015] Optionally, the blood transfusion and infusion heating tube also includes a pressure sensor; the pressure sensor is located on the outer wall of the heating tube body and is used to detect the liquid pressure inside the heating tube.

[0016] The controller is also electrically connected to a pressure sensor to receive liquid pressure and reduce the heating power of the heating module when the liquid pressure exceeds a preset pressure threshold.

[0017] Optionally, the rated power of the vibration motor is 1W-5W, the speed is 1000rpm-5000rpm, the vibration frequency is 50Hz-200Hz, and the vibration amplitude is 0.1mm-0.5mm.

[0018] Optionally, the blood transfusion and infusion heating tube also includes an isolation module; the isolation module includes multiple isolation parts formed by hot-melt welding between the front and back of the heating tube body to divide the heating channel into a non-linear tortuous flow path;

[0019] An isolation section is located within the vibration coverage area of ​​the vibrating motor to assist the bubbles in detaching and rising under the vibration action of the vibrating motor.

[0020] Optionally, the distance between two adjacent isolation sections is 10mm-30mm; the shape of the heating pipe includes at least S-shape or mesh shape.

[0021] Secondly, the present invention provides a temperature control method for a blood transfusion and infusion heating tube, comprising:

[0022] During intravenous or blood transfusion, the heating module and vibration motor are controlled to operate, and the heating temperature of the heating pipe is received by the heating module within a preset cycle.

[0023] If the heating temperature does not reach the preset temperature range, adjust the heating temperature of the heating module until the heating temperature reaches the preset temperature range.

[0024] Optionally, when the heating temperature does not reach the preset temperature range, the heating temperature of the heating module is adjusted, including:

[0025] When the heating temperature does not reach the preset temperature range, the heating temperature adjustment amount is determined based on the heating temperature and the first calculation formula; the first calculation formula is: Where u is the heating temperature adjustment amount, T is the preset period (0.1s ≤ T ≤ 0.5s), Kp is the proportional coefficient, Ki is the integral coefficient, Kd is the differential coefficient, and Kp, Ki, and Kd are all preset constants. 11 e represents the temperature difference between the current heating temperature and the target temperature. 21 This is the temperature difference between the heating temperature obtained from the last sampling and the target temperature.

[0026] Adjust the heating temperature of the heating module to the set heating temperature based on the heating temperature adjustment amount;

[0027] And / or, the operating modes of the vibration motor include blood transfusion mode and infusion mode;

[0028] The method also includes:

[0029] In transfusion mode, increase the vibration intensity of the vibration motor;

[0030] In infusion mode, reduce the vibration intensity of the vibration motor.

[0031] The technical solution of this invention involves electrically connecting a controller to both a heating module and a vibration motor. During infusion or blood transfusion, the controller simultaneously activates and controls both the heating module and the vibration motor. The heating module heats the outer wall of the heating tube, and the heat is conducted through the tube wall to the blood or liquid flowing inside the heating tube. Simultaneously, the controller acquires the heating temperature of the heating tube in real time. The controller compares the heating temperature received within a preset period with a preset temperature range. If the temperature does not reach the preset range, the heating power of the heating module is adjusted to regulate the temperature of the heating tube, forming a closed-loop temperature control until the heating temperature stabilizes within the preset range. Simultaneously, the vibration motor generates high-frequency micro-amplitude vibrations, which are transmitted to the heating tube through the heating module. This creates micro-disturbances on the tube wall and the liquid inside, causing tiny air bubbles generated during infusion or blood transfusion to detach from the tube wall and converge upwards at the top of the infusion chamber, preventing these bubbles from flowing downstream into the patient's body. Utilizing the above structure, through the synergistic operation of two major functions—temperature control closed-loop regulation and vibration active defoaming—it continuously and automatically eliminates tiny air bubbles while ensuring that the output liquid temperature is suitable for the human body. This solves the dual technical problems of cold stimulation to patients caused by low-temperature liquids and the inability to actively remove air bubbles during the heating process, which can easily lead to air embolism. This improves the safety and reliability of the infusion or blood transfusion process, and the structure is simple.

[0032] It should be understood that the description in this section is not intended to identify key or essential features of the embodiments of the present invention, nor is it intended to limit the scope of the invention. Other features of the invention will become readily apparent from the following description. Attached Figure Description

[0033] To more clearly illustrate the technical solutions in the embodiments of the present invention, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0034] Figure 1 This is a schematic diagram of the structure of a blood transfusion and infusion heating tube provided in an embodiment of the present invention;

[0035] Figure 2 This is a schematic diagram of another blood transfusion and infusion heating tube provided in an embodiment of the present invention;

[0036] Figure 3 A flowchart illustrating a temperature control method for a blood transfusion and infusion heating tube provided in an embodiment of the present invention;

[0037] Figure 4 A flowchart of another temperature control method for a blood transfusion and infusion heating tube provided in an embodiment of the present invention. Detailed Implementation

[0038] To enable those skilled in the art to better understand the present invention, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of the present invention.

[0039] It should be noted that the terms "first," "second," etc., in the specification, claims, and accompanying drawings of this invention are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments of the invention described herein can be implemented in orders other than those illustrated or described herein. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover non-exclusive inclusion; for example, a process, method, system, product, or apparatus that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to such processes, methods, products, or apparatus.

[0040] In one embodiment, Figure 1 This is a schematic diagram of a blood transfusion / infusion heating tube provided in an embodiment of the present invention. This embodiment is applicable to situations where effective temperature control is achieved, effectively eliminating air bubbles generated in the liquid, reducing the risk of gas embolism, and improving the safety and reliability of the infusion or blood transfusion process. Figure 1 As shown, the blood transfusion and infusion heating tube includes: a heating tube body 10, a heating module 20, a vibration motor 30, and a controller 40; the heating tube body 10 includes a heating pipe for transmitting blood or liquid; the heating module 20 is located on the outer wall of the heating tube body 10 and is used to heat the heating tube body 10 and obtain the heating temperature of the heating pipe during the heating process; the vibration motor 30 is fixed inside the heating tube body 10 and is fixedly connected to the heating module 20, and is used to drive the heating module 20 to vibrate synchronously during vibration, so that the air bubbles generated by blood transfusion or infusion gather in the infusion chamber; the controller 40 is electrically connected to the heating module 20 and the vibration motor 30 respectively, and is used to control the operation of the heating module 20 and the vibration motor 30 during infusion or blood transfusion, and to receive the heating temperature of the heating pipe obtained by the heating module 20 within a preset period, and to adjust the heating temperature of the heating module 20 when the heating temperature does not reach the preset temperature range until the heating temperature reaches the preset temperature range.

[0041] The heating tube body 10 is a hollow tubular structure made of high-temperature resistant plastic. The interior is a heating pipe, with bottle stopper plugs and external conical connectors at both ends. It serves as a fluid channel for infusion / transfusion, simultaneously acting as a heat transfer medium and a vibration conduction medium. During actual infusion or transfusion, the bottle stopper plug at the top of the heating tube body 10 is used to insert into and pierce the stopper of the medication bottle or blood bag, forming a sealed inlet passage. The external conical connector (i.e., a standard Luer connector) at the bottom of the heating tube body 10 forms a conical seal with the inner conical connector of the subsequent infusion set or intravenous catheter, thus enabling a detachable connection between the heating tube and the patient's infusion line. The heating module 20 is a component located on the outer wall of the heating tube body 10, responsible for generating heat to heat the liquid inside the tube, while simultaneously monitoring the temperature of the heating pipe in real time and feeding it back to the controller 40. The vibration motor 30 is a miniature motor (such as a DC motor or stepper motor) fixed inside the heating pipe body 10. Through a transmission connection with the heating module 20, it generates high-frequency, low-amplitude vibrations, causing the heating module 20 to vibrate synchronously. This transfers vibration energy to the liquid inside the heating pipe, causing bubbles to detach from the pipe wall and converge upwards. The controller 40 is an electronic control unit (using a PID control algorithm) electrically connected to both the heating module 20 and the vibration motor 30. It serves as the core control hub, simultaneously controlling the start / stop and parameter adjustment of both heating and vibration functions, achieving coordinated management of temperature control and defoaming. The preset temperature range is a pre-defined target temperature interval (e.g., 36.5℃-37.5℃) serving as a reference for closed-loop control, ensuring that the output liquid temperature meets the requirements for human infusion.

[0042] Specifically, by electrically connecting the controller 40 to the heating module 20 and the vibration motor 30 respectively, the controller 40 simultaneously starts and controls the operation of the heating module 20 and the vibration motor 30 during infusion or blood transfusion. After the heating module 20 starts working, it heats the outer wall of the heating tube body 10. The heat is conducted through the tube wall to the blood or liquid flowing inside the heating tube. At the same time, the heating module 20 acquires the heating temperature of the heating tube in real time and periodically feeds it back to the controller 40. The controller 40 compares the heating temperature of the heating tube received within a preset period with a preset temperature range. If the temperature does not reach the preset temperature range (e.g., higher than the highest temperature in the preset temperature range or lower than the lowest temperature in the preset temperature range), the controller adjusts the heating power of the heating module 20 through a PID algorithm, thereby regulating the temperature of the heating tube in the heating tube body 10, forming a closed-loop temperature control until the heating temperature stabilizes within the preset temperature range. Meanwhile, after the vibration motor 30 starts working, it generates high-frequency micro-amplitude vibrations. Since it is fixedly connected to the heating module 20, the micro-amplitude vibrations generated by the vibration motor 30 are directly transmitted to the heating module 20. The heating module 20 is located on the outer wall of the heating tube body 10, so the vibration is transmitted to the heating tube body 10, thereby causing micro-disturbances to the tube wall and the liquid inside the tube. This causes tiny bubbles generated during infusion or blood transfusion to detach from the tube wall and converge upwards to the top of the infusion chamber (such as a Murphy drip tube), preventing bubbles from flowing downstream into the patient's body with the liquid. Thus, this application, through the synergistic operation of closed-loop temperature control and active defoaming via vibration, ensures that the output liquid temperature is suitable for the human body while continuously and automatically eliminating tiny bubbles. It also solves the dual technical problems of cold stimulation to patients caused by low-temperature liquids and the inability to actively remove bubbles during heating, which can easily lead to air embolism.

[0043] The technical solution of this invention involves electrically connecting a controller to both a heating module and a vibration motor. During infusion or blood transfusion, the controller simultaneously activates and controls both the heating module and the vibration motor. The heating module heats the outer wall of the heating tube, and the heat is conducted through the tube wall to the blood or liquid flowing inside the heating tube. Simultaneously, the controller acquires the heating temperature of the heating tube in real time. The controller compares the heating temperature received within a preset period with a preset temperature range. If the temperature does not reach the preset range, the heating power of the heating module is adjusted to regulate the temperature of the heating tube, forming a closed-loop temperature control until the heating temperature stabilizes within the preset range. Simultaneously, the vibration motor generates high-frequency micro-amplitude vibrations, which are transmitted to the heating tube through the heating module. This creates micro-disturbances on the tube wall and the liquid inside, causing tiny air bubbles generated during infusion or blood transfusion to detach from the tube wall and converge upwards at the top of the infusion chamber, preventing these bubbles from flowing downstream into the patient's body. Utilizing the above structure, through the synergistic operation of two major functions—temperature control closed-loop regulation and vibration active defoaming—it continuously and automatically eliminates tiny air bubbles while ensuring that the output liquid temperature is suitable for the human body. This solves the dual technical problems of cold stimulation to patients caused by low-temperature liquids and the inability to actively remove air bubbles during the heating process, which can easily lead to air embolism. This improves the safety and reliability of the infusion or blood transfusion process, and the structure is simple.

[0044] Optional, continue to refer to Figure 1 The wall thickness of the heating tube body 10 is 0.5mm-1.5mm, the length is 50cm-150cm, and the inner diameter is 2mm-5mm.

[0045] Specifically, in this embodiment, the wall thickness of the heating tube body 10 is set to 0.5mm-1.5mm. For example, the wall thickness of the heating tube body 10 can be 0.5mm, 0.8mm, 1.0mm, 1.2mm, 1.3mm, or 1.5mm, etc., which can be determined according to actual parameters and are not limited here. By setting the wall thickness of the heating tube body 10, a balance is achieved between heat transfer efficiency and structural strength. In other words, setting the wall thickness to be greater than or equal to 0.5mm ensures that the tube wall has low thermal inertia, so that the heat generated by the heating module 20 can be quickly transferred to the liquid inside the tube, achieving rapid thermal response and precise temperature control; less than or equal to 1.5mm ensures that the heating tube body 10 has sufficient mechanical strength to withstand the positive pressure generated by the infusion pump and the continuous micro-vibration transmitted by the vibration motor 30, preventing the tube wall from cracking or deforming, thereby balancing heating speed and reliability.

[0046] Furthermore, in this embodiment, the length of the heating tube body 10 is set to 50cm-150cm. For example, the length of the heating tube body 10 can be 50cm, 70cm, 80cm, 100cm, 120cm, 130cm, or 150cm, etc., and can be determined according to actual parameters, without limitation. By setting the length of the heating tube body 10, this length range ensures sufficient heating effect at different infusion rates, while also taking into account the convenience of clinical operation. In other words, a length greater than or equal to 50cm provides sufficient heating path length at higher flow rates (such as rapid blood transfusion), ensuring that the liquid is heated to the target temperature before leaving the heating tube body 10; a length less than or equal to 150cm avoids excessive pressure loss and inconvenient tubing management caused by excessively long tubing, while also being compatible with the length of conventional infusion sets, facilitating operation by medical personnel.

[0047] Furthermore, in this embodiment, the inner diameter of the heating tube body 10 is set to 2mm-5mm. For example, the inner diameter of the heating tube body 10 can be 2mm, 2.5mm, 3mm, 3.5mm, 4mm, 4.5mm, or 5mm, etc., and can be determined according to actual parameters, without limitation. By setting the inner diameter of the heating tube body 10, this inner diameter range achieves an optimal match between heating efficiency, flow resistance, and defoaming effect. In other words, setting the lower limit of 2mm increases the ratio of contact area to volume between the liquid and the tube wall, improving heat exchange efficiency, while facilitating the concentration of vibration energy on the central region of the liquid, promoting the detachment of microbubbles from the tube wall and their upward convergence; the upper limit of 5mm avoids excessive flow resistance caused by an excessively small tube diameter and the risk of blockage when infusing viscous blood products, while providing sufficient space for bubbles to float.

[0048] Optional, Figure 2 This is a schematic diagram of another blood transfusion and infusion warming tube provided in an embodiment of the present invention, with reference to... Figure 2 As shown, the heating module 20 includes a heating element 21 and a temperature sensor 22; the vibration motor 30 is fixedly connected to the heating element 21; the heating element 21 is located on the outer wall of the heating tube body 10 and is used to heat the heating tube body 10; the temperature sensor 22 is located at the bottom of the outer wall of the heating tube body 10 and is used to obtain the heating temperature of the heating tube body 10.

[0049] The heating element 21 is a thin sheet-like heating element made of PTC heating element or nylon film heating element, which is attached to the outer wall of the heating tube body 10 to serve as a heat source, converting electrical energy into heat energy, which is conducted inward through the tube wall to heat the blood or liquid flowing inside the tube. The temperature sensor 22 is a temperature measuring element made of platinum resistance thermometer or NTC thermistor, located at the bottom of the outer wall of the heating tube body 10, used to detect the temperature at the bottom of the outer wall of the heating tube body 10 in real time (indirectly reflecting the temperature of the liquid inside the tube), and converting the temperature signal into an electrical signal to feed back to the controller 40. In this embodiment, the vibration motor 30 and the heating element 21 are rigidly connected (such as by gear transmission, screw fixing or integral molding) to ensure efficient transmission of vibration energy, so that the heating element 21 and the vibration motor 30 form a vibration community and avoid energy loss.

[0050] Specifically, during intravenous infusion or blood transfusion, the controller 40 simultaneously activates the heating element 21 and the vibration motor 30. The heating element 21, attached to the outer wall of the heating tube body 10, generates heat when energized. This heat is conducted through the tube wall to the flowing blood or fluid, thus warming the infused fluid. A temperature sensor 22, located at the bottom of the outer wall of the heating tube body 10, acquires the heating temperature of the heating tube body 10 in real time and periodically feeds the temperature signal back to the controller 40. The controller 40, based on the difference between the received current temperature of the heating tube body 10 and a preset temperature range, uses a PID algorithm to adjust the heating power of the heating element 21 in a closed-loop manner until the temperature stabilizes within the target range. Meanwhile, since the vibration motor 30 is fixedly connected to the heating element 21, the high-frequency micro-amplitude vibration generated by the vibration motor 30 during operation is directly transmitted to the heating element 21, thereby driving the heating tube body 10 to vibrate synchronously. This causes micro-disturbances in the tube wall and the liquid inside the tube, thereby causing tiny air bubbles generated during infusion or blood transfusion to detach from the tube wall and converge upwards to the top of the infusion chamber (such as a Murphy drip tube), preventing air bubbles from flowing downstream into the patient's body with the liquid. Thus, this embodiment, through the closed-loop temperature control system composed of the heating element 21 and the temperature sensor 22, and the vibration transmission path achieved by the fixed connection between the vibration motor 30 and the heating element 21, ensures that the output liquid temperature is suitable for the human body while continuously and automatically eliminating tiny air bubbles. This solves the technical problems of cold stimulation to patients caused by low-temperature liquids and the formation of air embolisms due to the inability to actively remove air bubbles during heating.

[0051] Optional, continue to refer to Figure 2 As shown, the heating element 21 is made of a PTC heating element or a nylon film heating element; the temperature sensor 22 is made of a platinum resistance thermometer or an NTC thermistor.

[0052] Among them, PTC (Positive Temperature Coefficient) heating elements are ceramic or polymer heating materials with self-limiting temperature characteristics. Their resistance increases sharply with temperature; when the temperature exceeds the Curie point, the resistance automatically increases, and the heating power automatically decreases, achieving self-limiting temperature control. This prevents overheating without the need for an additional temperature control switch, improving safety. Nylon film heating elements are flexible, thin-film heating elements formed by printing conductive ink or metal foil onto a nylon film substrate. They are ultra-thin, flexible, and bendable, allowing them to closely conform to the curved surface of the heating tube body, achieving uniform heating and a fast thermal response. Platinum resistance thermometers are temperature sensors that use high-purity platinum wire as the sensing element. Their resistance value changes stably and linearly with temperature increases, exhibiting high precision, high stability, and good linearity. They are suitable for medical applications with high temperature control requirements, providing accurate and reliable temperature feedback. NTC (Negative Temperature Coefficient) thermistors are semiconductor temperature-sensing elements made of sintered metal oxides. Their resistance decreases as the temperature increases, and they are characterized by high sensitivity, fast response, and low cost. They can quickly sense temperature changes and are suitable for dynamic temperature control scenarios with high response speed requirements.

[0053] Optional, continue to refer to Figure 2 The blood transfusion and infusion heating tube also includes a pressure sensor 50; the pressure sensor 50 is located on the outer wall of the heating tube body 10 and is used to detect the liquid pressure in the heating tube; the controller 40 is also electrically connected to the pressure sensor 50 to receive the liquid pressure and reduce the heating power of the heating module 20 when the liquid pressure exceeds the preset pressure threshold.

[0054] Among them, the pressure sensor 50 is a pressure-sensing element (such as a thin-film pressure sensor, MEMS pressure sensor or piezoresistive sensor, etc.) installed on the outer wall of the heating pipe body 10. It indirectly measures the pressure of the liquid in the heating pipe by detecting the slight deformation of the pipe wall, and monitors the changes in the liquid pressure in the heating pipe in real time, reflecting the abnormal flow rate, pipeline blockage or excessive pump pressure during the infusion / blood transfusion process.

[0055] Specifically, during intravenous infusion or blood transfusion, in addition to detecting the temperature of the heating tube body 10, a pressure sensor 50 installed on the outer wall of the heating tube body 10 also detects the pressure of the liquid inside the heating pipe in real time and transmits the pressure signal to the controller 40. The controller 40 compares the received current liquid pressure with a preset pressure threshold. When the detected liquid pressure exceeds the preset pressure threshold, such as due to pipe bends, blockages, infusion pump malfunctions, or excessively fast infusion rate, the controller 40 immediately and automatically reduces the heating power of the heating module 20, causing the heating temperature to drop. The technical logic is as follows: under normal infusion flow rate, the liquid flow can carry away heat, maintaining a stable temperature difference between the tube wall and the liquid; however, when the pressure increases, it means that the flow rate decreases or the pipe is blocked, and the residence time of the liquid per unit volume in the heating pipe is prolonged. If the heating power remains unchanged, the liquid is easily overheated, causing dissolved gases to precipitate and form microbubbles, and even triggering protein denaturation and the risk of gas embolism. By monitoring the pressure with pressure sensor 50 and reducing the heating power accordingly, adaptive adjustment is achieved. When the pipeline is blocked or the flow rate is abnormal, the heat input is actively reduced, suppressing the conditions for bubble formation from the source. At the same time, it avoids the liquid from overheating and causing harm to the patient, further improving the safety of the blood transfusion or infusion warming process.

[0056] Optional, continue to refer to Figure 2 The rated power of the vibration motor 30 is 1W-5W, the speed is 1000rpm-5000rpm, the vibration frequency is 50Hz-200Hz, and the vibration amplitude is 0.1mm-0.5mm.

[0057] In this embodiment, the rated power of the vibration motor 30 is set to 1W-5W. For example, the rated power can be 1W, 2W, 3W, 4W, or 5W, etc., and can be determined according to the actual situation, without limitation. This rated power range achieves an optimal balance between vibration energy output and energy consumption control. Specifically, setting the lower limit of 1W ensures that the vibration motor can generate sufficient mechanical vibration energy to overcome the damping of the pipe wall and the viscous resistance of the liquid, so that the vibration is effectively transmitted to the liquid in the heated pipe, causing microbubbles to detach from the pipe wall; the upper limit of 5W avoids excessive power input, which would cause the motor to generate too much heat, and prevents heat from being transferred to the heating module 20 through the fixed connection and interfering with the detection accuracy of the temperature sensor 22. At the same time, it reduces the overall power consumption, so that the product can be powered by a battery or integrated into a portable device to meet the needs of multiple clinical scenarios.

[0058] Furthermore, the vibration motor 30 operates at a speed of 1000 rpm to 5000 rpm. For example, speeds of 1000 rpm, 2000 rpm, 3000 rpm, 4000 rpm, or 5000 rpm can be determined based on actual conditions and are not limited here. This speed range ensures that the vibration motor can generate vibration characteristics suitable for medical defoaming scenarios. Specifically, setting a lower limit of 1000 rpm keeps the motor's output vibration frequency in the low-frequency range, facilitating a boost to an effective defoaming frequency above 50 Hz, while avoiding insufficient vibration energy due to excessively low speed. The upper limit of 5000 rpm controls the mechanical wear and noise level of the vibration motor 30, preventing unpleasant high-frequency noise or excessive mechanical wear from excessively high speeds, thus achieving a balance between defoaming effect, service life, and patient comfort.

[0059] Furthermore, the vibration frequency of the vibration motor 30 is 50Hz-200Hz. For example, the vibration frequency can be 50Hz, 80Hz, 120Hz, 150Hz, or 200Hz, etc., and the specific frequency can be determined according to the actual situation, without limitation here. This frequency range is optimized for the detachment and aggregation characteristics of microbubbles in the liquid. The lower limit of 50Hz can generate sufficient periodic acceleration, causing microbubbles attached to the tube wall to detach from the wall surface due to inertial force, while avoiding significant disturbance to the infusion flow rate caused by low-frequency vibration. The upper limit of 200Hz ensures that the vibration frequency is not too high and will cause the skin effect, while being controlled within the range of human hearing without being too harsh. Testing has shown that this frequency range has the best vibration transmission efficiency for conventional infusion tubing materials (such as PVC, PU, ​​or silicone), achieving efficient defoaming without interfering with the normal working environment of medical personnel.

[0060] Furthermore, the vibration amplitude of the vibration motor 30 is 0.1mm-0.5mm. For example, the vibration amplitude can be 0.1mm, 0.2mm, 0.3mm, 0.4mm, or 0.5mm, etc., which can be determined according to the actual situation and are not limited here. This amplitude range achieves a reasonable balance between vibration energy transmission and pipeline safety. Specifically, setting a lower limit of 0.1mm ensures that the vibration displacement is sufficient to break the surface tension between the bubbles and the pipe wall, causing the microbubbles to detach from the wall and converge upwards, while avoiding an amplitude that is too small, resulting in an insignificant defoaming effect; the upper limit of 0.5mm ensures that the vibration amplitude will not cause fatigue damage to the structural integrity of the heating tube body, preventing the pipe wall from developing microcracks or loosening of joints due to long-term large-amplitude vibration, and also avoiding excessive vibration transmission to the patient end, causing discomfort.

[0061] Optional, continue to refer to Figure 2The blood transfusion and infusion heating tube also includes an isolation module (not shown in the figure); the isolation module includes multiple isolation parts (not shown in the figure) formed by hot-melt welding between the front and back sides of the heating tube body 10 to divide the heating channel into a non-linear tortuous flow channel; the isolation parts are disposed in the vibration coverage area of ​​the vibration motor 30 to assist the bubbles to detach and float under the vibration action of the vibration motor 30.

[0062] The isolation module is an integral structure comprising multiple isolation sections, located inside the cavity of the heating tube body 10. It achieves physical defoaming by altering the flow channel geometry. As a passive defoaming mechanism, it works in conjunction with the active vibration of the vibration motor 30 to efficiently remove, intercept, and float bubbles. The isolation section is a protrusion or connection point formed by pressing and fusing the front and back walls of the heating tube body 10 together at local locations using a hot-melt welding process. Its shape can be circular or rectangular. It forms a physical obstacle within the cavity, dividing the originally straight heating channel into a curved, meandering, non-linear flow path, increasing the liquid flow path length and turbulence.

[0063] Specifically, during the manufacturing process of the heating tube body 10, multiple isolation sections are formed inside the tube cavity through a hot melt welding process. These isolation sections divide the originally straight and unobstructed heating channel into S-shaped, wavy, or mesh-shaped non-linear tortuous flow channels. At the same time, these isolation sections are arranged within the vibration coverage area of ​​the vibration motor 30, that is, the 50Hz-200Hz high-frequency micro-amplitude vibration generated by the vibration motor 30 can be effectively transmitted to the location of the isolation section. During operation, when the liquid flows through the tortuous flow channel, the tortuous structure produces the following three effects: First, it prolongs the flow path of the liquid in the fixed-length heating pipe (which can be 1.5-3 times longer than that of a straight pipe), increasing the contact area and heat exchange time between the liquid and the heated pipe wall, thus improving heating efficiency. Second, the isolation section acts as a physical barrier, intercepting and blocking the tiny bubbles flowing with the liquid, causing the bubbles to linger, converge, and float to the top of the infusion chamber upstream of the isolation section. Third, since the isolation section is located within the vibration coverage area, the continuous vibration of the vibration motor 30 causes slight deformation and disturbance to the isolation section and the surrounding pipe wall. This vibration-assisted effect can effectively break the adhesion between the bubbles and the surface of the isolation section, causing the intercepted bubbles to detach further and float upward, rather than accumulating on the surface of the isolation section to form a gas film that hinders the flow of liquid. Thus, through the synergistic effect of passive physical interception (isolation section) and active vibration-assisted desorption (vibration motor), efficient capture and removal of microbubbles are achieved. This overcomes the defect that bubbles may bypass the vibration node when relying solely on vibration, and also makes up for the deficiency that bubbles are prone to adhering to the interception structure when relying solely on physical isolation. Under the premise of ensuring normal liquid flow, a more thorough bubble elimination effect is achieved.

[0064] Optional, continue to refer toFigure 2 The distance between two adjacent isolation sections is 10mm-30mm. For example, the distance can be 10mm, 15mm, 20mm, 25mm, or 30mm, and the specific distance can be determined according to the actual situation; no limitation is imposed here. This setting can achieve an air bubble interception rate of over 90%, while controlling the pressure loss within 0.05MPa. It does not affect conventional gravity infusion and does not require additional power to the infusion pump, achieving a balance between efficient defoaming and clinical ease of use.

[0065] Based on the same inventive concept Figure 3 A flowchart illustrating a temperature control method for a blood transfusion / infusion warming tube provided in an embodiment of the present invention is shown below. Figure 3 As shown, the method includes:

[0066] S110: Control the operation of the heating module and vibration motor during infusion or blood transfusion, and receive the heating temperature of the heating pipeline obtained by the heating module within a preset cycle.

[0067] Specifically, this step essentially enables the simultaneous activation of heating and defoaming functions, as well as real-time temperature data acquisition. When infusion or blood transfusion begins, the controller simultaneously sends operating commands to the heating module and the vibration motor. The heating module begins heating the heating tube, while the vibration motor generates high-frequency micro-vibrations. This ensures that heating and defoaming functions operate in parallel from the start of the infusion, avoiding a time lag or defoaming gap. Simultaneously, the controller periodically reads the heating temperature of the heating pipe from the temperature sensor according to a preset sampling period (e.g., period T is 0.1s-0.5s). This periodic sampling mechanism ensures that the controller can fully grasp the dynamic temperature changes within the heating pipe, providing continuous and accurate temperature data input for subsequent closed-loop regulation and preventing the loss of critical temperature overshoot or undershoot due to excessively long sampling intervals.

[0068] S120. When the heating temperature does not reach the preset temperature range, adjust the heating temperature of the heating module until the heating temperature reaches the preset temperature range.

[0069] Specifically, this step essentially constitutes the core adjustment mechanism of closed-loop temperature control. The controller compares the current heating temperature with the preset target temperature range (i.e., the preset temperature range). If the current temperature is lower than the lower limit of the preset temperature range, the heating temperature is increased by increasing the output power of the heating module (e.g., increasing the PWM duty cycle or increasing the heating current). If the current temperature is higher than the upper limit of the preset temperature range, the heating temperature is reduced by decreasing the output power of the heating module or even temporarily shutting off heating. This adjustment process continues until the heating temperature stabilizes within the preset temperature range. This closed-loop adjustment mechanism uses a PID control algorithm, combining proportional (P), integral (I), and derivative (D) operations. The proportional stage responds quickly based on the current temperature difference, the integral stage eliminates steady-state errors, and the derivative stage predicts temperature change trends and suppresses overshoot. The synergistic effect of these three components ensures that the liquid temperature in the heating pipeline can be maintained quickly, stably, and accurately within the preset range, thereby providing patients with appropriately sized fluids throughout the infusion or blood transfusion process and avoiding low-temperature cold stimulation or overheating damage.

[0070] The technical solution of this invention controls the operation of a heating module and a vibration motor during intravenous infusion or blood transfusion, and receives the heating temperature of the heated pipeline acquired by the heating module within a preset period. If the heating temperature does not reach the preset temperature range, the heating temperature of the heating module is adjusted until the heating temperature reaches the preset temperature range. Using the above method, precise temperature control and active defoaming are achieved synergistically during intravenous infusion or blood transfusion, avoiding cold stimulation to the patient caused by low-temperature liquids and effectively eliminating microbubbles generated during heating, significantly reducing the risk of air embolism and improving the safety and patient comfort of clinical intravenous infusion or blood transfusion.

[0071] In another specific embodiment, Figure 4 This is a flowchart of another temperature control method for a blood transfusion and infusion heating tube provided by an embodiment of the present invention. This embodiment refines the specific implementation of S120 in the above embodiment, where the heating temperature is adjusted when the heating temperature has not reached the preset temperature range, as follows:

[0072] When the heating temperature does not reach the preset temperature range, the heating temperature adjustment amount is determined based on the heating temperature and the first calculation formula; the first calculation formula is: Where u is the heating temperature adjustment amount, T is the preset period (0.1s ≤ T ≤ 0.5s), Kp is the proportional coefficient, Ki is the integral coefficient, Kd is the differential coefficient, and Kp, Ki, and Kd are all preset constants. 11 e represents the temperature difference between the current heating temperature and the target temperature. 21 This is the temperature difference between the heating temperature obtained from the last sampling and the target temperature.

[0073] Adjust the heating temperature of the heating module to the set heating temperature based on the heating temperature adjustment amount;

[0074] Furthermore, in step S120, after adjusting the heating temperature of the heating module when the heating temperature has not reached the preset temperature range, the following steps are added:

[0075] In transfusion mode, increase the vibration intensity of the vibration motor;

[0076] In infusion mode, reduce the vibration intensity of the vibration motor.

[0077] For details not covered in this embodiment, please refer to the above embodiments, which will not be repeated here.

[0078] refer to Figure 4 As shown, the method includes:

[0079] S210: Control the operation of the heating module and vibration motor during infusion or blood transfusion, and receive the heating temperature of the heating pipeline obtained by the heating module within a preset cycle.

[0080] The vibration motor has two operating modes: blood transfusion mode and intravenous infusion mode.

[0081] S220. When the heating temperature does not reach the preset temperature range, determine the heating temperature adjustment amount based on the heating temperature and the first calculation formula.

[0082] The first calculation formula is: Where u is the heating temperature adjustment amount, T is the preset period (0.1s ≤ T ≤ 0.5s), Kp is the proportional coefficient, Ki is the integral coefficient, Kd is the differential coefficient, and Kp, Ki, and Kd are all preset constants. 11 e represents the temperature difference between the current heating temperature and the target temperature. 21 This is the temperature difference between the heating temperature obtained from the previous sampling and the target temperature.

[0083] Specifically, this step essentially involves quantitatively calculating the adjustment range of heating power (i.e., the adjustment amount of heating temperature), which is the core computational step of PID closed-loop control. When the controller determines that the current heating temperature has not reached the preset temperature range, it calculates the difference e between the currently sampled heating temperature and the target temperature. 11 (i.e., the current temperature difference) and the difference e between the heating temperature and the target temperature obtained from the last periodic sampling. 21 Substituting (i.e., the previous temperature difference) into the first calculation formula In this process, by combining three preset constants—the proportional coefficient Kp, the integral coefficient Ki, and the differential coefficient Kd—and a preset period T, the heating temperature adjustment amount u can be calculated. Specifically, Kp×e11 represents the adjustment amount determined by the current temperature difference proportionality formula; the larger the temperature difference, the larger the adjustment amount, achieving rapid response. Ki×e21 represents the elimination of system steady-state error based on the cumulative effect of historical temperature differences, ensuring that the final temperature accurately converges to the target value. The Kd×(e11-e21) / T term predicts the temperature change trend based on the rate of change of the temperature difference, reducing the adjustment amount in advance when the temperature rises rapidly to prevent overshoot. The heating temperature adjustment amount u obtained by the weighted sum of these three terms provides a precise numerical basis for the subsequent power adjustment.

[0084] It should be noted that the first calculation formula can differ in actual use when the preset period T is different. Specifically, each coefficient will be different, and these coefficients can be set in advance to determine the temperature rise time and stabilization time. For example, when T=0.2s, the first calculation formula can be: .

[0085] At T=0.3s, the first calculation formula can be expressed as: .

[0086] S230. Adjust the heating temperature of the heating module to the heating temperature adjustment amount according to the heating temperature adjustment amount.

[0087] Specifically, this step essentially transforms the theoretically calculated heating temperature adjustment amount into actual power output changes. The controller converts the calculated heating temperature adjustment amount *u* into a corresponding control signal (such as adjusting the duty cycle of a PWM wave or adjusting the magnitude of the heating current), driving the heating module to increase or decrease its heating power according to this adjustment amount. For example, when *u* is positive, the controller increases the output power of the heating module to raise the temperature; when *u* is negative, the controller decreases the output power to lower the temperature. This adjustment process is repeatedly executed at sampling period T, ensuring that the heating temperature approaches the target temperature in each cycle. Ultimately, through multiple iterations, it converges to the preset temperature range, achieving precise and stable control of the liquid temperature within the heating pipe.

[0088] S240. In blood transfusion mode, increase the vibration intensity of the vibration motor.

[0089] Specifically, this step provides a differentiated defoaming strategy tailored to the unique physical properties of blood products. Compared to ordinary medication solutions, blood products have higher viscosity (approximately 3-4 times that of saline) and more complex components (such as red blood cells, white blood cells, and platelets). Tiny air bubbles rise at a significantly slower rate in viscous liquids, and are more easily encapsulated by blood cells, making them more difficult to detach from the tube wall. Therefore, when a transfusion mode is determined, the controller increases the vibration intensity of the vibration motor (e.g., increasing the vibration frequency from 100Hz to 150Hz-200Hz, or increasing the PWM duty cycle to increase the amplitude). This stronger mechanical vibration energy overcomes the high viscosity resistance of blood, effectively disrupting the adhesion between air bubbles and the tube wall and blood cells, causing the bubbles to detach and converge upwards. This ensures that tiny air bubbles are promptly removed during the transfusion process, preventing air embolisms from entering the patient's circulatory system.

[0090] S250. In infusion mode, reduce the vibration intensity of the vibration motor.

[0091] Specifically, this step provides an optimized energy-saving defoaming strategy based on the low viscosity of common intravenous solutions. Compared to blood, routine intravenous infusions such as saline, glucose solutions, and antibiotics have lower viscosity (close to the viscosity of water). Tiny air bubbles in these solutions experience less resistance to rising and are more easily detached from the tubing wall and aggregate upwards. Therefore, when the current infusion mode is determined to be normal, the controller appropriately reduces the vibration intensity of the vibration motor (e.g., reducing the vibration frequency to 50Hz-100Hz or reducing the amplitude) to achieve a satisfactory defoaming effect with lower vibration energy. The benefits of this are: firstly, reduced overall power consumption, extending the operating time of battery-powered equipment; secondly, reduced fatigue wear on the heating tube body due to unnecessary mechanical vibration; and thirdly, prevention of discomfort caused by excessive vibration transmitted to the patient.

[0092] The technical solution of this invention determines the heating temperature adjustment amount based on the heating temperature and a first calculation formula when the heating temperature does not reach the preset temperature range; adjusts the heating temperature of the heating module to the adjusted amount according to the heating temperature adjustment amount; increases the vibration intensity of the vibration motor in blood transfusion mode; and decreases the vibration intensity of the vibration motor in infusion mode. Using the above method, the heating temperature adjustment amount is quantitatively calculated using a PID algorithm and closed-loop regulation is executed, achieving precise control of the liquid temperature in the heating pipeline. Simultaneously, the vibration intensity is differentiated according to the blood transfusion and infusion modes, matching strong vibration to high-viscosity blood to overcome bubble detachment resistance, and matching weak vibration to low-viscosity conventional drug solutions to reduce energy consumption and mechanical losses. This achieves a balance between temperature control accuracy, energy management, and clinical adaptability while ensuring defoaming effects.

[0093] It should be understood that the various forms of processes shown above can be used, with steps reordered, added, or deleted. For example, the steps described in this invention can be executed in parallel, sequentially, or in different orders, as long as the desired result of the technical solution of this invention can be achieved, and this is not limited herein.

[0094] The specific embodiments described above do not constitute a limitation on the scope of protection of this invention. Those skilled in the art should understand that various modifications, combinations, sub-combinations, and substitutions can be made according to design requirements and other factors. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this invention should be included within the scope of protection of this invention.

Claims

1. A blood transfusion / infusion warming tube, characterized in that, include: Heating tube body, heating module, vibration motor and controller; The heating tube body includes a heating pipe, which is used to transport blood or liquid; The heating module is located on the outer wall of the heating pipe body and is used to heat the heating pipe body and obtain the heating temperature of the heating pipe during the heating process. The vibration motor is fixed inside the heating tube and is fixedly connected to the heating module. It is used to drive the heating module to vibrate synchronously during vibration so that the air bubbles generated by blood transfusion or infusion can gather in the infusion chamber. The controller is electrically connected to the heating module and the vibration motor respectively, and is used to control the operation of the heating module and the vibration motor during infusion or blood transfusion, and to receive the heating temperature of the heating pipe obtained by the heating module within a preset period. When the heating temperature does not reach the preset temperature range, the controller adjusts the heating temperature of the heating module until the heating temperature reaches the preset temperature range.

2. The blood transfusion and infusion heating tube according to claim 1, characterized in that, The wall thickness of the heating tube body is 0.5mm-1.5mm, the length is 50cm-150cm, and the inner diameter is 2mm-5mm.

3. The blood transfusion and infusion heating tube according to claim 1, characterized in that, The heating module includes a heating element and a temperature sensor; the vibration motor is fixedly connected to the heating element. The heating element is located on the outer wall of the heating tube body and is used to heat the heating tube body; the temperature sensor is located at the bottom of the outer wall of the heating tube body and is used to obtain the heating temperature of the heating tube body.

4. The blood transfusion and infusion heating tube according to claim 3, characterized in that, The heating element is made of PTC heating element or nylon film heating element; the temperature sensor is made of platinum resistance thermometer or NTC thermistor.

5. The blood transfusion and infusion heating tube according to claim 1, characterized in that, It also includes a pressure sensor; the pressure sensor is located on the outer wall of the heating pipe body and is used to detect the liquid pressure inside the heating pipe; The controller is also electrically connected to the pressure sensor to receive the liquid pressure and reduce the heating power of the heating module when the liquid pressure exceeds a preset pressure threshold.

6. The blood transfusion and infusion heating tube according to claim 1, characterized in that, The vibration motor has a rated power of 1W-5W, a speed of 1000rpm-5000rpm, a vibration frequency of 50Hz-200Hz, and a vibration amplitude of 0.1mm-0.5mm.

7. The blood transfusion and infusion heating tube according to claim 1, characterized in that, It also includes an isolation module; the isolation module includes multiple isolation parts formed by hot-melt welding between the front and back sides of the heating tube body to divide the heating channel into a non-linear tortuous flow channel; The isolation section is disposed within the vibration coverage area of ​​the vibration motor and is used to assist the bubbles in detaching and rising under the vibration action of the vibration motor.

8. The blood transfusion and infusion heating tube according to claim 7, characterized in that, The distance between two adjacent isolation sections is 10mm-30mm; the shape of the heating pipe includes at least an S-shape or a mesh shape.

9. A method for temperature control of a blood transfusion / infusion heating tube, characterized in that, include: During intravenous or blood transfusion, the heating module and vibration motor are controlled to operate, and the heating temperature of the heating pipe obtained by the heating module is received within a preset period. If the heating temperature does not reach the preset temperature range, the heating temperature of the heating module is adjusted until the heating temperature reaches the preset temperature range.

10. The temperature control method according to claim 9, characterized in that, When the heating temperature does not reach the preset temperature range, adjusting the heating temperature of the heating module includes: When the heating temperature does not reach the preset temperature range, the heating temperature adjustment amount is determined based on the heating temperature and the first calculation formula; the first calculation formula is: Where u is the heating temperature adjustment amount, T is the preset period (0.1s ≤ T ≤ 0.5s), Kp is the proportional coefficient, Ki is the integral coefficient, Kd is the differential coefficient, and Kp, Ki, and Kd are all preset constants. 11 e represents the temperature difference between the current heating temperature and the target temperature. 21 This is the temperature difference between the heating temperature obtained from the last sampling and the target temperature. Adjust the heating temperature of the heating module to the specified heating temperature adjustment amount according to the specified heating temperature adjustment amount; And / or, the operating modes of the vibration motor include blood transfusion mode and infusion mode; The method further includes: In the blood transfusion mode, the vibration intensity of the vibration motor is increased; In the infusion mode, the vibration intensity of the vibration motor is reduced.

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