Blood transfusion bag heating equipment for blood transfusion department and uniform heating method

Abstract

The invention provides blood transfusion bag heating equipment for a blood transfusion department and a uniform heating method. The method comprises the following steps: acquiring a temperature value of a blood transfusion bag at a non-collinear preset monitoring point in a heating cavity; a two-dimensional temperature field of the blood transfusion bag on the contact surface of the heating cavity is constructed according to the temperature values of the monitoring points and the spatial distribution relation of the monitoring points, and the uniformity index of temperature distribution of the blood transfusion bag and the balance coefficient of the heat balance trend between the active heating area and the passive heat transfer area are recognized according to the two-dimensional temperature field; adjusting the output power of the heating units to the active heating area monitoring point and the power ratio among the heating units through the uniformity index and the balance coefficient so as to drive the two-dimensional temperature field to converge towards a preset uniform target temperature field; and after the two-dimensional temperature field converges to the uniform target temperature field, constant-temperature feedback adjustment of the blood transfusion bag is carried out based on the passive heat transfer area monitoring points. According to the technical scheme provided by the invention, the blood transfusion bag can be uniformly heated by the heating equipment under the heterogeneity of the heat conduction space.

Description

Technical Field

[0001] This application relates to the field of heating control technology, and more specifically, to a blood bag heating device and a uniform heating method for use in the transfusion department. Background Technology

[0002] Heating control is widely used in industrial production, biomedicine, smart homes, and new energy equipment. Its performance directly determines the system's operational stability, product quality, and energy efficiency. Traditional heating control often uses PID algorithms, which rely on manual parameter tuning. This results in problems such as response lag and low temperature control accuracy, making it difficult to adapt to complex working conditions involving multivariable coupling and nonlinearity. With the upgrading of intelligent manufacturing and energy conservation and environmental protection requirements, as well as the penetration of sensor, Internet of Things, and artificial intelligence technologies, heating control is developing towards precision, intelligence, and self-adaptability.

[0003] In existing heating control systems, especially in biopharmaceutical heating control, the core objective is to achieve a precise, uniform, and stable temperature environment. This heating control is based on a closed-loop feedback system, where a temperature sensor monitors the temperature inside the target bioreactor in real time and transmits the signal to a controller. The controller (typically using a PID algorithm) compares and calculates the measured value with the set value to obtain a heating adjustment signal. This signal then controls the actuator to perform heating control. However, in the uniform heating of blood bag heating equipment used in blood transfusion departments, the heating unit within the heating chamber... When heat is transferred within the cavity, a thermal gradient is formed between the active heating zone (directly heated area) and the passive heat transfer zone (area dependent on heat diffusion) due to the difference in the tightness of the contact between the blood bag and the cavity. As a non-Newtonian fluid, blood's internal convection and heat capacity characteristics further exacerbate the instability of the temperature field, making the active heating zone prone to overheating while the passive heat transfer zone heats up later. This results in uneven temperature distribution in the blood bag heating equipment due to the heterogeneity of the heat conduction space. Therefore, how to achieve uniform heating of the blood bag by the heating equipment under the heterogeneity of the heat conduction space has become a challenge for the industry. Summary of the Invention

[0004] This application provides a blood bag heating device and a uniform heating method for use in the transfusion department, which can achieve uniform heating of the blood bag by the heating device under the heterogeneity of the heat conduction space.

[0005] In a first aspect, this application provides a method for uniform heating of blood bag heating equipment in a transfusion department, comprising the following steps: The temperature value of the blood transfusion bag at a non-collinear preset monitoring point in the heating chamber is obtained. The preset monitoring point includes an active heating zone monitoring point directly corresponding to the heating unit and a passive heat transfer zone monitoring point far away from the heating unit. A two-dimensional temperature field is constructed on the contact surface of the blood transfusion bag in the heating cavity based on the temperature values ​​of each monitoring point and their spatial distribution relationship. The uniformity index of the temperature distribution of the blood transfusion bag and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone are identified based on the two-dimensional temperature field. The output power of the heating unit to the monitoring point of the active heating zone and the power ratio between each heating unit are adjusted by the uniformity index and the balance coefficient, so as to drive the two-dimensional temperature field to converge towards the preset uniform target temperature field. After the two-dimensional temperature field converges to the uniform target temperature field, the blood transfusion bag is subjected to constant temperature feedback regulation based on the monitoring points of the passive heat transfer zone.

[0006] In some embodiments, constructing a two-dimensional temperature field on the contact surface of the blood transfusion bag in the heating cavity based on the temperature values ​​of each monitoring point and their spatial distribution specifically includes: Based on the geometric parameters of the contact surface of the heating cavity, corresponding two-dimensional coordinates are assigned to each non-collinear preset monitoring point; The estimated temperature value of the area where no monitoring points are set on the contact surface of the heating cavity is calculated based on the two-dimensional coordinates of each monitoring point and the corresponding temperature value. The temperature values ​​at each monitoring point are mapped to the estimated temperature values ​​in areas without monitoring points using a grid based on their two-dimensional coordinates, generating a two-dimensional temperature field on the contact surface of the blood transfusion bag in the heating cavity.

[0007] In some embodiments, identifying the uniformity index of the temperature distribution of the blood transfusion bag and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone based on the two-dimensional temperature field specifically includes: The temperature values ​​of all grid points on the contact surface of the heating cavity are extracted from the two-dimensional temperature field, and the grid point temperature set corresponding to the active heating zone and the grid point temperature set corresponding to the passive heat transfer zone are obtained. The mean temperature and standard deviation of temperature are calculated based on the temperature values ​​of all grid points, and then the uniformity index of temperature distribution of blood transfusion bags is determined by the standard deviation of temperature and the mean temperature. The arithmetic mean of the grid point temperature set corresponding to the active heating zone and the grid point temperature set corresponding to the passive heat transfer zone is calculated to obtain the average temperature of the active heating zone and the average temperature of the passive heat transfer zone. Based on the difference between the average temperature of the active heating zone and the average temperature of the passive heat transfer zone, and combined with the preset target temperature, the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone is calculated.

[0008] In some embodiments, adjusting the output power of the heating unit to the monitoring point of the active heating zone and the power ratio between each heating unit by using the uniformity index and the balance coefficient to drive the two-dimensional temperature field to converge toward a preset uniform target temperature field specifically includes: The uniformity index is compared with a preset uniformity threshold to generate a power control signal that characterizes the degree of deviation in temperature distribution. Based on the power control signal, calculate the power reduction amount for the heating unit corresponding to the monitoring point of the active heating zone with the highest current temperature; Based on the balance coefficient, the power reduction amount is proportionally mapped to the power compensation amount of the heating unit corresponding to the monitoring point of the passive heat transfer zone with the lowest temperature, and a power redistribution instruction is generated. In response to the power redistribution command, the power reduction amount and the power compensation amount are executed to form a new power ratio of the heating unit until the two-dimensional temperature field meets the convergence condition of the preset uniform target temperature field.

[0009] In some embodiments, after the two-dimensional temperature field converges to a uniform target temperature field, the isothermal feedback adjustment of the blood transfusion bag based on the monitoring points of the passive heat transfer zone specifically includes: After confirming that the two-dimensional temperature field meets the preset convergence condition, the current power ratio of each heating unit remains unchanged; Real-time temperature data of the blood transfusion bag is collected through the monitoring points in the passive heat transfer zone and the active heating zone. The real-time temperature data of the passive heat transfer zone monitoring point is compared with the real-time temperature data of the nearest active heating zone monitoring point to obtain the temperature deviation value. When the temperature deviation value is lower than the preset temperature deviation threshold, the power adjustment increment of each heating unit is calculated based on the temperature deviation value using a proportional-integral-derivative control algorithm. Based on the maintained current power ratio, the power adjustment increment is added to the current output power of each heating unit to perform power adjustment and provide feedback on the adjustment result.

[0010] In some embodiments, the temperature value of the blood transfusion bag at a non-collinear preset monitoring point within the heating cavity is obtained by a temperature sensor.

[0011] In some embodiments, the temperature sensor is a miniature patch thermocouple sensor.

[0012] Secondly, this application provides a blood bag heating device for use in a transfusion department, which includes a uniform heating unit, the uniform heating unit comprising: The acquisition module is used to acquire the temperature value of the blood bag at a non-collinear preset monitoring point in the heating cavity. The preset monitoring point includes an active heating zone monitoring point directly corresponding to the heating unit and a passive heat transfer zone monitoring point far away from the heating unit. The processing module is used to construct a two-dimensional temperature field on the contact surface of the blood transfusion bag in the heating cavity based on the temperature values ​​of each monitoring point and their spatial distribution relationship, and to identify the uniformity index of the temperature distribution of the blood transfusion bag and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone based on the two-dimensional temperature field. The processing module is also used to adjust the output power of the heating unit to the monitoring point of the active heating zone and the power ratio between each heating unit through the uniformity index and the balance coefficient, so as to drive the two-dimensional temperature field to converge towards the preset uniform target temperature field. The execution module is used to perform constant temperature feedback adjustment of the blood transfusion bag based on the monitoring points of the passive heat transfer zone after the two-dimensional temperature field converges to the uniform target temperature field.

[0013] Thirdly, this application provides a computer device including a memory and a processor, the memory storing code, and the processor being configured to acquire the code and execute the above-described uniform heating method for a blood bag heating device in a transfusion department.

[0014] Fourthly, this application provides a computer-readable storage medium storing a computer program that, when executed by a processor, implements the above-described uniform heating method for a blood transfusion bag heating device in a transfusion department.

[0015] The technical solutions provided by the embodiments disclosed in this application have the following beneficial effects: The blood transfusion bag heating device and uniform heating method provided in this application for blood transfusion departments firstly acquire the temperature values ​​of the blood transfusion bag at non-collinear preset monitoring points within the heating cavity. These preset monitoring points include active heating zone monitoring points directly corresponding to the heating unit and passive heat transfer zone monitoring points far from the heating unit. Secondly, a two-dimensional temperature field is constructed on the contact surface of the blood transfusion bag within the heating cavity based on the temperature values ​​of each monitoring point and their spatial distribution relationship. The uniformity index of the blood transfusion bag temperature distribution and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone are identified based on the two-dimensional temperature field. Then, the output power of the heating unit to the active heating zone monitoring points and the power ratio between each heating unit are adjusted using the uniformity index and the balance coefficient to drive the two-dimensional temperature field to converge towards a preset uniform target temperature field. Finally, after the two-dimensional temperature field converges to the uniform target temperature field, constant temperature feedback adjustment of the blood transfusion bag is performed based on the passive heat transfer zone monitoring points.

[0016] Therefore, this application demonstrates that it can achieve uniform heating of blood transfusion bags by a heating device even under heterogeneous thermal conduction space. Firstly, by acquiring temperature values ​​at non-collinear preset monitoring points in the active heating zone and passive heat transfer zone, it comprehensively covers key temperature acquisition areas on the contact surface of the heating cavity, avoiding the partiality of temperature data caused by single-point or collinear monitoring, and providing spatially representative basic data for subsequent temperature field construction. Secondly, by constructing a two-dimensional temperature field based on the monitoring point temperature values ​​and spatial distribution, and identifying uniformity indicators and balance coefficients, it can transform discrete temperature data into a continuous, quantified temperature distribution model and thermal balance characterization parameters, avoiding the limitations of traditional methods that rely solely on local temperature judgments, and providing precise targeting basis for power adjustment. Then, by adjusting the output power and power ratio of the heating unit through the aforementioned indicators, the temperature can be driven. The convergence of the temperature field towards a uniform target can specifically correct uneven temperature distribution and thermal imbalance between the active and passive heat transfer zones, achieving precise control of the heating process. This avoids uneven temperature distribution caused by differences in the tightness of the contact between the blood bag and the cavity during the transfer of heat output from the heating unit within the heating chamber, which can lead to heterogeneity in the heat conduction space of the blood bag heating device. Finally, after the temperature field converges, isothermal feedback adjustment is performed based on the passive heat transfer zone. This utilizes the characteristic that temperature changes in the passive heat transfer zone reflect overall isothermal stability, continuously correcting minor temperature deviations and maintaining a stable uniform target temperature field. This ensures that the blood bag is heated uniformly throughout the process and that the temperature meets clinical safety standards. In summary, the technical solution provided in this application can achieve uniform heating of blood bags by the heating device even under heterogeneity in the heat conduction space. Attached Figure Description

[0017] Figure 1 This is a schematic diagram of an application scenario architecture for a uniform heating method of a blood transfusion bag heating device for a blood transfusion department, according to some embodiments of this application. Figure 2 This is an exemplary flowchart of a uniform heating method for a blood bag heating device in a transfusion department, according to some embodiments of this application; Figure 3 This is an exemplary flowchart illustrating the determination of a two-dimensional temperature field according to some embodiments of this application; Figure 4 This is a schematic diagram of the structure of a uniform heating unit according to some embodiments of this application; Figure 5 This is a schematic diagram of the structure of a computer device that implements a uniform heating method for a blood bag heating device in a transfusion department, according to some embodiments of this application. Detailed Implementation

[0018] To better understand the technical solution of this application, the technical solution of this application will be described in detail below with reference to the accompanying drawings and specific embodiments.

[0019] refer to Figure 1 This figure is a schematic diagram of an application scenario architecture for a uniform heating method of a blood transfusion bag heating device for a blood transfusion department, according to some embodiments of this application. The application scenario architecture includes a data acquisition terminal, a communication network, and a server. The data acquisition terminal and the server are directly or indirectly connected through the communication network. The data acquisition terminal acquires the temperature values ​​of the blood bag at non-collinear preset monitoring points within the heating chamber and uploads them to the server. The server constructs a two-dimensional temperature field on the contact surface of the blood bag within the heating chamber based on the temperature values ​​of each monitoring point and their spatial distribution relationship. It then identifies a uniformity index of the blood bag temperature distribution and a balance coefficient indicating the thermal equilibrium trend between the active heating zone and the passive heat transfer zone based on the two-dimensional temperature field. The output power of the heating unit to the monitoring points in the active heating zone and the power ratio between the heating units are adjusted using the uniformity index and the balance coefficient to drive the two-dimensional temperature field to converge towards a preset uniform target temperature field. After the two-dimensional temperature field converges to the uniform target temperature field, constant temperature feedback adjustment of the blood bag is performed based on the monitoring points in the passive heat transfer zone.

[0020] refer to Figure 2 The figure is an exemplary flowchart of a uniform heating method for a blood transfusion bag heating device in a blood transfusion department, according to some embodiments of this application. The uniform heating method for the blood transfusion bag heating device in a blood transfusion department mainly includes the following steps: In step 101, the temperature value of the blood transfusion bag at a non-collinear preset monitoring point in the heating cavity is obtained. The preset monitoring point includes an active heating zone monitoring point directly corresponding to the heating unit and a passive heat transfer zone monitoring point far away from the heating unit.

[0021] In practice, the temperature value of the blood bag at a non-collinear preset monitoring point within the heating chamber is obtained through a temperature sensor. Specifically, at least three non-collinear positions are pre-arranged as preset monitoring points within the heating chamber, and a temperature sensor is fixedly installed at each preset monitoring point. The temperature sensor is a miniature patch thermocouple sensor. The preset monitoring points include an active heating zone monitoring point directly corresponding to the heating unit and a passive heat transfer zone monitoring point far from the heating unit. The temperature sensor is fixed at the active heating zone monitoring point directly opposite the heating unit (e.g., the heating film) and the passive heat transfer zone monitoring point far from the heating unit (e.g., the edge of the heating chamber). When the blood bag is placed into the heating chamber and the heating process is started, the temperature value of the blood bag at the non-collinear preset monitoring point within the heating chamber is obtained through the temperature sensor.

[0022] It should be noted that the active heating zone monitoring point in this application refers to the temperature monitoring point located in the area where the blood bag is in direct contact with the heating unit inside the heating cavity, such as the area where the heating film is located. The heat in this area is directly transferred by the heating unit and is the core area of ​​the blood bag being heated. Its temperature change directly responds to the output power of the heating unit. The passive heat transfer zone monitoring point in this application refers to the temperature monitoring point located in the area of ​​the blood bag away from the heating unit inside the heating cavity, such as the area at the edge of the heating cavity. The heat in this area is indirectly obtained through heat conduction, heat convection or heat radiation from the active heating zone. The temperature change lags behind that of the active heating zone and is affected by the cavity environment and the internal blood flow state. The division of the two types of monitoring points aims to accurately capture the temperature characteristics of different heating mechanism areas of the blood bag and provide differentiated data support for the construction of the two-dimensional temperature field.

[0023] In step 102, a two-dimensional temperature field of the blood transfusion bag on the contact surface of the heating cavity is constructed based on the temperature values ​​of each monitoring point and their spatial distribution relationship. The uniformity index of the temperature distribution of the blood transfusion bag and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone are identified based on the two-dimensional temperature field.

[0024] In some embodiments, reference Figure 3 As shown in the figure, this is an exemplary flowchart of determining a two-dimensional temperature field according to some embodiments of this application. In this embodiment, the two-dimensional temperature field of the blood transfusion bag on the contact surface of the heating cavity can be constructed based on the temperature values ​​of each monitoring point and their spatial distribution relationship by the following steps: First, in step 1021, based on the geometric parameters of the contact surface of the heating cavity, corresponding two-dimensional coordinates are assigned to each non-collinear preset monitoring point; Then, in step 1022, the estimated temperature value of the area where no monitoring point is set on the contact surface of the heating cavity is calculated based on the two-dimensional coordinates of each monitoring point and the corresponding temperature value. Finally, in step 1023, the temperature values ​​of each monitoring point and the estimated temperature values ​​of the area without monitoring points are mapped in a grid according to their two-dimensional coordinates to generate a two-dimensional temperature field of the blood transfusion bag on the contact surface of the heating cavity.

[0025] In specific implementation, firstly, the geometric parameters of the heating cavity contact surface are obtained. These parameters include the overall shape of the heating cavity contact surface (e.g., rectangular, circular). A fixed reference point (e.g., the lower left corner vertex of a rectangular contact surface, the center of a circular contact surface) is set as the origin of the coordinate system based on the overall shape of the heating cavity contact surface. The x-axis and y-axis are set along two mutually perpendicular edges of the heating cavity contact surface, establishing a Cartesian coordinate system. Then, the two-dimensional coordinates of each non-collinear preset monitoring point are obtained in this Cartesian coordinate system. These two-dimensional coordinates refer to the specific location data of each monitoring point in the Cartesian coordinate system. Next, an existing bilinear interpolation algorithm is selected, using the two-dimensional coordinates of each monitoring point and its corresponding temperature value as algorithm input. By calculating the temperature gradient and spatial weight coefficient between four adjacent monitoring points, the algorithm is applied to the heating cavity contact surface where no coordinates are set. Temperature estimation is performed on the monitoring points to obtain the estimated temperature values ​​for each unmonitored area. This will not be elaborated further. The spatial location weight coefficient refers to the numerical weight assigned based on the distance between the monitoring point and the target area; the closer the distance, the larger the weight coefficient. The spatial location weight coefficient is calculated by normalizing the inverse of the coordinate difference between the estimated location and the adjacent monitoring point. The estimated temperature value refers to the temperature value of the unmonitored area obtained through linear interpolation. Finally, the rectangular area formed by dividing the heating cavity contact surface at fixed intervals along the X and Y axes is used as a grid unit. Each grid unit corresponds to a unique spatial coordinate range. The measured temperature values ​​of each preset monitoring point and the estimated temperature values ​​of the unmonitored area are mapped to the corresponding grid units according to their corresponding two-dimensional coordinates, generating a two-dimensional temperature field of the blood transfusion bag on the heating cavity contact surface.

[0026] It should be noted that the two-dimensional temperature field in this application refers to a visual model reflecting the temperature distribution at various locations on the contact interface between the blood bag and the heating chamber. It contains specific temperature information for each grid cell. During the heating of the blood bag, the temperature distribution within the heating chamber is significantly heterogeneous due to factors such as the layout of the heating cells, differences in heat conduction paths, and uneven distribution of blood mass. Traditional collinear temperature monitoring can only obtain local temperature data and cannot fully reflect the temperature difference between the active heating zone and the passive heat transfer zone, as well as the overall temperature gradient. Therefore, this application transforms the discrete temperature data of each non-collinear preset monitoring point into a continuous and complete contact surface temperature distribution model. This provides comprehensive and reliable data support for the subsequent accurate identification of temperature distribution uniformity indicators and the calculation of the heat balance coefficient between the active heating zone and the passive heat transfer zone. This enables the adjustment of the output power of the heating cell and the power ratio between each cell to have clear targeting, avoiding the blind control caused by the one-sided temperature perception in traditional control strategies.

[0027] In some embodiments, the identification of the uniformity index of the temperature distribution of the blood transfusion bag and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone based on the two-dimensional temperature field is achieved by the following steps: The temperature values ​​of all grid points on the contact surface of the heating cavity are extracted from the two-dimensional temperature field, and the grid point temperature set corresponding to the active heating zone and the grid point temperature set corresponding to the passive heat transfer zone are obtained. The mean temperature and standard deviation of temperature are calculated based on the temperature values ​​of all grid points, and then the uniformity index of temperature distribution of blood transfusion bags is determined by the standard deviation of temperature and the mean temperature. The arithmetic mean of the grid point temperature set corresponding to the active heating zone and the grid point temperature set corresponding to the passive heat transfer zone is calculated to obtain the average temperature of the active heating zone and the average temperature of the passive heat transfer zone. Based on the difference between the average temperature of the active heating zone and the average temperature of the passive heat transfer zone, and combined with the preset target temperature, the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone is calculated.

[0028] In specific implementation, firstly, the grid range of the active heating zone and the passive heat transfer zone is divided according to the preset installation position of the heating unit. The temperature values ​​of all grid points are extracted from the two-dimensional temperature field, and then the temperature sets of grid points corresponding to the active heating zone and the passive heat transfer zone are obtained. The temperature sets of grid points refer to the collection of temperature data of grid points corresponding to the active heating zone and the passive heat transfer zone in the two-dimensional temperature field. Secondly, the temperature mean and temperature standard deviation are calculated based on the temperature values ​​of all grid points. The ratio of the temperature standard deviation to the temperature mean is then calculated, and the result of the ratio calculation is used as the uniformity index of the blood bag temperature distribution. The uniformity index refers to the parameter characterizing the consistency of the blood bag temperature distribution. Then, the arithmetic mean algorithm is applied to the temperature sets of grid points corresponding to the active heating zone and the passive heat transfer zone, respectively. That is, by summing the temperature values ​​of all grid points in each set and dividing by the number of grid points in the corresponding set, the average temperature of the active heating zone and the average temperature of the passive heat transfer zone are obtained, respectively. The average temperature of the active heating zone refers to the arithmetic mean of all temperature data in the grid point temperature set corresponding to the active heating zone, reflecting the overall heating situation of the active heating zone. The average temperature of the passive heat transfer zone refers to the arithmetic mean of all temperature data in the grid point temperature set corresponding to the passive heat transfer zone, reflecting the overall heating level of the passive heat transfer zone. Finally, the average temperature of the active heating zone and the average temperature of the passive heat transfer zone are calculated to obtain the temperature difference value. The temperature difference value refers to the difference in the overall temperature level between the active heating zone and the passive heat transfer zone. The sign of the difference value reflects the temperature trend, and the magnitude of the difference value reflects the degree of thermal imbalance. The temperature difference value is used as the numerator and the preset target temperature is used as the denominator for division. The sign of the temperature difference value is retained during the calculation to clarify the direction of thermal imbalance. The final dimensionless calculation result is the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone. The preset target temperature refers to the target blood heating temperature required for clinical blood transfusion safety, which is a pre-set fixed temperature value, and will not be elaborated here.

[0029] It should be noted that the balance coefficient in this application refers to a parameter characterizing the heat exchange balance between the active heating zone and the passive heat transfer zone. The balance coefficient is determined because the active heating zone and the passive heat transfer zone naturally have a temperature gradient due to the difference in heat transfer mechanisms (the former is direct heat transfer from the heating unit, while the latter is indirect heat conduction and convection). The temperature difference between the two zones can only reflect the absolute temperature difference and cannot quantify the relative degree of thermal imbalance in combination with the preset target temperature for blood bag heating. It is difficult to provide an accurate basis for adjusting the heating power. Therefore, the absolute temperature difference between the average temperature of the active heating zone and the average temperature of the passive heat transfer zone is transformed into a dimensionless quantitative index through correlation calculation with the preset target temperature. This not only intuitively represents the degree of thermal balance between the two zones, but also clarifies the direction of thermal imbalance. This provides a clear and targeted basis for subsequent dynamic adjustment of the output power of the heating unit and the power ratio between each unit, avoiding the problem of local overheating or insufficient heating caused by focusing only on the overall temperature and ignoring the thermal imbalance between the two zones in traditional control.

[0030] In step 103, the output power of the heating unit to the monitoring point of the active heating zone and the power ratio between each heating unit are adjusted by the uniformity index and the balance coefficient, so as to drive the two-dimensional temperature field to converge toward the preset uniform target temperature field.

[0031] In some embodiments, adjusting the output power of the heating unit to the monitoring point of the active heating zone and the power ratio between each heating unit through the uniformity index and the balance coefficient to drive the two-dimensional temperature field to converge toward a preset uniform target temperature field is achieved through the following steps: The uniformity index is compared with a preset uniformity threshold to generate a power control signal that characterizes the degree of deviation in temperature distribution. Based on the power control signal, calculate the power reduction amount for the heating unit corresponding to the monitoring point of the active heating zone with the highest current temperature; Based on the balance coefficient, the power reduction amount is proportionally mapped to the power compensation amount of the heating unit corresponding to the monitoring point of the passive heat transfer zone with the lowest temperature, and a power redistribution instruction is generated. In response to the power redistribution command, the power reduction amount and the power compensation amount are executed to form a new power ratio of the heating unit until the two-dimensional temperature field meets the convergence condition of the preset uniform target temperature field.

[0032] In specific implementation, firstly, the identified uniformity index is compared numerically with a uniformity threshold, which includes an upper and lower limit. If the uniformity index exceeds the upper limit, a high-priority power control signal is generated; if it falls within the upper and lower limits, a medium-priority signal is generated; and if it does not fall below the lower limit, a low-priority signal is generated. This generates a power control signal characterizing the degree of temperature distribution deviation. This power control signal is a control signal that reflects the severity of temperature distribution uniformity deviation and guides power adjustment. The uniformity threshold can be set according to actual needs or expert knowledge; no limitation is made here. Secondly, based on the power... The power control signal is used to filter out the monitoring point of the active heating zone with the highest current temperature and locate its corresponding heating unit. The current output power of the heating unit is obtained. The control coefficient corresponding to the priority level of the power control signal (the higher the priority, the larger the control coefficient; for example, the control coefficients corresponding to high, medium, and low priority power control signals can be set between 0.6-0.9, 0.3-0.6, and 0.1-0.3 respectively, without limitation here), and the difference between the temperature of the highest temperature monitoring point and the preset target temperature are used as input variables. Combined with the current output power of the heating unit, the power reduction amount is calculated as: power reduction amount = current output power × control coefficient × (highest temperature - preset target temperature) / preset target temperature. Where the highest temperature is greater than the preset target temperature, the power reduction amount is calculated as follows: power reduction amount = current output power × control coefficient × (highest temperature - preset target temperature) / preset target temperature. Assuming the target temperature is taken as an absolute value, this formula is used when the temperature in the active heating zone is too high. The power reduction amount refers to the amount of output power of the heating unit that needs to be reduced to lower the temperature of the high-temperature active heating zone. Then, using linear proportional calculation known in the field of control engineering, the power reduction amount is multiplied by the absolute value of the balance coefficient to calculate the power compensation amount for the heating unit corresponding to the monitoring point of the lowest-temperature passive heat transfer zone. The power compensation amount integrates the identifier of the active heating zone heating unit that needs power reduction, the power reduction amount, the identifier of the passive heat transfer zone heating unit that needs power compensation, the power compensation amount, and the synchronous execution sequence to generate a power redistribution command. The power redistribution command is a control command for performing power redistribution, used to drive the heating unit to reduce its output power. The heating unit performs a power adjustment operation; finally, in response to the power redistribution command, the corresponding heating unit is controlled by the power drive module to perform power reduction and power compensation operations to form a new heating unit power ratio. The new heating unit power ratio refers to the proportional relationship of the output power of each heating unit after adjustment, ensuring that the cooling of the active heating zone and the heating of the passive heat transfer zone are achieved synchronously. The process of comparing the uniformity index, calculating the power reduction and compensation amount, and executing the power redistribution is repeated until the uniformity index of the two-dimensional temperature field meets the convergence condition of the preset uniform target temperature field. The convergence condition refers to the pre-set critical standard for judging that the temperature field has reached the uniform target state, such as the uniformity index being lower than the uniformity threshold and the balance coefficient being lower than the preset balance coefficient.

[0033] It should be noted that the uniform target temperature field in this application refers to a target temperature distribution model that is pre-set according to clinical transfusion safety standards, where the active heating area and passive heat transfer area on the contact surface between the blood bag and the heating cavity meet the thermal balance requirements. The function of driving the two-dimensional temperature field to converge toward the preset uniform target temperature field is to precisely correct the regional temperature difference and thermal imbalance of the actual temperature field by directionally adjusting the output power of the heating unit and the power ratio between each unit. This avoids local overheating or insufficient heating of the blood bag, which would lead to substandard transfusion temperature. It ensures that the blood bag is heated uniformly and the temperature is stable within the clinical safety range, ultimately meeting the clinical transfusion requirements for precise control of blood temperature.

[0034] In step 104, after the two-dimensional temperature field converges to the uniform target temperature field, the constant temperature feedback adjustment of the blood transfusion bag is performed based on the monitoring points of the passive heat transfer zone.

[0035] In some embodiments, after the two-dimensional temperature field converges to a uniform target temperature field, the isothermal feedback regulation of the blood transfusion bag based on the monitoring points of the passive heat transfer zone is achieved by the following steps: After confirming that the two-dimensional temperature field meets the preset convergence condition, the current power ratio of each heating unit remains unchanged; Real-time temperature data of the blood transfusion bag is collected through the monitoring points in the passive heat transfer zone and the active heating zone. The real-time temperature data of the passive heat transfer zone monitoring point is compared with the real-time temperature data of the nearest active heating zone monitoring point to obtain the temperature deviation value. When the temperature deviation value is lower than the preset temperature deviation threshold, the power adjustment increment of each heating unit is calculated based on the temperature deviation value using a proportional-integral-derivative control algorithm. Based on the maintained current power ratio, the power adjustment increment is added to the current output power of each heating unit to perform power adjustment and provide feedback on the adjustment result.

[0036] In specific implementation, firstly, after confirming that the two-dimensional temperature field meets the preset convergence condition, the current power ratio of each heating unit remains unchanged; secondly, real-time temperature data of the blood transfusion bag is collected through the monitoring points of the passive heat transfer zone and the active heating zone; further, based on the established Cartesian coordinate system, the nearest active heating zone monitoring point of each passive heat transfer zone monitoring point is selected by calculating the Euclidean distance, and the difference between the real-time temperature data of the two is calculated to obtain the temperature deviation value between each passive heat transfer zone monitoring point and the nearest active zone monitoring point. The temperature deviation value refers to the temperature difference between the passive heat transfer zone and the nearest active heating zone; then, when the temperature deviation value is lower than the preset temperature deviation threshold, the proportional-integral-derivative (PID) control algorithm is selected, and the temperature deviation value is used as the algorithm input. The proportional term (i.e., deviation value × P), integral term (i.e., integral of deviation value × I), and derivative term (d) are calculated respectively using preset proportional coefficients (P), integral coefficients (I), and derivative coefficients (D) (these three types of coefficients are determined through multiple calibration experiments based on the thermal response characteristics of the equipment, and will not be elaborated here). The three results are then superimposed to obtain the power adjustment increment of each heating unit. The power adjustment increment refers to the value of the output power of the heating unit that needs to be increased or decreased to correct the temperature deviation. Finally, based on the unchanged current power ratio, the power adjustment increment corresponding to each heating unit is superimposed to its current output power, and the power adjustment is executed through the power drive module. The adjusted real-time power data is fed back to the control module to form a constant temperature feedback closed-loop control, thereby completing the constant temperature feedback adjustment of the blood transfusion bag.

[0037] In another aspect, in some embodiments, this application provides a blood bag heating device for a transfusion department, the device including a uniform heating unit, referenced... Figure 4 The figure is a schematic diagram of the structure of a uniform heating unit according to some embodiments of this application. The uniform heating unit includes: an acquisition module 201, a processing module 202, and an execution module 203, which are described below: The acquisition module 201 in this application is mainly used to acquire the temperature value of the blood transfusion bag at a non-collinear preset monitoring point in the heating cavity. The preset monitoring point includes an active heating zone monitoring point directly corresponding to the heating unit and a passive heat transfer zone monitoring point far away from the heating unit. Processing module 202, in this application, is mainly used to construct a two-dimensional temperature field on the contact surface of the blood transfusion bag on the heating cavity based on the temperature values ​​of each monitoring point and their spatial distribution relationship, and to identify the uniformity index of the temperature distribution of the blood transfusion bag and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone based on the two-dimensional temperature field. The processing module 202 is also used to adjust the output power of the heating unit to the monitoring point of the active heating zone and the power ratio between each heating unit through the uniformity index and the balance coefficient, so as to drive the two-dimensional temperature field to converge towards the preset uniform target temperature field. The execution module 203 in this application is mainly used to perform constant temperature feedback adjustment of the blood transfusion bag based on the monitoring point of the passive heat transfer zone after the two-dimensional temperature field converges to the uniform target temperature field.

[0038] In addition, this application also provides a computer device, the computer device including a memory and a processor, the memory storing code, the processor being configured to acquire the code and execute the above-described uniform heating method for a blood bag heating device in a transfusion department.

[0039] In some embodiments, reference Figure 5 The figure is a schematic diagram of the structure of a computer device implementing a uniform heating method for a blood transfusion bag heating device in a transfusion department, according to some embodiments of this application. The uniform heating method for a blood transfusion bag heating device in the above embodiments can be achieved through… Figure 5 The computer device shown is used to implement this, and the computer device includes at least one processor 301, a communication bus 302, a memory 303, and at least one communication interface 304.

[0040] The processor 301 may be a general-purpose central processing unit (CPU), an application-specific integrated circuit (ASIC), or one or more devices used to control the execution of a uniform heating method for the blood bag heating device used in the transfusion department of this application.

[0041] The communication bus 302 can be used to transmit information between the aforementioned components.

[0042] The memory 303 may be a read-only memory (ROM) or other type of static storage device capable of storing static information and instructions, random access memory (RAM) or other type of dynamic storage device capable of storing information and instructions, or electrically erasable programmable read-only memory (EEPROM), compact disc read-only memory (CDROM) or other optical disc storage, optical disc storage (including compressed optical discs, laser discs, optical discs, digital universal optical discs, Blu-ray discs, etc.), magnetic disks or other magnetic storage devices, or any other medium capable of carrying or storing desired program code in the form of instructions or data structures and accessible by a computer, but not limited thereto. The memory 303 may exist independently and be connected to the processor 301 via the communication bus 302. The memory 303 may also be integrated with the processor 301.

[0043] The memory 303 stores program code for executing the scheme of this application, and its execution is controlled by the processor 301. The processor 301 executes the program code stored in the memory 303. The program code may include one or more software modules. In the above embodiments, the determination of the uniform heating method of the blood bag heating device for the blood transfusion department can be achieved by the processor 301 and one or more software modules in the program code in the memory 303.

[0044] Communication interface 304 uses any transceiver-like device for communicating with other devices or communication networks, such as Ethernet, radio access network (RAN), wireless local area networks (WLAN), etc.

[0045] In a specific implementation, as one example, a computer device may include multiple processors, each of which may be a single-core (single CPU) processor or a multi-core (multi CPU) processor. Here, a processor may refer to one or more devices, circuits, and / or processing cores used to process data (e.g., computer program instructions).

[0046] The aforementioned computer device can be a general-purpose computer device or a special-purpose computer device. In specific implementations, the computer device can be a desktop computer, a portable computer, a network server, a handheld digital assistant (PDA), a mobile phone, a tablet computer, a wireless terminal device, a communication device, or an embedded device. This application does not limit the type of computer device.

[0047] In addition, this application also provides a computer-readable storage medium storing a computer program that, when executed by a processor, implements the above-described uniform heating method for a blood bag heating device used in a blood transfusion department.

[0048] Although preferred embodiments of this application have been described, those skilled in the art, upon learning the basic inventive concept, can make other changes and modifications to these embodiments. Therefore, the appended claims are intended to be interpreted as including the preferred embodiments as well as all changes and modifications falling within the scope of this application.

[0049] Obviously, those skilled in the art can make various modifications and variations to this application without departing from the spirit and scope of this application. Therefore, if such modifications and variations fall within the scope of the claims of this application and their equivalents, this application also intends to include such modifications and variations.

Claims

1. A method for uniform heating of blood bag heating equipment used in blood transfusion departments, characterized in that, Includes the following steps: The temperature value of the blood transfusion bag at a non-collinear preset monitoring point in the heating chamber is obtained. The preset monitoring point includes an active heating zone monitoring point directly corresponding to the heating unit and a passive heat transfer zone monitoring point far away from the heating unit. A two-dimensional temperature field is constructed on the contact surface of the blood transfusion bag in the heating cavity based on the temperature values ​​of each monitoring point and their spatial distribution relationship. The uniformity index of the temperature distribution of the blood transfusion bag and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone are identified based on the two-dimensional temperature field. The output power of the heating unit to the monitoring point of the active heating zone and the power ratio between each heating unit are adjusted by the uniformity index and the balance coefficient, so as to drive the two-dimensional temperature field to converge towards the preset uniform target temperature field. After the two-dimensional temperature field converges to the uniform target temperature field, the blood transfusion bag is subjected to constant temperature feedback regulation based on the monitoring points of the passive heat transfer zone.

2. The method as described in claim 1, characterized in that, The two-dimensional temperature field of the blood transfusion bag on the contact surface of the heating cavity is constructed based on the temperature values ​​of each monitoring point and their spatial distribution. Specifically, this includes: Based on the geometric parameters of the contact surface of the heating cavity, corresponding two-dimensional coordinates are assigned to each non-collinear preset monitoring point; The estimated temperature value of the area where no monitoring points are set on the contact surface of the heating cavity is calculated based on the two-dimensional coordinates of each monitoring point and the corresponding temperature value. The temperature values ​​at each monitoring point are mapped to the estimated temperature values ​​in areas without monitoring points using a grid based on their two-dimensional coordinates, generating a two-dimensional temperature field on the contact surface of the blood transfusion bag in the heating cavity.

3. The method as described in claim 1, characterized in that, The uniformity index of temperature distribution in blood transfusion bags and the balance coefficient of thermal equilibrium trend between the active heating zone and the passive heat transfer zone, identified based on the two-dimensional temperature field, specifically include: The temperature values ​​of all grid points on the contact surface of the heating cavity are extracted from the two-dimensional temperature field, and the grid point temperature set corresponding to the active heating zone and the grid point temperature set corresponding to the passive heat transfer zone are obtained. The mean temperature and standard deviation of temperature are calculated based on the temperature values ​​of all grid points, and then the uniformity index of temperature distribution of blood transfusion bags is determined by the standard deviation of temperature and the mean temperature. The arithmetic mean of the grid point temperature set corresponding to the active heating zone and the grid point temperature set corresponding to the passive heat transfer zone is calculated to obtain the average temperature of the active heating zone and the average temperature of the passive heat transfer zone. Based on the difference between the average temperature of the active heating zone and the average temperature of the passive heat transfer zone, and combined with the preset target temperature, the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone is calculated.

4. The method as described in claim 1, characterized in that, Adjusting the output power of the heating unit to the monitoring points of the active heating zone and the power ratio between each heating unit by using the uniformity index and the balance coefficient to drive the two-dimensional temperature field to converge toward the preset uniform target temperature field specifically includes: The uniformity index is compared with a preset uniformity threshold to generate a power control signal that characterizes the degree of deviation in temperature distribution. Based on the power control signal, calculate the power reduction amount for the heating unit corresponding to the monitoring point of the active heating zone with the highest current temperature; Based on the balance coefficient, the power reduction amount is proportionally mapped to the power compensation amount of the heating unit corresponding to the monitoring point of the passive heat transfer zone with the lowest temperature, and a power redistribution instruction is generated. In response to the power redistribution command, the power reduction amount and the power compensation amount are executed to form a new power ratio of the heating unit until the two-dimensional temperature field meets the convergence condition of the preset uniform target temperature field.

5. The method as described in claim 1, characterized in that, After the two-dimensional temperature field converges to the uniform target temperature field, the isothermal feedback adjustment of the blood transfusion bag based on the monitoring points of the passive heat transfer zone specifically includes: After confirming that the two-dimensional temperature field meets the preset convergence condition, the current power ratio of each heating unit remains unchanged; Real-time temperature data of the blood transfusion bag is collected through the monitoring points in the passive heat transfer zone and the active heating zone. The real-time temperature data of the passive heat transfer zone monitoring point is compared with the real-time temperature data of the nearest active heating zone monitoring point to obtain the temperature deviation value. When the temperature deviation value is lower than the preset temperature deviation threshold, the power adjustment increment of each heating unit is calculated based on the temperature deviation value using a proportional-integral-derivative control algorithm. Based on the maintained current power ratio, the power adjustment increment is added to the current output power of each heating unit to perform power adjustment and provide feedback on the adjustment result.

6. The method as described in claim 1, characterized in that, Temperature values ​​of the blood transfusion bag at non-collinear preset monitoring points within the heating chamber are obtained using temperature sensors.

7. The method as described in claim 6, characterized in that, The temperature sensor is a miniature patch thermocouple sensor.

8. A blood bag warming device for use in a transfusion department, the blood bag warming device comprising a uniform heating unit, characterized in that, The uniform heating unit includes: The acquisition module is used to acquire the temperature value of the blood bag at a non-collinear preset monitoring point in the heating cavity. The preset monitoring point includes an active heating zone monitoring point directly corresponding to the heating unit and a passive heat transfer zone monitoring point far away from the heating unit. The processing module is used to construct a two-dimensional temperature field on the contact surface of the blood transfusion bag in the heating cavity based on the temperature values ​​of each monitoring point and their spatial distribution relationship, and to identify the uniformity index of the temperature distribution of the blood transfusion bag and the balance coefficient of the thermal balance trend between the active heating zone and the passive heat transfer zone based on the two-dimensional temperature field. The processing module is also used to adjust the output power of the heating unit to the monitoring point of the active heating zone and the power ratio between each heating unit through the uniformity index and the balance coefficient, so as to drive the two-dimensional temperature field to converge towards the preset uniform target temperature field. The execution module is used to perform constant temperature feedback adjustment of the blood transfusion bag based on the monitoring points of the passive heat transfer zone after the two-dimensional temperature field converges to the uniform target temperature field.

9. A computer device, characterized in that, The computer device includes a memory and a processor, the memory storing code, and the processor being configured to retrieve the code and execute a uniform heating method for a blood bag heating device for a transfusion department as described in any one of claims 1 to 7.

10. A computer-readable storage medium storing a computer program, characterized in that, When the computer program is executed by the processor, it implements the uniform heating method for a blood bag heating device for a transfusion department as described in any one of claims 1 to 7.

Images