Method for controlling a limb compression device based on a visualized map and limb compression device

Abstract

The present application relates to air pressure equipment control technical field, disclose a kind of limb pressurizing equipment control method and limb pressurizing equipment, to solve the problems that existing method is tedious, setting precision is poor and resource occupation is high, scheme mainly includes: in display interface construction to air bag serial number as abscissa, pressure value as ordinate pressure atlas of line graph form is constructed;In response to the automatic gradient mode or custom mode selected by user, only need to set the first and last air bag boundary value in automatic gradient mode, automatically derive the target pressure value of each air bag in the middle and update atlas, in custom mode, corresponding air bag pressure value is adjusted in real time by dragging atlas node and updating atlas;According to the target pressure value determined by the updated pressure atlas, the inflation and deflation control of each air bag is executed.The present application improves the convenience and accuracy of limb pressurizing equipment control, reduces the operation load and resource occupation, and is especially suitable for air wave massage instrument.

Description

Technical Field

[0001] This invention relates to the field of pneumatic equipment control technology, specifically to a control method and a limb pressurization device based on a visualization graph. Background Technology

[0002] Limb compression devices (such as air wave massagers) are devices that achieve physical massage by applying controllable pressure to the limbs. They use multi-chamber airbags to sequentially and repeatedly inflate and deflate, applying periodic cyclical pressure to the limbs to simulate massage techniques such as kneading and squeezing by human hands. These devices typically include multiple airbags, an air pump, a solenoid valve, a controller, and a display.

[0003] Currently, limb compression devices are generally equipped with six or more independent airbags. During operation, a target pressure value needs to be set for each airbag, and a controller drives the air pump and solenoid valves in a preset sequence to control the inflation and deflation of each airbag. To achieve independent pressure control for each airbag, existing technologies typically employ a scheme where each airbag is connected in series with an intake control solenoid valve, and the air pump inflates each airbag separately through multiple parallel air paths; some solutions also use flexible force sensors on the surface of the airbags to monitor the pressure status of each airbag in real time.

[0004] However, existing limb compression devices have the following shortcomings in terms of pressure setting and interactive control:

[0005] First, the operation is cumbersome. Traditional devices typically have six or more independent air chambers. When adjusting the pressure, users need to access a sub-menu for each air chamber to set the pressure value, or rotate multiple physical knobs. If a fine adjustment of the pressure value of a specific air chamber is required, it is necessary to frequently switch between multiple setting pages, making the operation lengthy and inefficient.

[0006] Second, the settings are inaccurate. Users need to manually input the pressure values ​​for more than six airbags one by one. It is very easy for operational errors to cause the values ​​of adjacent airbags to jump, which disrupts the smooth transition of pressure. This makes the changes in massage pressure inconsistent with the force patterns of the limbs' natural shape, affecting the massage experience and potentially causing excessive local pressure, leading to user discomfort.

[0007] Third, the system has a high computational load. The traditional method of setting up airbags one by one requires the main control chip to frequently refresh register data on different pages, which consumes a lot of memory resources and increases the risk of system lag and crashes.

[0008] Application publication number CN121445600A discloses an intelligent control method and system for a limb compression device. This method determines the pressure curve of the target limb by collecting multiple training features and combining the pressure condition of the target limb with the user's age, thus achieving automatic determination of pressure parameters. However, in this solution, the user cannot intuitively adjust the specific pressure value of each airbag according to their own feelings, lacking a convenient human-computer interaction method; it also does not involve the fine adjustment of the pressure gradient configuration between airbags in multi-airbag scenarios, making it difficult to meet the differentiated needs of different users for chamber-by-chamber pressure distribution; moreover, it requires the collection of multiple data sources and multiple calculation steps to generate the pressure curve, resulting in a complex system architecture and high computational resource consumption. Summary of the Invention

[0009] This invention aims to solve the problems of cumbersome operation, poor setting accuracy, and high resource consumption in the control methods of existing limb compression devices, and proposes a control method and limb compression device based on visualization map.

[0010] The technical solution adopted by the present invention to solve the above-mentioned technical problems is as follows:

[0011] In a first aspect, the present invention provides a control method for a limb compression device based on a visual atlas, wherein the limb compression device includes N airbags, the N airbags being arranged sequentially along the limb from the distal end to the proximal end, wherein the first airbag corresponds to the distal end of the limb, and the Nth airbag corresponds to the proximal end of the limb; the method includes:

[0012] A pressure map is constructed on the display interface. The pressure map uses the airbag number as the horizontal axis and the pressure value as the vertical axis, and displays the pressure distribution of each airbag in real time in the form of a broken line.

[0013] In response to a user's mode selection action, the modes include automatic gradient mode and custom mode;

[0014] In the automatic gradient mode, the user-defined first airbag pressure boundary value and the Nth airbag pressure boundary value are obtained. Based on the preset physiological attenuation algorithm, the target pressure values ​​of the 2nd to N-1th airbags are generated according to the first airbag pressure boundary value and the Nth airbag pressure boundary value. The pressure map is updated according to the first airbag pressure boundary value, the Nth airbag pressure boundary value and the target pressure values ​​of the 2nd to N-1th airbags.

[0015] In the custom mode, the user's drag operation on any node on the polyline is obtained, the position of the node in the vertical axis direction is mapped to the target pressure value of the corresponding airbag, and the pressure map is updated.

[0016] Inflation and deflation control is performed on each airbag based on the target pressure value determined by the updated pressure map.

[0017] The above solution constructs a pressure map in the form of a line graph on the display interface, allowing users to intuitively view the pressure distribution of all airbags; and provides two control logics: automatic gradient mode and custom mode. In automatic gradient mode, users only need to set the pressure boundary values ​​of the first and last airbags. Based on a preset physiological attenuation algorithm, the target pressure values ​​of each intermediate airbag are automatically derived and the graph is updated. This simplifies multiple settings for each chamber into a one-time operation, significantly reducing operation steps and avoiding numerical jumps, ensuring a smooth pressure transition. In custom mode, users can directly drag the line nodes to adjust the pressure value of the corresponding airbag in real time, improving operational convenience and accuracy. At the same time, it simplifies multiple writes that require frequent refreshing of data in different page registers into a single batch write, significantly reducing system computational load and resource consumption.

[0018] Furthermore, the preset physiological attenuation algorithm includes:

[0019] Call the pre-stored weight coefficients Where i is the airbag number, i∈[1,N], and N is the total number of airbags. The trend decreases as the airbag serial number i increases, and The weighting coefficients Based on pre-stored human anatomical data, the weights are used to characterize the influence of limb taper changes from distal to proximal on external vascular pressure.

[0020] The target pressure value of the i-th airbag is calculated using the following formula. :

[0021] ;

[0022] in, This is the first airbag pressure boundary value. This represents the Nth airbag pressure boundary value.

[0023] The above method utilizes pre-stored weighting coefficients based on human anatomy data to calculate the target pressure value for each airbag. Weighting coefficients Based on the tapering variation of the limb from distal to proximal, the pressure gradient is preset, decreasing with increasing airbag number i, but in a non-linear manner. Users only need to set the first and last boundary values ​​to automatically obtain the complete chamber-by-chamber pressure gradient sequence, improving setting accuracy and safety. Furthermore, since the human limb is not a uniform cylinder but a cone that gradually thickens from distal to proximal, compared to using linear interpolation to achieve a uniform decrease, the weighting coefficient... Based on the limb circumference change rate and venous return hydrodynamic model, a nonlinear pressure curve that fits the human conical anatomical structure can be generated, so that the pressure reduction amplitude between adjacent air bladders can automatically adapt to the morphological changes of different limb segments, avoiding the discomfort caused by uniform reduction in circumference abrupt changes or insufficient pressure attenuation in flat segments.

[0024] Furthermore, after calculating the target pressure value of the i-th airbag... Following this, a smoothing correction step is also included:

[0025] Calculate the pressure difference between adjacent airbags : ;

[0026] If the pressure difference Exceeding the preset maximum differential pressure threshold Then the target pressure value will be automatically reverted. Until satisfied .

[0027] The above scheme calculates the pressure difference between adjacent airbags and determines whether it exceeds the preset maximum pressure difference threshold. If it exceeds the threshold, it automatically adjusts back to the target pressure value until the constraint conditions are met. This effectively prevents sudden changes in local pressure caused by excessive pressure differences between adjacent airbags and improves the safety and physiological rationality of the multi-airbag pressure distribution.

[0028] Furthermore, the maximum differential pressure threshold The blood pressure is 30 mmHg.

[0029] The above solution, by setting the maximum pressure difference threshold to 30 mmHg, ensures that there will not be an excessive pressure difference between adjacent airbags that would cause localized pressure on the limbs. While ensuring the user's comfort, it provides sufficient safety redundancy for the pressure values ​​of each airbag generated in automatic gradient mode.

[0030] Furthermore, the preset physiological attenuation algorithm includes:

[0031] Calculate the segment spacing k using the following formula:

[0032] ;

[0033] The target pressure value of the i-th airbag is calculated using the following formula. :

[0034] ;

[0035] Where i is the airbag number, i∈[1,N], and N is the total number of airbags. This is the first airbag pressure boundary value. This represents the Nth airbag pressure boundary value.

[0036] The above scheme uses a linear interpolation algorithm as another implementation of the physiological decay algorithm. By calculating the segment spacing, it generates an arithmetically decreasing pressure sequence, providing a less computationally intensive alternative for the automatic gradient mode, which is suitable for devices with limited computing power.

[0037] Furthermore, in the automatic gradient mode, the user-set first airbag pressure boundary value and Nth airbag pressure boundary value are obtained through the touch slider or numerical input box on the display interface, and the first airbag pressure boundary value is greater than the Nth airbag pressure boundary value.

[0038] The above solution uses a touch slider or numerical input box in automatic gradient mode to obtain the user-set first and last pressure boundary values. The pressure value input method is intuitive and convenient. At the same time, the pressure boundary value of the first airbag is greater than the pressure boundary value of the Nth airbag, ensuring that the pressure decreases from the distal end to the proximal end, which is in line with the physiological force law of the limb.

[0039] Furthermore, in the custom mode, in response to the user's dragging operation on any node on the broken line, the pressure value change of the corresponding node is displayed in real time.

[0040] The above solution responds to the user's dragging operation on the polyline nodes in custom mode and displays the pressure value changes of the corresponding nodes in real time, providing the user with immediate visual feedback and improving the operation efficiency and user control precision in custom mode.

[0041] Furthermore, based on the target pressure value determined by the updated pressure map, inflation / deflation control is performed on each airbag, specifically including:

[0042] Based on the target pressure value of each airbag, the airbags are inflated sequentially from the distal end to the proximal end according to their serial numbers. When the pressure value of the current airbag reaches the corresponding target pressure value, the solenoid valve corresponding to that airbag is turned off, and the inflation operation is switched to the next airbag.

[0043] The above solution achieves sequential inflation of each chamber and precise independent pressure control, avoiding problems such as uneven air pressure distribution or excessive air pump load caused by simultaneous inflation of multiple airbags, and optimizing the working efficiency of the air pump.

[0044] Secondly, the present invention provides a limb compression device, comprising N airbags, wherein the N airbags are arranged sequentially along the limb from the distal end to the proximal end, wherein the first airbag corresponds to the distal end of the limb, and the Nth airbag corresponds to the proximal end of the limb, and further comprising:

[0045] The display interaction module is used to construct a pressure map on the display interface. The pressure map uses the airbag number as the horizontal axis and the pressure value as the vertical axis, and displays the pressure distribution status of each airbag in real time in the form of a broken line.

[0046] The main control module is used to respond to the user's mode selection operation, the modes including automatic gradient mode and custom mode;

[0047] In the automatic gradient mode, the user-defined first airbag pressure boundary value and the Nth airbag pressure boundary value are obtained. Based on the preset physiological attenuation algorithm, the target pressure values ​​of the 2nd to N-1th airbags are generated according to the first airbag pressure boundary value and the Nth airbag pressure boundary value. The pressure map is updated according to the first airbag pressure boundary value, the Nth airbag pressure boundary value and the target pressure values ​​of the 2nd to N-1th airbags.

[0048] In the custom mode, the user's drag operation on any node on the polyline is obtained, the position of the node in the vertical axis direction is mapped to the target pressure value of the corresponding airbag, and the pressure map is updated.

[0049] The air circuit execution module is used to perform inflation and deflation control on each airbag based on the target pressure value determined by the updated pressure spectrum.

[0050] The limb compression device provided by the above solution features a display and interaction module that constructs a pressure map in the form of a line graph on the display interface, allowing users to intuitively view the pressure distribution of all airbags. The main control module offers two control logics: automatic gradient mode and custom mode. In automatic gradient mode, users only need to set the pressure boundary values ​​for the first and last airbags. Based on a preset physiological attenuation algorithm, the target pressure values ​​for each intermediate airbag are automatically derived and the graph is updated. This simplifies multiple settings for each chamber into a single operation, significantly reducing operation steps and avoiding numerical jumps, ensuring a smooth pressure transition. In custom mode, users can directly drag the line nodes to adjust the pressure value of the corresponding airbag in real time, improving operational convenience and accuracy. At the same time, it simplifies multiple writes that require frequent refreshing of data in different page registers into a single batch write, significantly reducing system computational load and resource consumption.

[0051] Furthermore, the limb pressurization device is an air wave pressurization device for the upper or lower limbs, and the air wave pressurization device is a sleeve-type air wave pressurization device or a strap-type air wave pressurization device.

[0052] This invention is applicable to different limb parts such as arms and legs, and can be used in two mainstream structural forms: sleeve wrapping and strap wrapping, and has good versatility.

[0053] The beneficial effects of this invention are as follows: By constructing a pressure map in the form of a line graph on the display interface, this invention allows users to intuitively view the pressure distribution of each airbag and provides two switchable control logics: automatic gradient mode and custom mode. In automatic gradient mode, users only need to set the pressure boundary values ​​of the first and last airbags to automatically derive the complete chamber-by-chamber pressure gradient sequence. On the one hand, by pre-storing weight coefficients based on human anatomical data, a nonlinear pressure curve conforming to the conical anatomical structure of the limb can be generated, avoiding the discomfort caused by uniformly decreasing pressure in abrupt changes in limb shape. On the other hand, a linear interpolation algorithm provides a simpler alternative for devices with limited computing power. Both algorithms significantly reduce operation steps and avoid numerical jumps, and the smoothing correction steps further ensure the physiological rationality and safety of the pressure distribution of each airbag. In custom mode, users can directly drag and drop the map nodes to adjust the pressure value of the corresponding airbag in real time and synchronously drive the air circuit execution, improving the convenience and accuracy of operation. In addition, this invention simplifies multiple register writes to a single batch write, significantly reducing the system's computational load and resource consumption, and achieves precise independent control of each airbag through sequential inflation combined with solenoid valve switching. This invention is applicable to various limb compression devices, whether upper or lower limb, sleeve-type or strap-type, improving the operating efficiency, setting accuracy, interactive experience, system stability, and device versatility of limb compression devices. Attached Figure Description

[0054] Figure 1 A schematic diagram of the limb compression device provided in the embodiment;

[0055] Figure 2 A flowchart illustrating the control method for a limb compression device based on a visual graph, provided for an embodiment.

[0056] Figure 3 A schematic diagram of the display interface of the pressure map in the initial state provided for the embodiment;

[0057] Figure 4 A schematic diagram of the pressure map interface in automatic gradient mode provided for an embodiment;

[0058] Figure 5 This is a schematic diagram of the pressure graph interface in the custom mode provided for an embodiment. Detailed Implementation

[0059] The present invention provides a limb compression device control method and limb compression device based on a visual graph. First, a pressure graph in the form of a line graph with the airbag number as the horizontal axis and the pressure value as the vertical axis is constructed on the display interface to present the pressure distribution of each airbag in real time. Then, in response to the user's selection of automatic gradient mode or custom mode, in automatic gradient mode, the pressure boundary values ​​of the first and Nth airbags set by the user are obtained. A preset physiological attenuation algorithm automatically derives the target pressure values ​​of the 2nd to N-1th airbags based on these boundary values, and updates the pressure graph according to the target pressure values ​​of all airbags. In custom mode, the user's drag operation on the line graph node is obtained, and the position of the node in the vertical direction is mapped to the target pressure value of the corresponding airbag, updating the pressure graph. Finally, based on the target pressure values ​​determined by the updated pressure graph, inflation and deflation control is performed on each airbag.

[0060] The technical solutions in this embodiment will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments.

[0061] Figure 1 A schematic diagram of a limb compression device is shown. Please refer to [link / reference]. Figure 1 The limb compression device includes:

[0062] N airbags are arranged sequentially along the limb from the distal end to the proximal end, with the first airbag corresponding to the distal end of the limb and the Nth airbag corresponding to the proximal end of the limb. Each airbag is connected to the pneumatic execution module through an independent air passage.

[0063] The display and interaction module is used to construct a pressure graph on the display interface. The pressure graph uses the airbag number as the horizontal axis and the pressure value as the vertical axis, and displays the pressure distribution of each airbag in real time in the form of a broken line. It is also used to receive user mode selection operations, touch slider or numerical input box setting operations, and drag operations on the broken line nodes. The display and interaction module is preferably a touch screen.

[0064] The main control module, which is communicatively connected to the display interaction module, is used to respond to the user's mode selection operation. In automatic gradient mode, it generates the target pressure value of each airbag based on a preset physiological attenuation algorithm and updates the pressure map. In custom mode, it maps the vertical coordinate position of the polyline node to the target pressure value of the corresponding airbag and updates the pressure map. It is also used to generate control commands based on the target pressure value determined by the updated pressure map.

[0065] The air path execution module, which is communicatively connected to the main control module, includes an air pump, N solenoid valves, and N pressure sensors. Each of the N solenoid valves is connected to one of the N airbags, and the N pressure sensors are respectively located in each airbag or each air path. The air path execution module responds to the control commands of the main control module, performs inflation / deflation control on each airbag, monitors the pressure value of each airbag in real time, and feeds back the pressure signal to the main control module.

[0066] In this embodiment, the limb pressurization device is an air wave pressurization device for the upper or lower limbs, and the air wave pressurization device is a sleeve-type air wave pressurization device or a strap-type air wave pressurization device.

[0067] Figure 2 A flowchart illustrating a limb compression device control method based on visualization maps is shown below. Please refer to it. Figure 2 The method includes:

[0068] Step 1: Construct a pressure map on the display interface. The pressure map uses the airbag number as the horizontal axis and the pressure value as the vertical axis, and displays the pressure distribution of each airbag in real time in the form of a broken line.

[0069] Figure 3 This diagram shows the pressure graph of a 6-airbag limb compression device in its initial state. (See also...) Figure 3 A pressure graph is constructed on the touchscreen display of the interactive display module. This pressure graph uses the airbag number (Zone 1 to Zone 6 represent the 1st to 6th airbags respectively) as the horizontal axis and the pressure value (mmHg) as the vertical axis. In the initial state, the initial pressure value corresponding to each airbag can be 200mmHg, and the broken line is a horizontal straight line, indicating that all airbags are currently in the same pressure setting state.

[0070] Step 2: Responding to the user's mode selection operation, the modes include automatic gradient mode and custom mode;

[0071] In the automatic gradient mode, the user-defined first airbag pressure boundary value and the Nth airbag pressure boundary value are obtained. Based on the preset physiological attenuation algorithm, the target pressure values ​​of the 2nd to N-1th airbags are generated according to the first airbag pressure boundary value and the Nth airbag pressure boundary value. The pressure map is updated according to the first airbag pressure boundary value, the Nth airbag pressure boundary value and the target pressure values ​​of the 2nd to N-1th airbags.

[0072] In the custom mode, the user's drag operation on any node on the broken line is obtained, the position of the node in the vertical axis direction is mapped to the target pressure value of the corresponding airbag, and the pressure map is updated.

[0073] Specifically, the display interaction module provides mode switching controls, including an "Auto Gradient" button and a "Custom" button. Users can select the appropriate control mode according to their needs.

[0074] Figure 4 This diagram shows the display interface of a pressure map for a 6-airbag limb compression device in automatic gradient mode. Please refer to [link / reference]. Figure 4 When the user clicks the "Auto Gradient" button, the system enters Auto Gradient mode. In this mode, the user sets the pressure boundary values ​​for the first airbag (Zone 1) and the Nth airbag (Zone 6) via the touch slider or numerical input box on the display interface. After obtaining these two boundary values, the main control module calls the preset physiological attenuation algorithm to automatically calculate the target pressure values ​​for the 2nd to N-1th airbags (i.e., Zones 2 to 5). After the calculation is completed, the main control module updates the pressure map based on the pressure boundary values ​​of the first airbag, the Nth airbag, and the target pressure values ​​of the 2nd to N-1th airbags.

[0075] When the user sets the first and last boundary values, the first airbag pressure boundary value must be greater than the Nth airbag pressure boundary value. If this is not met, a reasonable decreasing pressure sequence cannot be generated, and the system will prompt the user to reset it to ensure that the distal pressure is greater than the proximal pressure, avoid pressure inversion, and prevent unreasonable pressure distribution caused by user misoperation.

[0076] In this embodiment, the preset physiological attenuation algorithm can use the weighting coefficient method to calculate the target pressure value of the intermediate airbag in automatic gradient mode, including:

[0077] Call the pre-stored weight coefficients Where i is the airbag number, i∈[1,N], and N is the total number of airbags. The trend decreases as the airbag serial number i increases, and The weighting coefficients Based on pre-stored human anatomical data, the weights are used to characterize the influence of limb taper changes from distal to proximal on external vascular pressure.

[0078] The target pressure value of the i-th airbag is calculated using the following formula. :

[0079] ;

[0080] in, This is the first airbag pressure boundary value. This represents the Nth airbag pressure boundary value.

[0081] Specifically, the human limb has a cone shape that gradually thickens from the distal end to the proximal end. The rate of change of circumference and soft tissue density differ in different segments. The distal end of the limb has a stronger tolerance to pressure, while the proximal end has a weaker tolerance to pressure. Therefore, the pressure value of each airbag should have a non-linear decreasing distribution from the distal end to the proximal end, which conforms to the anatomical shape of the limb.

[0082] Therefore, in this embodiment, the system pre-stores a set of weighting coefficients based on human anatomical data. This weighting coefficient is used to characterize the influence of the limb's conical change from distal to proximal on pressure. In practical applications, the main control module calls the pre-stored weighting coefficient. And based on the pressure boundary value of the first airbag set by the user. and the pressure boundary value of the Nth airbag Calculate the target pressure value of each airbag in the middle. .

[0083] The aforementioned scheme automatically increases the pressure reduction amplitude in sections where the limb circumference changes rapidly and decreases it in sections where the circumference change is gradual, based on the tapering variation of the limb from distal to proximal. This generates a smooth, non-linear pressure curve that conforms to the human body's tapering anatomy, avoiding the discomfort caused by uniform pressure reduction in sections where the limb shape changes abruptly. Furthermore, multiple sets of different weight coefficient templates can be preset for different application scenarios (such as arms and legs, rehabilitation and sports recovery). The system can incrementally adjust each weight coefficient based on feedback data collected during actual use, gradually approximating the personalized optimal configuration for a specific user. Users only need to set the first and last boundary values ​​to automatically derive the complete chamber-by-chamber pressure gradient sequence, thereby improving operational convenience and the accuracy of setting pressure values.

[0084] Based on the weighted coefficient method, this embodiment calculates the target pressure value for each airbag. Following this, a smoothing correction step is also included:

[0085] Calculate the pressure difference between adjacent airbags : ;

[0086] If the pressure difference Exceeding the preset maximum differential pressure threshold Then the target pressure value will be automatically reverted. Until satisfied .

[0087] Among them, the maximum differential pressure threshold It can be set to 30 mmHg to ensure that there is no excessive pressure difference between adjacent airbags, which would cause local compression of the limbs. While ensuring the user's comfort, it provides sufficient safety redundancy for the airbag pressure values ​​generated in automatic gradient mode.

[0088] Specifically, the weighted coefficient method pre-stores weighted coefficients based on the general principles of human anatomy. However, there are individual differences in limb shape, soft tissue density, and pressure tolerance among different users. The initial pressure sequence generated by a fixed set of weighted coefficients may produce a large pressure difference between some adjacent airbags. If this difference exceeds the user's tolerance range, it will create an excessive pressure gradient in the local area of ​​the limb, causing discomfort.

[0089] This embodiment introduces a first-order differential check as a safety constraint based on the calculation results of the weighted coefficient method through a smoothing correction step. By limiting the upper limit of the pressure difference between any two adjacent airbags, it ensures that the entire pressure curve meets safety requirements. Simultaneously, this correction mechanism preserves the non-linear decreasing trend generated by the weighted coefficient method, only performing moderate corrections at local threshold exceedances to avoid over-correction that could damage the gradient characteristics of the original algorithm.

[0090] Through the aforementioned smoothing correction steps, the problem of excessive local pressure differences in the initial calculation results of the weighted coefficient method can be automatically identified and eliminated, controlling the pressure difference between any adjacent airbags within a preset safety threshold. This correction mechanism, while preserving the nonlinear decreasing pressure curve generated by the weighted coefficient method, ensures that the pressure of each airbag decreases from the distal to the proximal end in a manner consistent with limb anatomy through the weighted coefficient, and also ensures the smoothness and safety of adjacent pressure changes through differential verification, effectively avoiding discomfort to the user caused by excessive local pressure differences.

[0091] In this embodiment, the preset physiological attenuation algorithm can also use a linear interpolation algorithm to calculate the target pressure value of the intermediate airbag in automatic gradient mode, including:

[0092] Calculate the segment spacing k using the following formula:

[0093] ;

[0094] The target pressure value of the i-th airbag is calculated using the following formula. :

[0095] ;

[0096] Where i is the airbag number, i∈[1,N], and N is the total number of airbags. This is the first airbag pressure boundary value. This represents the Nth airbag pressure boundary value.

[0097] Specifically, the linear interpolation algorithm assumes that the pressure values ​​of each airbag decrease uniformly from the distal to the proximal end. In practical applications, it will... and The total pressure difference between airbags is divided equally according to the number of airbag intervals, keeping the pressure difference between adjacent airbags constant, thus generating a pressure sequence that decreases arithmetically. The linear interpolation algorithm can generate a complete chamber-by-chamber pressure gradient sequence through simple arithmetic mean calculation. Compared with the weighted coefficient method, it does not require pre-stored weighted coefficient templates, making the algorithm simpler and less computationally complex. It is suitable for devices with low computational resource requirements to achieve automatic pressure derivation in automatic gradient mode.

[0098] Please see Figure 4 The user sets the pressure boundary value for the first airbag (Zone 1). Set the pressure boundary value of the 6th airbag (Zone 6) to 125 mmHg. The target pressure is set to 65 mmHg. After receiving the above first and last boundary values, the main control module uses a linear interpolation algorithm to calculate the target pressure values ​​of each airbag in the middle and updates the map: the target pressure value of the second airbag (Zone2) is 113 mmHg, the target pressure value of the third airbag (Zone3) is 101 mmHg, the target pressure value of the fourth airbag (Zone4) is 89 mmHg, and the target pressure value of the fifth airbag (Zone5) is 77 mmHg.

[0099] Figure 5 This diagram shows the display interface of a pressure graph for a 6-airbag limb compression device in custom mode. Please refer to [link / reference]. Figure 5 When the user clicks the "Customize" button, the system enters custom mode. In this mode, the display shows six line nodes corresponding to the six airbags in the pressure graph. Each node is initially located at the currently stored pressure value. The user can drag any node in the graph (e.g., the node corresponding to Zone2) by pressing and holding it with their finger or stylus. The system captures the displacement of this drag operation in the vertical axis in real time, converts the displacement into the corresponding pressure adjustment value, and updates the target pressure value of the Zone2 airbag according to the pressure adjustment value (e.g., from 125 mmHg to 75 mmHg). At the same time, the line shape of the pressure graph is refreshed in real time, and control commands are issued synchronously to make the corresponding airbag reach the adjusted target pressure value. The pressure values ​​of each node are displayed synchronously during the dragging process.

[0100] Step 3: Based on the target pressure value determined by the updated pressure map, perform inflation / deflation control on each airbag.

[0101] In this embodiment, step 3 specifically includes:

[0102] Based on the target pressure value of each airbag, the airbags are inflated sequentially from the distal end to the proximal end according to their serial numbers. When the pressure value of the current airbag reaches the corresponding target pressure value, the solenoid valve corresponding to that airbag is turned off, and the inflation operation is switched to the next airbag.

[0103] In practical applications, after the main control module determines the target pressure value of each airbag based on the updated pressure spectrum, it generates the corresponding control command and sends it to the air path execution module. The air path execution module responds to the control command and performs inflation and deflation control on each airbag.

[0104] Because each airbag has a different target pressure value, and the airbags are arranged sequentially along the limb from distal to proximal, if all airbags are inflated simultaneously, the air pump's output volume is distributed across multiple air paths, which may lead to inconsistent pressure rise rates or uneven pressure distribution among the airbags, making it difficult to ensure that each airbag accurately reaches its target pressure value. Therefore, this embodiment adopts a chamber-by-chamber sequential inflation method. By controlling the timing of the solenoid valves, the air pump inflates only one airbag at a time, avoiding the problem of uneven pressure distribution. Simultaneously, pressure sensors are installed in each airbag or air path to monitor the pressure value of each airbag in real time and feed the pressure signal back to the main control module to ensure inflation accuracy.

[0105] In summary, the limb compression device control method and device provided in this embodiment, by constructing a pressure map in the form of a line graph on the display interface, allow users to intuitively view the pressure distribution of each airbag. It also provides two switchable control logics: automatic gradient mode and custom mode, significantly improving operational efficiency and setting accuracy. In automatic gradient mode, users only need to set the pressure boundary values ​​of the first and last airbags. Based on a preset physiological attenuation algorithm, the target pressure values ​​of each intermediate airbag are automatically derived, simplifying the multiple settings for each chamber into a one-time operation of setting only the first and last values, reducing the number of operation steps by more than 70%. Simultaneously, a weighting coefficient algorithm ensures that the pressure values ​​of each airbag decrease smoothly from the distal to the proximal end, conforming to the cone-shaped anatomical structure of the limb, avoiding numerical abrupt changes or inversions caused by manual input. Combined with a smoothing correction step, it further eliminates the risk of excessive local pressure differences, balancing setting accuracy and usage safety. In custom mode, users can directly drag and drop graph nodes to adjust the pressure values ​​of the corresponding airbags in real time and synchronously drive the airway execution, achieving a "what you see is what you get" single-screen interaction without needing to jump to a separate page for confirmation, further improving operational efficiency and user experience. Furthermore, this embodiment simplifies the multiple write operations that originally required frequent refreshing of different page register data into a single batch write by using a single-screen overview and automatic generation logic. This significantly reduces the computational load of the embedded system, reduces the risk of system lag and crashes, and improves the stability of the device under high-load continuous operation.

Claims

1. A control method for limb compression devices based on visual atlases, characterized in that, The limb compression device includes N airbags, which are arranged sequentially along the limb from the distal end to the proximal end, wherein the first airbag corresponds to the distal end of the limb, and the Nth airbag corresponds to the proximal end of the limb; the method includes: A pressure map is constructed on the display interface. The pressure map uses the airbag number as the horizontal axis and the pressure value as the vertical axis, and displays the pressure distribution of each airbag in real time in the form of a broken line. In response to a user's mode selection action, the modes include automatic gradient mode and custom mode; In the automatic gradient mode, the user-defined first airbag pressure boundary value and the Nth airbag pressure boundary value are obtained. Based on the preset physiological attenuation algorithm, the target pressure values ​​of the 2nd to N-1th airbags are generated according to the first airbag pressure boundary value and the Nth airbag pressure boundary value. The pressure map is updated according to the first airbag pressure boundary value, the Nth airbag pressure boundary value and the target pressure values ​​of the 2nd to N-1th airbags. In the custom mode, the user's drag operation on any node on the polyline is obtained, the position of the node in the vertical axis direction is mapped to the target pressure value of the corresponding airbag, and the pressure map is updated. Inflation and deflation control is performed on each airbag based on the target pressure value determined by the updated pressure map.

2. The limb compression device control method based on visualization map according to claim 1, characterized in that, The preset physiological attenuation algorithm includes: Call the pre-stored weight coefficients Where i is the airbag number, i∈[1,N], and N is the total number of airbags. The trend decreases as the airbag serial number i increases, and The weighting coefficients Based on pre-stored human anatomical data, the weights are used to characterize the influence of limb taper changes from distal to proximal on external vascular pressure. The target pressure value of the i-th airbag is calculated using the following formula. : ； in, This is the first airbag pressure boundary value. This represents the Nth airbag pressure boundary value.

3. The limb compression device control method based on visualization map according to claim 2, characterized in that, After calculating the target pressure value of the i-th airbag Following this, a smoothing correction step is also included: Calculate the pressure difference between adjacent airbags : ; If the pressure difference Exceeding the preset maximum differential pressure threshold Then the target pressure value will be automatically reverted. Until satisfied .

4. The limb compression device control method based on visualization map according to claim 3, characterized in that, The maximum differential pressure threshold The blood pressure is 30 mmHg.

5. The limb compression device control method based on visualization map according to claim 1, characterized in that, The preset physiological attenuation algorithm includes: Calculate the segment spacing k using the following formula: ； The target pressure value of the i-th airbag is calculated using the following formula. : ； Where i is the airbag number, i∈[1,N], and N is the total number of airbags. This is the first airbag pressure boundary value. This represents the Nth airbag pressure boundary value.

6. The limb compression device control method based on visualization map according to claim 1, characterized in that, In the automatic gradient mode, the user-set first airbag pressure boundary value and Nth airbag pressure boundary value are obtained through the touch slider or numerical input box on the display interface, and the first airbag pressure boundary value is greater than the Nth airbag pressure boundary value.

7. The limb compression device control method based on visualization map according to claim 1, characterized in that, In the custom mode, in response to the user's drag operation on any node on the fold line, the pressure value change of the corresponding node is displayed in real time.

8. The limb compression device control method based on visualization map according to claim 1, characterized in that, Based on the target pressure value determined by the updated pressure map, inflation / deflation control is performed on each airbag, specifically including: Based on the target pressure value of each airbag, the airbags are inflated sequentially from the distal end to the proximal end according to their serial numbers. When the pressure value of the current airbag reaches the corresponding target pressure value, the solenoid valve corresponding to that airbag is turned off, and the inflation operation is switched to the next airbag.

9. A limb compression device, characterized in that, It includes N airbags, which are arranged sequentially along the limb from the distal end to the proximal end, wherein the first airbag corresponds to the distal end of the limb, the Nth airbag corresponds to the proximal end of the limb, and it also includes: The display interaction module is used to construct a pressure map on the display interface. The pressure map uses the airbag number as the horizontal axis and the pressure value as the vertical axis, and displays the pressure distribution status of each airbag in real time in the form of a broken line. The main control module is used to respond to the user's mode selection operation, the modes including automatic gradient mode and custom mode; In the automatic gradient mode, the user-defined first airbag pressure boundary value and the Nth airbag pressure boundary value are obtained. Based on the preset physiological attenuation algorithm, the target pressure values ​​of the 2nd to N-1th airbags are generated according to the first airbag pressure boundary value and the Nth airbag pressure boundary value. The pressure map is updated according to the first airbag pressure boundary value, the Nth airbag pressure boundary value and the target pressure values ​​of the 2nd to N-1th airbags. In the custom mode, the user's drag operation on any node on the polyline is obtained, the position of the node in the vertical axis direction is mapped to the target pressure value of the corresponding airbag, and the pressure map is updated. The air circuit execution module is used to perform inflation and deflation control on each airbag based on the target pressure value determined by the updated pressure spectrum.

10. The limb compression device according to claim 9, characterized in that, The limb compression device is an air wave compression device for the upper or lower limbs, and the air wave compression device is a sleeve-type air wave compression device or a strap-type air wave compression device.

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