Intra-abdominal pressure measurement system and method

Abstract

The present invention relates to an intra-abdominal pressure measurement system and method, the system comprises: a three-way pipe; a first pipeline is configured to correct abnormal values ​​in the first bladder pressure measurement in a manner of averaging the urine production rates in at least two adjacent time periods based on the patient's urine production rate in several time periods; a third pipeline; wherein the fluid balance detection structure in the third pipeline balances the fluid pressure and uses the balanced pressure as a baseline to obtain continuous bladder pressure change data for bladder pressure correction. The three-way pipe provided in the present invention integrates a variety of measurement methods, which can be adaptively selected based on the patient's current physical signs, and a variety of measurement methods can be combined to measure a more accurate patient's bladder pressure, and the measurement method of the third pipeline is continuous, so that the patient does not need to perform multiple intra-bladder fluid injections, and the patient's intra-abdominal pressure changes can be detected in real time to ensure the best time for rescue.

Description

Technical Field

[0001] The present invention relates to the technical field of intra-abdominal pressure, and particularly to an intra-abdominal pressure measurement system and method. Background Art

[0002] In the prior art, a single and simple measurement method is often used to calculate the bladder pressure of a patient. The method of observing the bladder pressure by injecting normal saline and then observing the height of the water column can only perform intermittent pressure measurement, and repeated injection brings great pain and the risk of infection to the patient. This method is both time-consuming and has the risk of bladder infection, because when injecting saline, the closed sterile tube may be contaminated due to the insertion of the needle. In many cases, the bladder pressure of the patient should not be measured in this way.

[0003] Chinese Patent CN105559769B discloses a method and device for reflecting intra-abdominal pressure by measuring the pressure in the bladder, including the following steps: 1) empty the liquid in the bladder; 2) measure the amount of urine produced in the bladder per unit time to obtain the urine production rate; 3) calculate the time required for the cumulative amount of urine in the bladder to reach 50 milliliters and start timing; 4) after the timing is completed, measure the bladder pressure and convert it into intra-abdominal pressure; 5) repeat the above steps to complete periodic measurement; it also includes a urinary catheter, a urine volume measurement device, a bladder pressure measurement device, a main control board, a display screen, and a controller. The urinary catheter is respectively connected to the urine volume measurement device and the bladder pressure measurement device. The urine volume measurement device includes an outlet urine solenoid valve, a drainage bag, and a weighing sensor. The bladder pressure measurement device includes a Luer cock valve and a pressure sensor. The defect of this patent is that the intra-abdominal pressure measurement method has a large error and cannot continuously measure the intra-abdominal pressure, and each measurement will cause pain to the patient.

[0004] In addition, on the one hand, there are differences in the understanding of those skilled in the art; on the other hand, although the inventor studied a large number of literatures and patents when making the present invention, all details and contents are not listed in detail due to space limitations. However, this does not mean that the present invention does not possess the features of these prior arts. On the contrary, the present invention already possesses all the features of the prior arts, and the applicant reserves the right to add relevant prior arts in the background art. Summary of the Invention

[0005] In view of the deficiencies of the prior art, the technical solution of the present invention is to provide an intra-abdominal pressure measurement system, which at least includes: a three-way tube; the three-way tube includes: a first pipeline, a third pipeline and a control module, wherein the control module obtains a first bladder pressure in the first pipeline by measuring the urine production speed in the patient's bladder; the control module obtains a third bladder pressure in the third pipeline by measuring the change in the fluid pressure in the airbag; the control module is further configured to: based on the urine production speed of the patient in several time periods, correct the abnormal value in the first bladder pressure measurement by averaging the urine production speeds in at least two adjacent time periods; the fluid balance detection structure in the third pipeline balances the fluid pressure and uses the balanced pressure as a reference line to obtain continuous bladder pressure change data for bladder pressure correction. The first pipeline is provided so that the contents in the patient's bladder can be the fluid produced by the patient himself, rather than the fluid injected from the outside, so as to ensure that the measured intra-abdominal pressure is accurate enough. The present invention measures the weight of the urine drained from the patient's bladder within a period of time (that is, obtains the volume size), so as to obtain the urine production speed of the patient. To ensure the accuracy of the measured bladder pressure, it is necessary to accurately obtain the volume of urine in the patient's bladder, that is, accurately obtain the urine production speed in the patient's bladder. The time period is not limited to the calculation of the urine production speed within a single time period, and the urine production speeds in several adjacent time periods can also be calculated to reduce abnormal values.

[0006] According to a preferred embodiment, the method of averaging the urine production speeds in at least two adjacent time periods means: taking the current moment as the starting measurement time point T1, and the following N moments as the ending measurement time points Tn, then the urine production speed of the patient in this time period = (urine weight at the following N moments - urine weight at the current moment) / (Tn - T1), and the continuity of the calculated urine production speed of the patient in this time period is averaged with other urine production speeds again, and the obtained final urine production speed is used as the actual urine production speed of the patient. After all values are measured, the obtained final urine production speed can be used as the actual urine production speed of the patient. Preferably, the actual urine production speed of the patient can also be subjected to standard deviation normalization processing of the urine production speeds in the above-mentioned several time periods to reduce the occurrence of abnormal values.

[0007] According to a preferred embodiment, the control module calculates the time required for the patient's bladder to produce a certain amount of urine based on the actual urine production speed of the patient. After the urine in the patient's bladder is emptied, the control module starts timing and stops after reaching the calculated required time, and sends the measured bladder pressure to the control module through the pressure sensor provided in the first pipeline. A certain amount of urine can be set to 50 ml. This method is simple to operate, reduces the pain of the patient, avoids infection of the patient, and is convenient for further understanding the patient's condition.

[0008] According to a preferred embodiment, the third pipeline is connected to a balance component for fluid balance. The balance component at least includes an injection valve, a syringe, a balance chamber, and a spring chamber. The balance chamber is communicated with the third pipeline. The syringe injects fluid into the airbag through the injection valve, the balance chamber, and the third pipeline. The third pipeline is used to promote the fluid communication between the airbag and the balance component. The continuous or periodic change of the fluid pressure in the airbag can be detected through fluid balance. The setting of the third pipeline is intended to be able to measure accurate patient bladder pressure data through the change of the fluid pressure in the airbag. The detection of the patient's bladder pressure lies in that when the patient's bladder pressure changes, the pressure applied to the airbag is changed. If the pressure received by the airbag increases, the airbag compresses, resulting in an increase in the pressure in the fluid balance detection structure. If the pressure received by the airbag decreases, the airbag expands, resulting in a decrease in the pressure in the fluid balance detection structure. This pressure can be continuously detected by a pressure sensor. The change of the airbag pressure completely depends on the change of the patient's intra-abdominal pressure and has nothing to do with any other pressure sources of the components in this device. The pressure sensor sends the detected pressure change to the control module to obtain the change of the bladder pressure change over time, and finally obtain accurate patient bladder pressure data.

[0009] According to a preferred embodiment, the system further includes a valve assembly. The airbag is arranged at one end of the tee that needs to be inserted into the patient's bladder, and the valve assembly is arranged at the end of the tee away from the patient's bladder part. Wherein, the tee is internally provided with an inner pipe and an outer pipe that are spaced apart inside and outside. The inner pipe is nested into the outer pipe and has the same central axis as the outer pipe. The outer pipe and the inner pipe are connected at one end inside the patient's bladder, and the outer pipe is provided with a circumferential opening communicated with the airbag. The inner pipe extends out of the outer pipe and is provided with an opening communicated with the patient's bladder. The airbag is configured to be an airbag that is close to the patient's bladder wall and only communicated with the outer pipe. The airbag measures the change of the patient's intra-abdominal pressure in real time and continuously through the change of its own internal fluid pressure.

[0010] According to a preferred embodiment, the inner pipe is configured to drain the internal fluid from the patient's bladder and to inject fluid into the patient's bladder. The end of the inner pipe away from the patient's bladder is connected with the valve assembly. Wherein, the valve assembly is communicated with the first pipeline and the second pipeline, and the valve assembly can switch between the inner pipe being communicated with the first pipeline and the inner pipe being communicated with the second pipeline. The closed design of the first pipeline and the second pipeline can prevent the patient's urine from contaminating the fluid injected into the patient's body.

[0011] According to a preferred embodiment, the second pipeline is configured to calculate the second bladder pressure based on the set measurement mark through the water column height. When the first bladder pressure, the second bladder pressure, and the third bladder pressure are calculated, the actual bladder pressure of the patient can be calculated according to the weight ratio of the measured bladder pressures. The three-way pipe provided in the present invention integrates multiple measurement methods, which can be adaptively selected based on the current physical signs of the patient, and multiple measurement methods can be combined to measure a more accurate bladder pressure of the patient. Moreover, the measurement method of the third pipeline has continuity, so that the patient does not need to perform multiple intravesical fluid injections, and the change of the patient's intra-abdominal pressure can be detected in real time to ensure the best rescue time.

[0012] The present invention also relates to an intra-abdominal pressure measurement method, which at least includes: correcting the abnormal value in the first bladder pressure measurement based on the urine production rate of the patient within several time periods by averaging the urine production rates in at least two adjacent time periods; calculating the third bladder pressure based on the change in the fluid pressure in the airbag; wherein, the fluid balance detection structure balances the fluid pressure and uses the balanced pressure as a reference line to obtain continuous bladder pressure change data for correcting the bladder pressure.

[0013] According to a preferred embodiment, the method of averaging the urine production rates in at least two adjacent time periods means: taking the current moment as the starting measurement time point T1 and the next N moments as the ending measurement time point Tn, then the urine production rate of the patient within this time period = (urine weight at the next N moments - urine weight at the current moment) / (Tn - T1), and the continuity of the calculated urine production rate of the patient within this time period is averaged again with other urine production rates to obtain the final urine production rate as the actual urine production rate of the patient.

[0014] According to a preferred embodiment, the method further includes: calculating the second bladder pressure based on the set measurement mark through the water column height. When the first bladder pressure, the second bladder pressure, and the third bladder pressure are calculated, the actual bladder pressure of the patient can be calculated according to the weight ratio of the measured bladder pressures.

[0015] The beneficial technical effects of the present invention:

[0016] (1) The measurements of the first bladder pressure, the second bladder pressure, and the third bladder pressure of the present invention can be respectively used for the requirements in different situations. In the prior art, a single and simple measurement method is often used to calculate the bladder pressure of a patient. The method of injecting normal saline and then observing the bladder pressure through the height of the water column can only perform intermittent pressure measurement, and repeated injections bring great pain and the risk of infection to the patient. In many cases, the bladder pressure measurement of the patient should not be carried out in this way. The three-way tube provided by the present invention integrates a variety of measurement methods, which can be adaptively selected based on the current physical signs of the patient, and a variety of measurement methods can be combined to measure a more accurate bladder pressure of the patient. Moreover, the measurement method of the third pipeline has continuity, enabling the patient to avoid multiple injections of fluid into the bladder, real-time detecting the change of the intra-abdominal pressure of the patient, and ensuring the best rescue time. The measurement method of the third pipeline can also be used for further calibration of the first bladder pressure and / or the second bladder pressure measured by the first pipeline and / or the second pipeline. This undoubtedly greatly improves the accuracy of the calculation, thereby reducing the possible measurement error;

[0017] (2) The present invention optimizes the calculation of the urine production rate in the patient's bladder. The bladder pressure is the magnitude of the bladder pressure when a certain volume of urine is produced in the patient's bladder. To ensure the accuracy of the measured bladder pressure, it is necessary to accurately obtain the volume of urine in the patient's bladder, that is, accurately obtain the urine production rate in the patient's bladder. The present invention reduces the outliers by continuous calculation and through the urine production rate in adjacent time periods, and the finally obtained actual urine production rate of the patient greatly reduces the measurement error, and the calculated bladder pressure is more accurate. Description of the Drawings

[0018] Figure 1 is a schematic structural diagram of a preferred embodiment of the first pipeline of an intra-abdominal pressure measurement system of the present invention;

[0019] Figure 2 is a schematic structural diagram of a preferred embodiment of the second pipeline of an intra-abdominal pressure measurement system of the present invention;

[0020] Figure 3 is a schematic structural diagram of a preferred embodiment of the third pipeline of an intra-abdominal pressure measurement system of the present invention.

[0021] List of Reference Numerals

[0022] 1: Three-way tube; 2: Airbag; 3: Valve assembly; 4: First pipeline; 5: Second pipeline; 6: Third pipeline; 7: Balance assembly; 8: Detection module; 101: Inner tube; 102: Outer tube; 601: First valve; 701: Injection valve; 702: Syringe; 703: Balance cavity; 704: Spring cavity; 801: Pressure sensor; 802: Second valve; 803: Filter. Detailed Embodiments

[0023] The following is a detailed description with reference to the accompanying drawings.

[0024] First, the professional terms mentioned in the present invention are described.

[0025] Control module: Any type of computer or processing system, including but not limited to mobile terminals, personal computers (PCs), personal digital assistants (PDAs), mainframe computers, network devices, systems having a database capable of storing and processing patient information, or other devices or combinations of devices. It is widely defined to cover any device or combination of devices having at least one processor that executes instructions from a storage medium.

[0026] Embodiment 1

[0027] This application relates to an intra-abdominal pressure measurement system, which at least includes a three-way tube 1, an airbag 2, and a valve assembly 3. The airbag 2 is disposed at one end of the three-way tube 1 that needs to be inserted into the patient's bladder, and the valve assembly 3 is disposed at one end of the three-way tube 1 away from the patient's bladder part. Among them, the three-way tube 1 is internally provided with an inner tube 101 and an outer tube 102 that are spaced apart from each other. The inner tube is nested in the outer tube 102 and has the same central axis as the outer tube 102. The outer tube 102 is connected to the inner tube 101 at one end inside the patient's bladder, and the outer tube 102 is provided with a circumferential opening communicating with the airbag 2. The inner tube 101 extends out of the outer tube 102 and is provided with an opening communicating with the patient's bladder. The airbag 2 is configured as a spherical airbag that is close to the patient's bladder wall and only communicates with the outer tube 102. The airbag 2 can continuously and real-time measure the change of the patient's intra-abdominal pressure according to the change of the internal fluid pressure of itself. It should be noted that the above-mentioned fluid can be gas, liquid, or other fluid media that can reflect pressure changes.

[0028] According to a preferred embodiment, the inner tube 101 of the three-way tube 1 is configured to drain the internal fluid from the patient's bladder and to inject fluid into the patient's bladder. Among them, the drained fluid can be the patient's urine, and the fluid injected into the patient's bladder can be sterile normal saline. One end of the inner tube 101 away from the patient's bladder is connected to the valve assembly 3. The valve assembly 3 communicates with a first pipeline 4 and a second pipeline 5. The first pipeline 4 is used to drain and empty the urine in the patient's bladder. The second pipeline 5 is used to inject fluid into the patient's bladder to measure the patient's bladder pressure. The valve assembly 3 can switch between the inner tube 101 communicating with the first pipeline 4 and the inner tube 101 communicating with the second pipeline 5.

[0029] According to a preferred embodiment, one end of the outer tube 102 away from the patient's bladder is connected to a third pipeline 6. The third pipeline 6 is connected to a balance assembly 7 for fluid balance. The balance assembly 7 may include an injection valve 701, a syringe 702, a balance chamber 703, and a spring chamber 704. The balance chamber 703 communicates with the third pipeline 6. The syringe 702 injects fluid into the airbag 2 through the injection valve 701, the balance chamber 703, and the third pipeline 6. The third pipeline 6 is used to promote fluid communication between the airbag 2 and the balance assembly 7. A first valve 601 for controlling fluid connection is also provided at the connection part between the third pipeline 6 and the balance chamber 703. The continuity or periodic change of the fluid pressure in the airbag 2 can be detected through fluid balance.

[0030] According to a preferred embodiment, the other end of the balance chamber 703 away from the third pipeline 6 is connected to a detection module 8 for measuring and / or detecting pressure changes in the fluid balance structure composed of the airbag 2, the third pipeline 6, and the balance assembly 7. The detection module 8 at least includes a pressure sensor 801, a second valve 802, and a filter 803.

[0031] Embodiment 2

[0032] This embodiment is a further supplement to the above embodiment, and repeated content will not be elaborated.

[0033] The setting of the first pipeline 4 is such that the contents in the patient's bladder can be the fluid produced by the patient himself, rather than the fluid injected from the outside, so as to ensure that the measured intra-abdominal pressure is accurate enough.

[0034] According to a preferred embodiment, the valve assembly 3 connects the inner tube 101 to the first pipeline 4. After the control module calculates the speed of urine production in the patient's bladder, it then calculates the time required to produce 50 ml of urine in the bladder. After the urine in the patient's bladder is emptied, the control module starts timing and stops after reaching the calculated time required to produce 50 ml of urine, and sends the measured bladder pressure to the control module through the pressure sensor provided in the first pipeline 4. The control module converts the received bladder pressure into intra-abdominal pressure.

[0035] According to a preferred embodiment, the present invention weighs and detects the amount of urine drained from the patient's bladder within a period of time (i.e., obtains the volume size), so as to obtain the urine production speed of the patient. The present invention is provided with a urine drainage bag for placing the drained urine, and the weight sensor sends the urine weight to the control module, and the control module receives and calculates the data.

[0036] According to a preferred embodiment, the present invention can optimize the method for detecting bladder pressure of the first pipeline 4. Specifically, the present invention optimizes the calculation of the urine production speed in the patient's bladder. The bladder pressure is the magnitude of the bladder pressure when a certain volume of urine is produced in the patient's bladder. To ensure the accuracy of the measured bladder pressure, it is necessary to accurately obtain the volume of urine in the patient's bladder, that is, to accurately obtain the speed of urine production in the patient's bladder. In the above embodiment, by calculating the average speed of the patient's urine production, the time required for the patient to produce 50 ml of urine is deduced to calculate the bladder pressure. However, since the patient's urine production speed is in a state of real-time change, simply using the ratio of the total urine volume and time is difficult to represent the actual urine production speed of the patient, resulting in inaccurate measurement of the final bladder pressure, and further inaccurate measurement of the intra-abdominal pressure. In response to this, the present invention performs a calibrated calculation on the detected urine production speed to obtain the actual urine production speed of the patient. Specifically, the present invention is provided with a urine drainage bag and a weight sensor. The position of the urine drainage bag and the weight sensor is not overly limited. The weight sensor can detect the weight change in the urine drainage bag. The weight sensor can be a hook type, and the weight change in the urine drainage bag is obtained by hanging the urine drainage bag. The weight sensor can be a platform type, and the weight change in the urine drainage bag is obtained by holding up the urine drainage bag. The weight sensor sends the weight change data to the control module. Among them, the control module matches the weight change data based on the time axis to obtain the actual urine production speed of the patient. The control module is in the process of continuously calculating the urine production speed. After obtaining the urine production speed of the patient at the previous moment, taking the current moment as the starting measurement time point T1 and the next moment as the ending measurement time point T2, then the urine production speed of the patient within this time period = (urine weight at the next moment - urine weight at the current moment) / (T2 - T1). By continuously and periodically performing the above steps, the urine production speed of the patient in each time period can be obtained. Preferably, the above time period is not limited to the calculation of the urine production speed within a single time period, and the urine production speed in several adjacent time periods can also be calculated to reduce outliers. For example, taking the current moment as the starting measurement time point T1 and the next N moments as the ending measurement time point Tn, then the urine production speed of the patient within this time period = (urine weight at the next N moments - urine weight at the current moment) / (Tn - T1). After obtaining the urine production speed in the above several time periods, by respectively taking their averages, the actual urine production speed of the patient can be calculated. Specifically, by averaging the urine production speed in a certain time period calculated and the urine production speed in another time period or the urine production speed in another time period including a certain time period, and continuously averaging the averaged value with other urine production speeds again. After all values are measured, the final urine production speed obtained can be used as the actual urine production speed of the patient.Preferably, the actual urine production rate of the patient can also be normalized by standard deviation for the urine production rates in the above-mentioned several time periods to reduce the occurrence of outliers. Standard deviation normalization means calculating the mean μ (which can be calculated by the above mean method) and the standard deviation σ of the urine production rates in several time periods, and then standardizing the urine production rate in each time period to standardize the data set of the urine production rate, so as to conform to the standard normal distribution and reduce the influence of outliers on the final calculation result. The standardization calculation formula is:

[0037]

[0038]

[0039]

[0040] Among them, n represents the number of time periods, i represents the current moment, v represents the urine production rate, and v' represents the urine production rate after standard deviation normalization.

[0041] Standard deviation normalization is used in many fields. That is, first, the present application does not aim to improve the standard deviation normalization process belonging to the prior art. Second, those skilled in the art can select the standard deviation normalization process according to actual needs. Third, for the sake of brevity, the present application will not elaborate on the specific steps of standard deviation normalization.

[0042] According to a preferred embodiment, after measuring the actual urine production rate of the patient, it can be stored as a data buffer for the reference data of the next measurement of the bladder pressure of the same patient. This reference data can provide basic data for the next bladder pressure measurement of the patient, thus saving the data processing amount. Preferably, the control module can respond to this reference data. For example, when the patient performs multiple bladder pressure measurements in a short period of time, there is too much data to be calculated and processed, but the final results obtained have little deviation, thus wasting the computing power of the control module. In this regard, when the control module detects the bladder pressure of the same patient in a short period of time, it can increase the time period T1, thereby reducing the data processing amount. The reduced data processing amount can be directly used for the first or long-term bladder pressure measurement of different patients, that is, by shortening the time period T1, accurate bladder pressure measurement can be achieved, the time density of the measurement can be improved, and it is beneficial to improve the accuracy of the patient's bladder pressure.

[0043] It should be noted that the above outliers refer to the urine production rate calculated after a large measurement error occurs. Among them, the time period between two adjacent moments can be adjusted according to the calculation efficiency of the control module and / or the accuracy of the intra-abdominal pressure to be measured. It can be understood that the shorter this time period is, the more accurate the patient's urine production rate obtained is, that is, the calculated bladder pressure and intra-abdominal pressure are more accurate.

[0044] It should be noted that the present invention is not limited to the above embodiments, and various modified embodiments can also be adopted. For example, the present invention can calibrate the actual urine production rate of the patient through the above several urine production rates.

[0045] In the present invention, the bladder pressure obtained through the above embodiment is set as the first bladder pressure.

[0046] Embodiment 3

[0047] This embodiment is a further supplement to the above embodiment, and the repeated content will not be elaborated.

[0048] The setting of the second pipeline 5 is a secondary detection method to be adopted when the measurement conditions are simple and the most accurate detection tools are not available in various complex scenarios.

[0049] According to a preferred implementation manner, the second pipeline 5 is communicated with the atmosphere. The second pipeline 5 is set as a manometer tube, which includes a series of measurement marks. The above measurement marks can use the scale cmH 2 O or mmHg as the unit. The measured water column height is the patient's bladder pressure. Specifically, when the patient maintains a lying posture, after emptying the urine in the patient's bladder through the first pipeline 4, the valve assembly 3 is changed so that 50 ml of sterile isotonic saline is input into the patient's bladder through the second pipeline 5. Taking the pubic symphysis as the zero adjustment point, the measured water column height is the pressure value. The unit of the displayed intra-abdominal pressure is cmH 2 O or mmHg, and it can be converted into kPa according to needs. Preferably, a pressure sensor, a valve and a filter can also be arranged in the second pipeline 5 to measure the bladder pressure more accurately. The above method is an important technical means in bladder pressure measurement, and for the sake of brevity in this application, the specific steps thereof will not be elaborated.

[0050] In the present invention, the bladder pressure obtained through the above embodiment is set as the second bladder pressure.

[0051] Embodiment 4

[0052] This embodiment is a further supplement to the above embodiment, and the repeated content will not be elaborated.

[0053] The setting of the third pipeline 6 is to be able to measure accurate patient bladder pressure data through the change of the fluid pressure in the airbag 2.

[0054] According to a preferred embodiment, when measuring through the pressure change in the airbag 2, it is necessary to first keep the pressure inside the airbag within a constant range. For example, keep the pressure inside the airbag 2 at 250 millimeters of mercury (mmHg) ± 5 mmHg. At this time, the second valve 802 is in the open state. To enable the normal operation of the airbag 2. The syringe 702 is filled with fluid, and the balance chamber 703 and the pipeline connected to the detection module 8 are filled with fluid by injecting the fluid into the balance chamber 703. The filter 803 is used to discharge non-fluid substances (such as air) in the balance assembly 7 before and during the introduction of the fluid. The cooperative setting of the balance chamber 703 and the spring chamber 704 can use the pressure detected by the pressure sensor 801 as a reference line. That is, the pressure detected by the pressure sensor 801 is zeroed to adapt to the pressure pre-maintained by the current airbag 2. Preferably, the balance chamber 703 and the spring chamber 704 are respectively used to maintain the pressure and volume pre-maintained by the current airbag 2. It should be noted that the subsequent pressure change of the airbag 2 depends entirely on the change in the patient's intra-abdominal pressure and has nothing to do with any other pressure sources of the components in this device. Then, the first valve 601 is opened to keep the airbag 2, the balance assembly 7, and the detection module 8 in fluid communication, and balance the fluid balance detection structure composed of the airbag 2, the third pipeline 6, the balance assembly 7, and the detection module 8 to the reference line. That is, the zero reference line of the pressure sensor 801 is at 250 millimeters of mercury (mmHg) ± 5 mmHg. Therefore, through the establishment of the reference line of the pressure sensor 801, the subsequent change of the pressure sensor 801 can characterize the change of the patient's bladder pressure. The above change generally remains between 10 mmHg and 20 mmHg, or between 5 mmHg and 30 mmHg, and this change depends on the patient's physical signs. The compression of the spring chamber 704 is used to maintain the appropriate pressure and volume in the balance chamber 703. The opening of the first valve 601 is after the pressure balance between the airbag 2 and the balance assembly 7, so as to keep the fluid communication between the airbag 2 and the balance assembly 7.

[0055] Specifically, the detection of the patient's bladder pressure lies in: when the patient's bladder pressure changes, the pressure applied to the airbag 2 is changed. If the pressure received by the airbag 2 increases, the airbag 2 compresses, resulting in an increase in the pressure in the fluid balance detection structure. If the pressure received by the airbag 2 decreases, the airbag 2 expands, resulting in a decrease in the pressure in the fluid balance detection structure. This pressure can be continuously detected by the pressure sensor 801.

[0056] The pressure sensor 801 sends the detected pressure change to the control module to obtain the change of bladder pressure over time, and finally obtains accurate patient bladder pressure data. The fluid injected by the syringe 702 can also be controlled by the injection valve 701, and the injection valve 701 also prevents the pressure in the fluid balance detection structure from being released. When enough fluid is injected into the fluid balance detection structure, the spring chamber 704 balances the structure. Specifically, the spring chamber 704 adjusts the pressure in the structure by adjusting the size of the balance chamber 703. This adjustment is an automatic adjustment of the spring chamber 704 in a closed environment. The fluid can be a gas, a liquid, or other fluid media that can reflect pressure changes.

[0057] In the present invention, the bladder pressure obtained through the above embodiments is set as the third bladder pressure.

[0058] Embodiment 5

[0059] This embodiment is a further supplement to the above embodiments, and the repeated content will not be elaborated.

[0060] According to a preferred implementation manner, in the present invention, for the measurement of bladder pressure, especially for the measurement of bladder pressure by various measurement methods with measurement errors, it is very important to further reduce the generation of measurement errors. Therefore, the following steps are given:

[0061] When the first bladder pressure, the second bladder pressure, and the third bladder pressure are measured through the above embodiments, further bladder pressure calculation can be performed according to the weight ratio of the measured bladder pressures. The weight formula is:

[0062] X = 0.4a + 0.2b + 0.4c;

[0063] Wherein, X represents the actual bladder pressure of the patient, a represents the first bladder pressure, b represents the second bladder pressure, and c represents the third bladder pressure.

[0064] The measurements of the first bladder pressure, the second bladder pressure, and the third bladder pressure can be respectively used for the requirements in different situations. The prior art often uses a single and simple measurement method to calculate the patient's bladder pressure. The method of observing the bladder pressure by the height of the water column after injecting normal saline can only perform intermittent pressure measurement, and repeated injections bring great pain and the risk of infection to the patient. In many cases, the bladder pressure measurement of the patient should not be carried out in this way. The three-way pipe 1 provided by the present invention integrates multiple measurement methods, can adaptively select based on the current physical signs of the patient, and multiple measurement methods can be combined. For example, the first pipeline 4 and the third pipeline 6, and the second pipeline 5 and the third pipeline 6 can be carried out together to measure the more accurate bladder pressure of the patient, and the measurement method of the third pipeline 6 has continuity, so that the patient does not need to perform multiple injections of fluid in the bladder, and the change of the patient's intra-abdominal pressure can be detected in real time to ensure the best rescue time. The measurement method of the third pipeline 6 can also be used for further calibration of the first bladder pressure and / or the second bladder pressure measured by the first pipeline 4 and / or the second pipeline 5. This undoubtedly improves the accuracy of the calculation, thereby reducing the possible measurement error.

[0065] According to a preferred embodiment, the method for calculating the third bladder pressure actually calculates the change curve of the patient's actual bladder pressure under the standard bladder pressure. For this purpose, the control module records the patient's bladder pressure change data with the time when the third bladder pressure undergoes a preset change value as the change period. For example, the preset change value is set to +6 mmHg. When the pressure change detected by the pressure sensor reaches +6 mmHg or exceeds +6 mmHg, the control module records it and collects the time. Similarly, the preset change value is set to -6 mmHg. When the pressure change detected by the pressure sensor reaches -6 mmHg or exceeds -6 mmHg, the control module records it and collects the time. The above settings enable the patient's bladder pressure change to be recorded not according to the time axis, but according to the time when the bladder pressure change occurs. That is, the time interval between two consecutive changes may be the same or different. The purpose of such a design is to clearly reflect the change law of the bladder pressure, prevent the influence of uncontrollable factors on the bladder pressure measurement, and obtain the bladder pressure change speed in an objective manner. For example, if the calculated third bladder pressure of the patient is within the normal range, that is, within the preset change value, this value conforms to the fact and is used in the weight calculation of the first bladder pressure and the second bladder pressure. If the calculated third bladder pressure of the patient only changes beyond the preset change value within a short period, this section of the change may be caused by the contraction of the patient's detrusor muscle. This data should not be used in the weight calculation of the first bladder pressure and the second bladder pressure. By separating the calculated continuous third bladder pressure through the preset change value, the data that conforms to the patient's bladder pressure change over time is objectively selected, so that the finally obtained bladder pressure is more accurate. Preferably, the preset change value for recording the patient's bladder pressure change data is set in a way that decreases as the pressure change amount increases. For example, when the preset change value is set to +6 mmHg, the pressure change detected by the pressure sensor in the first time period reaches +6 mmHg, the pressure change detected by the pressure sensor in the second time period reaches +9 mmHg, and the pressure change detected by the pressure sensor in the third time period reaches +10 mmHg. That is, the respective change values are +6 mmHg, +3 mmHg, and +2 mmHg. The above settings indicate that the patient's third bladder pressure data is continuously changing and the overall change amount is increasing. At this time, reducing the preset change value can improve the accuracy of bladder pressure detection, thereby providing more accurate detection data for the final reduction of the bladder pressure.

[0066] According to a preferred embodiment, since the control module records the patient's bladder pressure change data with the time when the third bladder pressure undergoes a preset change value as the change period, the control module can obtain multiple time periods during which the bladder pressure changes. During the long-term measurement of the same patient, an overly long period leads to the calculation of invalid data, resulting in a large amount of data that the control module needs to process and a slow speed of obtaining the bladder pressure data. Preferably, medical staff can selectively divide the multiple time periods of the measured third bladder pressure according to the observed patient status or behavior. For example, the change amount in a short time can be specifically ignored, thereby reducing the calculation of the data volume and avoiding the delay phenomenon in the final determination of the bladder pressure. By allowing medical staff to independently select the required time period, the present invention reduces the data measurement volume, thereby reducing the measurement of invalid data.

[0067] Throughout the text, the features guided by "preferably" are only optional and should not be construed as mandatory. Therefore, the applicant reserves the right to waive or delete the relevant preferred features at any time.

[0068] It should be noted that the above specific embodiments are exemplary. Those skilled in the art can come up with various solutions inspired by the disclosure of the present invention, and these solutions also fall within the scope of the disclosure of the present invention and within the protection scope of the present invention. Those skilled in the art should understand that the description of the present invention and its accompanying drawings are illustrative and do not constitute a limitation to the claims. The protection scope of the present invention is defined by the claims and their equivalents.

Claims

1. An intra-abdominal pressure measurement system, comprising at least a three-way pipe (1), characterized in that: The three-way pipe (1) comprises: a first pipeline (4), a third pipeline (6) and a control module, wherein: The control module obtains a first bladder pressure in the first pipeline (4) by measuring the urine production rate in the patient's bladder; The control module obtains a third bladder pressure in the third pipeline (6) by measuring the change in fluid pressure in the air bag (2); The control module is further configured to: based on the urine production rate of the patient in a plurality of time periods, correct the abnormal value in the first bladder pressure measurement by averaging the urine production rates in at least two adjacent time periods; The fluid balance detection structure in the third pipeline (6) balances the fluid pressure and uses the balanced pressure as a baseline to obtain continuous bladder pressure change data for correction of bladder pressure.

2. The intra-abdominal pressure measurement system according to claim 1, characterized in that: The method of averaging the urine production rates in at least two adjacent time periods refers to: Take the current moment as the starting time point T1 for measurement, and the next N moments as the ending time point Tn for measurement, then the patient's urine production rate in this time period = (urine weight at the next N moments - urine weight at the current moment) / (Tn-T1), and the patient's urine production rate continuity measured in this time period is averaged again with other urine production rates, and the final urine production rate is taken as the patient's actual urine production rate.

3. The intra-abdominal pressure measurement system according to claim 2, characterized in that: The control module calculates the time required for the patient's bladder to produce a certain amount of urine based on the patient's actual urine production rate. After the patient's bladder is emptied of urine, the control module starts timing and stops after the calculated required time is reached. The pressure sensor provided in the first pipeline (4) sends the measured first bladder pressure to the control module.

4. The intra-abdominal pressure measurement system according to claim 3, characterized in that: The third pipeline (6) is connected to a balancing component (7) for fluid balance, and the balancing component (7) at least includes an injection valve (701), a syringe (702), a balancing chamber (703) and a spring chamber (704). The balancing chamber (703) is connected to the third pipeline (6). The syringe (702) injects fluid into the airbag (2) through the injection valve (701), the balancing chamber (703) and the third pipeline (6). The third pipeline (6) is used to promote fluid communication between the airbag (2) and the balancing component (7). The continuity or periodic change of the fluid pressure in the airbag (2) can be detected by fluid balance.

5. The intra-abdominal pressure measurement system according to claim 4, characterized in that: The system further comprises a valve assembly (3), the air bag (2) being arranged at one end of the three-way tube (1) to be inserted into the patient's bladder, and the valve assembly (3) being arranged at one end of the three-way tube (1) away from the patient's bladder, wherein the three-way tube (1) is provided with an inner tube (101) and an outer tube (102) spaced apart from each other, the inner tube (101) being nested in the outer tube (102) and having the same central axis as the outer tube (102), the outer tube (102) being connected to the inner tube (101) at one end inside the patient's bladder and the outer tube (102) being provided with a circumferential opening communicating with the air bag (2), the inner tube (101) extending out of the outer tube (102) and being provided with an opening communicating with the patient's bladder, The airbag (2) is configured as an airbag close to the patient's bladder wall and connected only to the outer tube (102). The airbag (2) measures the patient's intra-abdominal pressure changes in real time and continuously through the changes in the fluid pressure inside the airbag (2).

6. The intra-abdominal pressure measurement system according to claim 5, characterized in that: The inner tube (101) is configured to drain internal fluid from the patient's bladder and to inject fluid into the patient's bladder. The end of the inner tube (101) away from the patient's bladder is connected to the valve assembly (3), wherein: The valve assembly (3) is connected to the first pipeline (4) and the second pipeline (5), and the valve assembly (3) can be switched between the inner tube (101) being connected to the first pipeline (4) and the inner tube (101) being connected to the second pipeline (5).

7. The intra-abdominal pressure measurement system according to claim 6, characterized in that: The second pipeline (5) is configured to: calculate the second bladder pressure through the height of the water column based on the set measurement mark, When the first bladder pressure, the second bladder pressure and the third bladder pressure are measured, the actual bladder pressure of the patient can be calculated according to the weight ratio of each measured bladder pressure.

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