CN115326160B - A method for monitoring bleeding volume - Google Patents
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- CN115326160B CN115326160B CN202211074390.8A CN202211074390A CN115326160B CN 115326160 B CN115326160 B CN 115326160B CN 202211074390 A CN202211074390 A CN 202211074390A CN 115326160 B CN115326160 B CN 115326160B
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F22/00—Methods or apparatus for measuring volume of fluids or fluent solid material, not otherwise provided for
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F5/00—Orthopaedic methods or devices for non-surgical treatment of bones or joints; Nursing devices ; Anti-rape devices
- A61F5/48—Devices for preventing wetting or pollution of the bed
- A61F5/485—Absorbent protective pads
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- G—PHYSICS
- G06—COMPUTING OR CALCULATING; COUNTING
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Abstract
本发明提供了一种出血量的监测方法，用于可监测出血量产褥垫。本发明以第一柔性电极层上的印刷电极为行、第二柔性电极层的印刷电极为列进行阵列排布，确定第i行、第j列的产褥垫测量点；利用测量点的设计，接通电源后得到与测量点的相关电压信息Vij、液体渗入百分比Mij，再经过数据拟合，得到测量点所在组的面积A，最后经由液体扩散模型输出体积V，从而得到产褥垫上的出血量信息，方便医护人员进行下一步的治疗措施。本发明的检测方法能够精准的检测手术过程中产妇的出血量，且不产生刺痛感，具有推广价值。
The present invention provides a method for monitoring the amount of bleeding, which is used for a maternity pad that can monitor the amount of bleeding. The present invention arranges the printed electrodes on the first flexible electrode layer as rows and the printed electrodes on the second flexible electrode layer as columns to determine the maternity pad measurement points of the i-th row and the j-th column; by using the design of the measurement points, the voltage information V ij and the liquid penetration percentage M ij related to the measurement points are obtained after the power is turned on, and then the area A of the group where the measurement points are located is obtained through data fitting, and finally the volume V is output through the liquid diffusion model, so as to obtain the bleeding amount information on the maternity pad, which is convenient for medical staff to take the next step of treatment measures. The detection method of the present invention can accurately detect the amount of bleeding of parturients during surgery without causing tingling, and has promotion value.
Description
Technical Field
The invention relates to the technical field of medical care equipment, in particular to a bleeding amount monitoring method for a mattress capable of monitoring bleeding amount production.
Background
Along with the continuous development of science and technology and the continuous improvement of living standard of people, people increasingly lean towards intelligent development, especially in the field of medical sanitation, after parturient birth, medical staff needs to accurately master the postpartum hemorrhage amount of the parturient, and the evaluation method of the hemorrhage amount is a simple and practical visual method, but the visual method needs to rely on the experience of the medical staff, and because the experience difference of each person is very large, the visual hemorrhage amount often has a large error. More researchers are monitoring the progress toward blood volume. The patent document with the patent number of CN113049638A discloses a liquid content measuring device, a system and a nursing article, a plurality of impedance measuring units are arranged on the nursing article such as a paper diaper or a mattress, when the humidity of the nursing article changes, the resistance value of the impedance measuring units is reduced, and then the liquid content in the current nursing article can be calculated.
And when testing, most products need to supply power to the impedance test unit, and nursing articles such as mattress are produced when wetted by blood etc., can form conductive loop with test circuit, and the human body can produce the stinging sense, and product security is difficult to guarantee.
In view of the above, we have designed a monitorable system with maximum power supply of 2.5V and maximum current of 25uA, which can accurately detect the bleeding amount of the parturient in the operation process without generating a tingling sensation.
Disclosure of Invention
Aiming at the defects of the prior art, the invention aims to provide a bleeding amount monitoring method which has the characteristics of accuracy and high efficiency.
The technical scheme adopted for solving the technical problems is as follows:
the invention discloses a method for monitoring bleeding amount, which is used for producing mattresses capable of monitoring bleeding amount and comprises the following steps of:
Step 1, arranging measuring points on the mattress, switching on a power supply of the mattress, dripping liquid and simulating liquid infiltration;
The mattress production device comprises a mattress production layer, a first flexible electrode layer, a second flexible electrode layer, a first conducting wire, a second conducting wire, a first electrode layer, a second electrode layer, a first electrode layer and a second electrode layer, wherein the first flexible electrode layer and the second electrode layer are respectively arranged on two sides of the water absorption layer;
Step 2, scanning the mattress, collecting voltage V ij of a measurement point, and converting voltage information into liquid infiltration percentage M ij, wherein the liquid infiltration percentage M ij meets the following formula:
M ij =100% is liquid 100% penetrated, and M ij =0% is liquid no penetrated;
step 3, determining an infiltration area according to the liquid infiltration percentage M ij and a plurality of groups formed by the liquid infiltration measuring points, and recording the starting time T start and the infiltration time T of the groups;
the infiltration time t=clock-T start, wherein clock is a singlechip clock electrically connected with the mattress;
step 4, performing equivalent fitting on each group of data of the liquid infiltration area, and estimating a weight area A k of the group:
Let the distance (Δx, Δy) before the electrodes are printed on the same flexible electrode layer, then each measurement point represents an area Δa=ΔxΔy, and then the area a k of the group is calculated as:
Ak＝∑ijMijΔxΔyδij
k∈[1,2,3,...]i∈[1,2,...,m]j∈[1,2,...,n]
step 5, substituting the infiltration time t of the step 3 and the weight area A k of the group of the step 4 into a liquid diffusion model, and outputting a volume V;
repeating the steps 2-5.
The liquid diffusion model in step 5 is as follows:
V=ΣkVk
wherein A k is the weight area of the group;
V is the total liquid volume, V k is the k-th set of liquid volumes;
a and b are mathematical fitting results, and have no specific physical significance;
t k is the soak time of a group;
t d is the diffusion time constant, and t e is the evaporation time constant.
In addition to the above, and as a preferable aspect of the above, the water absorbing layer is made of a water absorbing resin.
On the basis of the above scheme and as a preferable scheme of the above scheme, the printing electrode is screen printing conductive ink, and the conductive ink is one of copper foil, silver paste and carbon paste material.
On the basis of the scheme and as a preferable scheme of the scheme, the distance between the adjacent printing electrodes of the same flexible electrode layer is 45-65mm.
On the basis of the above scheme and as a preferable scheme of the above scheme, the voltage V ij of the measurement point is in the range of 0-2.5V.
The beneficial effects of the invention are as follows:
Compared with the prior art, the invention utilizes the design of the measuring points, obtains the related voltage information and the liquid penetration percentage of the measuring points after the power is turned on, obtains the area of the group where the measuring points are positioned through data fitting, and finally outputs the volume through the liquid diffusion model, thereby obtaining the bleeding amount information on the mattress and facilitating the medical staff to carry out the next treatment measures. The detection method can accurately detect the bleeding amount of the puerpera in the operation process, does not produce the tingling sensation, and has popularization value.
Drawings
FIG. 1 is a flow chart of the steps of the present invention;
FIG. 2 is a schematic view of the mattress structure of the present invention;
FIG. 3 is a schematic diagram of a connection structure of a first flexible electrode layer and a second flexible electrode layer;
FIG. 4 is a fitting diagram of a liquid diffusion model;
FIG. 5 is a graph of the measured volume versus the actual measured volume of a liquid diffusion model.
In the figure, 12-a first flexible electrode layer, 13-a water-absorbing layer, 14-a second flexible electrode layer, 2-a printed electrode and 3-a wire.
Detailed Description
The present invention will be further described in conjunction with the following specific embodiments, and the technical solutions in the embodiments of the present invention will be clearly and completely described, and it is apparent that the described embodiments are only some embodiments of the present invention, not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
Example 1
As shown in fig. 1-3, a method for monitoring bleeding volume includes the steps of:
step 1, arranging measuring points on the mattress, switching on a power supply of the mattress, and dripping liquid;
the mattress production comprises a water absorption layer 13, wherein a first flexible electrode layer 12 and a second flexible electrode layer 14 are respectively arranged on two sides of the water absorption layer 13, the first flexible electrode layer 12 and the second flexible electrode layer 14 respectively comprise printed electrodes 2 which are arranged in parallel, the printed electrodes 2 on the first flexible electrode layer 12 and the printed electrodes 2 on the second flexible electrode layer 14 are arranged in a crisscross manner, the first flexible electrode layer 12 and the second flexible electrode layer 14 are connected with a lead 3, the lead 3 is electrically connected with a power supply, the printed electrodes 2 on the first flexible electrode layer 12 are arranged in rows, and the printed electrodes 2 on the second flexible electrode layer 14 are arranged in columns in an array manner, and the measurement points of the mattress production in the ith row and the jth row are recorded;
Step 2, scanning the mattress, collecting voltage V ij of a measurement point, and converting voltage information into liquid infiltration percentage M ij, wherein the liquid infiltration percentage M ij meets the following formula:
M ij =100% is liquid 100% penetrated, and M ij =0% is liquid no penetrated;
Step 3, according to the liquid infiltration percentage M ij, integrating adjacent liquid infiltration measuring points into a plurality of groups, determining an infiltration area, recording the starting time T start of the groups, and calculating the infiltration time T;
the soaking time t=clock-T start, wherein clock is the current time recorded by a singlechip clock electrically connected with the mattress;
step 4, performing equivalent fitting on each group of data of the liquid infiltration area, and estimating a weight area A k of the group:
Let the distance (Δx, Δy) before the electrodes 2 are printed on the same flexible electrode layer, the surface area represented by each measurement point is Δa=ΔxΔy, and the weight area a k of the group is calculated as:
Ak＝∑ijMijΔxΔyδij
k∈[1,2,3,...]i∈[1,2,...,m]j∈[1,2,...,n]
M ij is the mattress measurement point of the ith row and the jth column in M mxn, and M and n respectively represent the number of electrodes on the first flexible electrode layer 12 and the second flexible electrode layer 14, in this embodiment, m=8 and n=8.
Step 5, substituting the infiltration time t of the step 3 and the weight area A k of the group of the step 4 into a liquid diffusion model, and outputting a volume V;
repeating the steps 2-5.
The liquid diffusion model in step 5 is as follows:
V=ΣkVk
wherein A k is the weight area of the group;
V is the total liquid volume, V k is the k-th set of liquid volumes;
a and b are mathematical fitting results, and have no specific physical significance;
t k is the soak time of a group;
t d is the fit diffusion time constant and t e is the fit evaporation time constant.
Specifically, V max in this embodiment is 2.5V, and when V ij =2.5V, the measurement point is not permeated with liquid, and when V ij =0V, the measurement point is completely permeated with liquid.
Further, in step 3, the immersion time t=clock-T start, where clock is a single-chip clock electrically connected to the mattress, and T start is a start time, where when there is no liquid on the mattress, the timer does not record time, i.e., T start =clock, so that the immersion time t=0. In this embodiment, to remove the influence of noise, the timer starts counting when M ij =10%, i.e., T start +.clock. Still further, according to the liquid infiltration percentage M ij, and integrating the liquid infiltration measurement points into a plurality of groups, determining the infiltration area, the specific grouping rule is as follows:
1. If one measuring point (i, j) has liquid (M ij > 0.1) but is not grouped, detecting whether the liquid exists around the measuring point (i, j), if not, establishing a group, recording the infiltration time t of the group, if so, dividing the measuring point into groups of surrounding measuring points, and if a plurality of groups exist around, combining all the groups, wherein the infiltration time t is the longest infiltration time.
2. Updating M ij when the liquid exists in the measurement points (i, j) and the group exists;
3. the measurement point (i, j) is free of liquid (M ij. Ltoreq.0.1) and the next point is continued.
Since the thickness of the mattress is much smaller than the length and width, the equivalent mattress can be seen as a two-dimensional plane. After a small amount of liquid (1-2 ml) is dripped, the liquid can penetrate through the water absorption layer 13 extremely quickly, so that the supersaturation (M ij > 100%) of the dripping point area is caused, and the liquid transversely permeates to the periphery under the supersaturation pressure to form a wetting area, namely a group. Also in this process, the thickness direction is completely permeable under wet conditions. In this embodiment, the thickness of the mattress is 0.85-1 mm, and the thickness after infiltration is also 0.85-1 mm.
Still further, the gram weight of the water absorbing layer 13 in this embodiment is 176g/m 2, and the liquid diffusion model in step 5 is:
V=ΣkVk
wherein A k is the weight area of the group;
V is the total liquid volume, V k is the k-th set of liquid volumes;
a and b are mathematical fitting results, and have no specific physical significance;
t k is the soak time of a group;
t d is the fit diffusion time constant and t e is the fit evaporation time constant.
In the above formula, a is influenced by the thickness of the water absorbing layer 13, the thicker the water absorbing layer 13 is, the larger the gram weight of unit area is, the larger a in the formula is, and aV b refers to the maximum liquid content after the water absorbing layer is filled. In the practical application process, the water absorbing layer 13 becomes slightly thicker in the water absorbing process, but the water absorbing material per unit area is not added, so the aV b in the formula is not affected, that is, the coefficient a is not changed under the same type of mattress producing condition.
In a general practical application process, three processes of fast diffusion (0-30 s), slow diffusion (1-30 min) and evaporation (more than or equal to 30-40 min) are sequentially adopted, and the liquid diffusion can be reflected by using A (t) =aV b α (t) β (t):
Alpha (t) is an infiltration excitation function, which is a function of 0-1 increasing with time, the increasing speed being the liquid diffusion speed, in this case alpha (t) being To reflect the liquid diffusion rate;
Beta (t) is the evaporation excitation function, which is a function of 1~0 decreasing with time, the decreasing rate being the liquid evaporation rate, in this case beta (t) is To reflect the liquid evaporation rate.
AV b is the maximum wetted area for a volume V of liquid.
The liquid diffusion model can reflect the liquid diffusion process more completely, and the infiltration time t of the step 3 and the area A k of the group of the step 4 are utilized to be substituted into the liquid diffusion model, so that the blood permeation volume V can be output.
Further, the water absorbing layer 13 is made of a water absorbing resin, and the water absorbing resin is a novel functional polymer material, has a good water absorbing function, and can accelerate the permeation of blood and the like. Still further, the printed electrode 2 is a screen printed conductive ink, and the conductive ink is one of copper foil, silver paste and carbon paste material, so as to ensure good conductivity.
Furthermore, the distance between the adjacent printed electrodes 2 of the same flexible electrode layer is 45mm, so that the volume V can be fed back more accurately.
Referring to standard GB/T8939-2018, a simulation test is performed by taking standard synthetic liquid as blood equivalent liquid, and dripping is performed at a rate of 3mL per minute at a measurement interval of 1 minute to determine a liquid diffusion model, wherein FIG. 4 is a fitting chart of the liquid diffusion model, and the obtained liquid diffusion model meets the following formula:
After the power is turned on and the mattress is subjected to scanning test, the infiltration time t and the area A k of the group are substituted into the liquid diffusion model to output the volume V, and the measured volume of the liquid diffusion model is compared with the actual test volume to obtain the comparison result of FIG. 5. Fig. 5 is a graph of the measured volume of the liquid diffusion model compared with the actual measured volume, and the liquid measurement error is 40mL as can be seen from the comparison information.
Example two
Unlike the first embodiment, the distance between adjacent printed electrodes 2 of the same flexible electrode layer is 55mm, and the other is the same as the first embodiment.
Example III
Unlike the first embodiment, the spacing between adjacent printed electrodes 2 of the same flexible electrode layer is 65mm, and the other is the same as the first embodiment.
Example IV
In contrast to the above embodiment, the pitch between adjacent printed electrodes 2 of one flexible electrode layer is 65mm, and the pitch between adjacent printed electrodes 2 of the other flexible electrode layer is 45mm, so as to form a rectangular unit area, otherwise the same as the embodiment.
The foregoing describes in detail preferred embodiments of the present invention. It should be understood that numerous modifications and variations can be made in accordance with the concepts of the invention by one of ordinary skill in the art without undue burden. Therefore, all technical solutions which can be obtained by logic analysis, reasoning or limited experiments based on the prior art by the person skilled in the art according to the inventive concept shall be within the scope of protection defined by the claims.
Claims (5)
1. A method for monitoring bleeding amount, for a mattress capable of monitoring bleeding amount, comprising the steps of:
step 1, arranging measuring points on the mattress, switching on a power supply of the mattress, and dripping liquid;
The mattress comprises a water absorption layer (13), wherein a first flexible electrode layer (12) and a second flexible electrode layer (14) are respectively arranged on two sides of the water absorption layer (13), the first flexible electrode layer (12) and the second flexible electrode layer (14) comprise printed electrodes (2) which are arranged in parallel, the printed electrodes (2) on the first flexible electrode layer (12) and the printed electrodes (2) on the second flexible electrode layer (14) are arranged in a crisscross manner, a wire (3) is connected to the first flexible electrode layer (12) and the second flexible electrode layer (14), the wire (3) is electrically connected with a power supply, the printed electrodes (2) on the first flexible electrode layer (12) are arranged in rows, the printed electrodes (2) on the second flexible electrode layer (14) are arranged in columns, and mattress measuring points of an ith row and a jth row are recorded;
Step 2, scanning the mattress, collecting voltage V ij of a measurement point, and converting voltage information into liquid infiltration percentage M ij, wherein the liquid infiltration percentage M ij meets the following formula:
M ij =100% is liquid 100% penetrated, and M ij =0% is liquid no penetrated;
Step 3, according to the liquid infiltration percentage M ij, integrating adjacent liquid infiltration measuring points into a plurality of groups, determining an infiltration area, recording the starting time T start of the groups, and calculating the infiltration time T;
the soaking time t=clock-T start, wherein clock is the current time recorded by a singlechip clock electrically connected with the mattress;
step 4, performing equivalent fitting on each group of data of the liquid infiltration area, and estimating a weight area A k of the group:
Let the distance (Δx, Δy) before the electrode (2) is printed on the same flexible electrode layer, then each measurement point represents an area Δa=ΔxΔy, and then the weight area a k of the group is calculated as:
step 5, substituting the infiltration time t of the step 3 and the weight area A k of the group of the step 4 into a liquid diffusion model, and outputting a volume V;
Repeating the steps 2-5;
the liquid diffusion model in step 5 is as follows:
V=∑kVk
wherein A k is the weight area of the group;
V is the total liquid volume, V k is the k-th set of liquid volumes;
a and b are mathematical fitting results, and have no specific physical significance;
t k is the soak time of a group;
t d is the fit diffusion time constant and t e is the fit evaporation time constant.
2. The method for monitoring bleeding amount according to claim 1, wherein the water-absorbing layer (13) is made of a water-absorbent resin.
3. The method for monitoring bleeding amount according to claim 1, wherein the printed electrode (2) is screen printed conductive ink, and the conductive ink is one of copper foil, silver paste and carbon paste material.
4. A method of monitoring bleeding as in claim 3, wherein adjacent printed electrodes (2) of the same flexible electrode layer are spaced 45-65mm apart.
5. A method of monitoring bleeding as in claim 1, wherein the voltage V ij at the measurement point is in the range of 0-2.5V.
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| CN218391514U (en) * | 2022-09-03 | 2023-01-31 | 嘉兴暄泽医疗科技有限公司 | Mattress capable of monitoring bleeding amount |
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| JP2002090329A (en) * | 2000-09-19 | 2002-03-27 | Tabai Espec Corp | Humidity sensor and its manufacturing method |
| US20030203504A1 (en) * | 2002-04-26 | 2003-10-30 | John Hefti | Diffusion-based system and method for detecting and monitoring activity of biologic and chemical species |
| EP1642125B1 (en) * | 2003-06-20 | 2017-09-27 | Roche Diabetes Care GmbH | Biosensor with multiple electrical functionalities |
| US8398603B2 (en) * | 2006-02-28 | 2013-03-19 | Coloplast A/S | Leak sensor |
| EP2148838B1 (en) * | 2007-05-24 | 2017-03-01 | Digital Biosystems | Electrowetting based digital microfluidics |
| FI123318B (en) * | 2009-09-29 | 2013-02-28 | Outotec Oyj | Three-dimensional imaging of a mass flow |
| CN106580558A (en) * | 2016-12-09 | 2017-04-26 | 广东工业大学 | Replaceable urine-excrement monitoring system |
| CN110927332A (en) * | 2019-10-29 | 2020-03-27 | 上海创始实业（集团）有限公司 | Liquid content detection system and detection method thereof, and nursing product |
| CN113049638A (en) * | 2021-03-25 | 2021-06-29 | 上海创始医疗科技(集团)有限公司 | Liquid content measuring device and system and nursing product |
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