CN115282365B - Infusion liquid volume calibration method and device, electronic equipment and medium - Google Patents
Infusion liquid volume calibration method and device, electronic equipment and medium Download PDFInfo
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- CN115282365B CN115282365B CN202211219901.0A CN202211219901A CN115282365B CN 115282365 B CN115282365 B CN 115282365B CN 202211219901 A CN202211219901 A CN 202211219901A CN 115282365 B CN115282365 B CN 115282365B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/02—Blood transfusion apparatus
- A61M1/024—Means for controlling the quantity of transfused blood, e.g. by weighing the container and automatic stopping of the transfusion after reaching a determined amount
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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
Abstract
The application relates to the field of volume calibration, and provides a method and a device for calibrating the volume of infusion liquid, electronic equipment and a medium. The method comprises the following steps: detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose; if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a corrected analog signal formed by the bubble and an analog signal formed when the infusion bag is empty; and supplementing the liquid volume in the infusion bag according to the difference value between the liquid volume and the target volume until the liquid volume in the infusion bag reaches the target volume, and completing the calibration of the infusion liquid. The method for calibrating the volume of the infusion liquid can ensure that the dosage of the cell liquid input into a human body is sufficient, so that the treatment effect is ensured.
Description
Technical Field
The application relates to the technical field of volume calibration, in particular to a method and a device for calibrating the volume of infusion liquid, electronic equipment and a medium.
Background
In the field of cell therapy, need carry the quantitative cell liquid in the infusion bag to the human body and treat, before this, need earlier inject cell liquid into infusion bag through the hose, in the injection process, because various factor interference, can produce the bubble in the cell liquid, lead to injecting into infusion bag not totally cell liquid, but the fluid that cell liquid and bubble mix, the space of cell liquid has been crowded to have taken up to the bubble, lead to actually injecting into infusion bag's cell liquid volume to appear the deviation, when needs quantitative infusion treatment, because the dose is inaccurate, thereby influence treatment.
Disclosure of Invention
The embodiment of the application provides a method and a device for calibrating the volume of infusion liquid, electronic equipment and a medium, which are used for solving the technical problems that the volume of the cell liquid actually injected into an infusion bag is deviated due to bubbles generated in the cell liquid, and the treatment effect is influenced due to inaccurate dosage when quantitative infusion treatment is needed.
In a first aspect, an embodiment of the present application provides an infusion liquid volume calibration method, including:
detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose;
if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a correction analog signal formed by the bubble and an analog signal formed when the infusion bag is empty;
and supplementing the liquid volume in the infusion bag according to the difference value between the liquid volume and the target volume until the liquid volume in the infusion bag reaches the target volume, and completing the calibration of the infusion liquid.
In one embodiment, the detecting whether bubbles exist in the fluid flowing through the hose based on infrared rays includes:
emitting a first infrared ray to the fluid at a first preset position, and receiving a first analog signal at a second preset position; the first preset position and the second preset position are positioned on two sides of the hose, and the first analog signal is an analog signal of the first infrared ray after passing through the fluid;
emitting a second infrared ray to the fluid at a third preset position, and receiving a second analog signal at a fourth preset position; the third preset position and the fourth preset position are positioned on two sides of the hose, the third preset position is positioned at the downstream of the first preset position, and the second analog signal is an analog signal of the second infrared ray after passing through the fluid;
obtaining the diameter of the suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of a single concave waveform and a preset distance; the duration of the single concave waveform is the duration of the single concave waveform from appearance to disappearance in the waveform of the first analog signal or the waveform of the second analog signal, and the preset distance is the projection length of the straight-line distance between the first preset position and the third preset position on the hose;
and if the diameter of the suspected bubble is larger than the diameter threshold value, determining that the bubble exists in the fluid.
In one embodiment, the obtaining the diameter of the suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of the single concave waveform, and the preset distance includes:
subtracting the first starting time point from the second starting time point to obtain a first time difference absolute value; the first starting time point is the time point when the Nth concave waveform in the waveform of the first analog signal begins to appear, the second starting time point is the time point when the Nth concave waveform in the waveform of the second analog signal begins to appear, wherein N is an integer greater than or equal to 1, and the sequence of the concave waveforms is arranged from first to last according to the time sequence;
obtaining the flow velocity of the fluid according to the ratio of the preset distance to the absolute value of the first time difference;
obtaining the diameter of the suspected bubble according to the product of the duration of the Nth concave waveform in the waveform of the first analog signal and the flow rate of the fluid; or obtaining the diameter of the suspected bubble according to the product of the duration of the nth concave waveform in the waveform of the second analog signal and the flow rate of the fluid.
In one embodiment, the obtaining a volume of liquid in a volume of fluid flowing into the infusion bag based on the corrected analog signal of bubble formation and the analog signal of the infusion bag formed when the infusion bag is empty comprises:
comparing the first analog signal with the second analog signal, and fitting the first analog signal with the second analog signal to obtain a corrected analog signal if the absolute value of the error between the first analog signal and the second analog signal is less than or equal to an error threshold;
emitting a third infrared ray to the infusion bag at a fifth preset position, and receiving a third analog signal at a sixth preset position; the infusion bag is in an empty bag state, the fifth preset position and the sixth preset position are located on two sides of an inlet pipeline of the infusion bag, and the third analog signal is an analog signal of the third infrared ray after passing through the inlet pipeline;
translating the corrected analog signal and the third analog signal to a position between a first preset time point and a second preset time point to obtain a corrected analog signal section and a third analog signal section; the first preset time point is the time point when the fluid starts to enter the infusion bag, and the second preset time point is any time point later than the first preset time point when the infusion bag is in an empty bag state;
and obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the first preset time point, the second preset time point, the correction analog signal section and the third analog signal section.
In one embodiment, the obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the first preset time point, the second preset time point, the correction analog signal section and the third analog signal section includes:
subtracting the first preset time point from the second preset time point to obtain a second time difference absolute value;
subtracting the empty liquid voltage digital value of the third analog signal segment from the maximum voltage digital value in the corrected analog signal segment to obtain a voltage digital difference value; the empty liquid voltage digital value is a voltage digital value of the third analog signal section at any time point when the infusion bag is in an empty bag state;
obtaining the total area to be processed according to the product of the second time difference absolute value and the voltage digital difference value;
and obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the total area of the sunken part of the sunken waveform in the waveform of the corrected analog signal section and the total area to be processed.
In one embodiment, said determining the presence of a bubble within said fluid comprises:
if the change rate of the slope absolute value of a single sunken waveform in the waveform of the corrected analog signal section from the maximum value to the minimum value is greater than the change rate threshold value, the type of the bubble corresponding to the sunken waveform is a circular bubble;
if the change rate of the slope absolute value of a single sunken waveform in the waveform of the corrected analog signal section from the maximum value to the minimum value is larger than zero and smaller than or equal to the change rate threshold value, the type of the bubble corresponding to the sunken waveform is an ellipse-like bubble;
according to the bubble type, calculating the depression area of a single depression waveform in the waveform of the modified analog signal segment;
summing the depression areas of all the single depression waveforms in the corrected analog signal section to obtain a summed depression area;
comparing the summed depression area to the total depression area to verify the total depression area.
In a second aspect, an embodiment of the present application provides an infusion liquid volume calibration device, including:
a bubble determination module to: detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose;
a liquid volume calculation module to: if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a corrected analog signal formed by the bubble and an analog signal formed when the infusion bag is empty;
a transfusion liquid calibration module for: and supplementing the liquid volume in the infusion bag according to the difference value between the liquid volume and the target volume until the liquid volume in the infusion bag reaches the target volume, and completing the calibration of the infusion liquid.
In one embodiment, the bubble determination module includes:
a first infrared sensor module comprising:
a first infrared-emitting tube for: emitting first infrared rays to the fluid at a first preset position;
a first photoelectric receiver for: receiving a first analog signal at a second preset position;
the first preset position and the second preset position are positioned on two sides of the hose, and the first analog signal is an analog signal of the first infrared ray after passing through the fluid;
a second infrared sensor module comprising:
a second infrared emitting tube for: emitting second infrared rays to the fluid at a third preset position;
a second photoelectric receiver for: receiving a second analog signal at a fourth preset position;
the third preset position and the fourth preset position are positioned on two sides of the hose, the third preset position is positioned at the downstream of the first preset position, and the second analog signal is an analog signal of the second infrared ray after passing through the fluid;
a diameter calculation module to: obtaining the diameter of a suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of a single concave waveform and a preset distance; the duration of the single concave waveform is the duration of the single concave waveform from appearance to disappearance in the waveform of the first analog signal or the waveform of the second analog signal, and the preset distance is the projection length of the linear distance between the first preset position and the third preset position on the hose;
a diameter comparison module to: and if the diameter of the suspected bubble is larger than the diameter threshold value, determining that the bubble exists in the fluid.
In a third aspect, an embodiment of the present application provides an electronic device, which includes a processor and a memory storing a computer program, where the processor implements the steps of the infusion liquid volume calibration method according to the first aspect when executing the program.
In a fourth aspect, embodiments of the present application provide a non-transitory computer-readable storage medium, on which a computer program is stored, where the computer program, when executed by a processor, implements the steps of the infusion liquid volume calibration method according to the first aspect.
According to the infusion liquid volume calibration method, the infusion liquid volume calibration device, the electronic equipment and the medium, the model signal formed by bubbles in the infrared irradiation hose and the model signal formed by the infrared irradiation of the empty infusion bag are utilized to obtain the liquid volume in the fluid volume flowing into the infusion bag, so that the deviation of the liquid volume relative to the target volume can be determined and the volume can be supplemented, finally the liquid volume reaches the target volume, the calibration of the liquid volume is completed, and when cell therapy is performed, the dosage of cell liquid input into a human body can be ensured to be sufficient, so that the therapeutic effect is ensured.
Drawings
In order to more clearly illustrate the technical solutions in the present application or the prior art, the drawings needed for the description of the embodiments or the prior art will be briefly introduced below, and it is obvious that the drawings in the following description are some embodiments of the present application, and it is obvious for those skilled in the art to obtain other drawings based on these drawings without creative efforts.
FIG. 1 is a schematic flow chart of a method for calibrating a volume of an infusion fluid provided in an embodiment of the present application;
FIG. 2 is a second schematic flow chart of a method for calibrating a volume of an infusion liquid according to an embodiment of the present application;
FIG. 3 is a third schematic flow chart of a method for calibrating the volume of an infusion liquid provided in the embodiments of the present application;
FIG. 4 is a fourth schematic flowchart of a method for calibrating a volume of infusion liquid provided by an embodiment of the present application;
fig. 5 is a schematic waveform diagram illustrating a modified analog signal and a third analog signal provided by an embodiment of the present application translating to a time between a first preset time point and a second preset time point;
FIG. 6 is a fifth flowchart of a calibration method for volume of infusion liquid provided by an embodiment of the present application;
FIG. 7 is a schematic structural diagram of an infusion liquid volume calibration device provided in an embodiment of the present application;
FIG. 8 is a schematic structural diagram of a bubble determination module in an infusion liquid volume calibration apparatus according to an embodiment of the present disclosure;
fig. 9 is a schematic structural diagram of an electronic device provided in an embodiment of the present application.
Detailed Description
To make the purpose, technical solutions and advantages of the present application clearer, the technical solutions in the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are some embodiments of the present application, but not all embodiments. All other embodiments obtained by a person of ordinary skill in the art based on the embodiments in the present application without making any creative effort belong to the protection scope of the present application.
Fig. 1 is a schematic flow chart of a calibration method for infusion liquid volume according to an embodiment of the present application. Referring to fig. 1, an embodiment of the present application provides an infusion liquid volume calibration method, which may include:
101. detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays;
the fluid flows from the hose to the infusion bag.
102. If the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the corrected analog signal formed by the bubble and the analog signal formed when the infusion bag is empty;
since the liquid flowing into the bag is typically contaminated with a certain amount of gas to form a fluid, the actual volume of liquid flowing into the bag is less than the volume of fluid.
103. And supplementing the liquid volume in the infusion bag according to the difference value between the liquid volume and the target volume until the liquid volume in the infusion bag reaches the target volume, and finishing the calibration of the infusion liquid.
It should be noted that, because the flow path from the flexible tube to the infusion bag is relatively closed, the form and the number of the bubbles do not change significantly during the process of flowing the fluid from the flexible tube into the infusion bag, that is, the bubble condition in the fluid flowing into the infusion bag can be characterized by detecting the bubble condition in the fluid flowing through the flexible tube.
According to the method for calibrating the volume of the infusion liquid, the volume of the liquid flowing into the infusion bag is obtained by utilizing the model signal formed by irradiating the bubbles in the hose with the infrared rays and the model signal formed by irradiating the infusion bag in the empty bag state with the infrared rays, so that the deviation of the volume of the liquid from the target volume can be determined and the volume can be supplemented, finally the volume of the liquid reaches the target volume, the calibration of the volume of the liquid is completed, and when cell therapy is performed, the dosage of cell liquid input into a human body can be ensured to be sufficient, so that the therapeutic effect is ensured.
Fig. 2 is a second flowchart of the calibration method for the volume of infusion liquid according to the embodiment of the present application. Referring to fig. 2, in one embodiment, detecting whether bubbles exist in fluid flowing through a hose based on infrared rays may include:
201. emitting first infrared rays to the fluid at a first preset position, and receiving a first analog signal at a second preset position;
the first preset position and the second preset position are located on two sides of the hose, and the first analog signal is an analog signal of the first infrared ray after passing through the fluid.
The wavelength of the first infrared ray may be 850 nm, and the emission angle may be ± 10 degrees, that is, an included angle between a connection line between the first preset position and the second preset position and a vertical line from the first preset position or the second preset position to the hose may be ± 10 degrees.
202. Emitting a second infrared ray to the fluid at a third preset position, and receiving a second analog signal at a fourth preset position;
the third preset position and the fourth preset position are located on two sides of the hose, the third preset position is located at the downstream of the first preset position, and the second analog signal is an analog signal of second infrared rays after the second infrared rays penetrate through the fluid.
The wavelength of the second infrared ray may be 850 nanometers, and the emission angle may be ± 10 degrees, that is, an included angle between a connection line between the third preset position and the fourth preset position and a vertical line from the third preset position or the fourth preset position to the hose may be ± 10 degrees.
It should be noted that the first preset position and the third preset position may be located on the same side of the hose or on different sides of the hose, where the first preset position and the third preset position are not limited herein, and when the first preset position and the third preset position are located on the same side of the hose, the second preset position and the fourth preset position are also located on the same side of the hose, and when the first preset position and the third preset position are located on different sides of the hose, the second preset position and the fourth preset position are also located on different sides of the hose.
203. Obtaining the diameter of the suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of the single concave waveform and the preset distance;
the duration of the single concave waveform is the duration of the waveform of the first analog signal or the waveform of the second analog signal from appearance to disappearance of the single concave waveform, the preset distance is the projection length of the straight line distance between the first preset position and the third preset position on the hose, and the projection length can be 16.5 mm.
If bubbles exist in the fluid, when infrared rays pass through the bubbles, voltage digital values of the infrared rays passing through the bubbles are influenced due to refraction and absorption of the bubbles to light, and waveforms of the first analog signal and the second analog signal are in a concave state, so that suspected bubbles can be analyzed according to the waveforms of the first analog signal and the second analog signal, the duration and the preset distance of a single concave waveform.
It should be noted that, because the third preset position is located downstream of the first preset position, if there is a bubble in the fluid, the bubble is reflected on the first analog signal before the bubble is reflected on the second analog signal, so that when a waveform in a concave form appears on the first analog signal, the infrared emission at the third preset position and the analog signal reception at the fourth preset position can be triggered, the success rate of acquiring the second analog signal is increased, and the problem that the second analog signal is still acquired in real time when there is no bubble or few bubbles in the fluid, which causes resource waste, is avoided.
204. And if the diameter of the suspected bubble is larger than the diameter threshold value, determining that the bubble exists in the fluid.
The diameter threshold may be 2 mm, that is, when the diameter of the suspected bubble is greater than 2 mm, it is determined that the suspected bubble is indeed a bubble.
The method and the device can send infrared rays to the fluid in the hose at two different positions on the side edge of the hose, determine the diameter of the suspected bubble according to the received analog signal, the duration of the concave waveform in the analog signal and the distance of the infrared ray emission position, and judge whether the suspected bubble is really a bubble or not according to the diameter.
Fig. 3 is a third flowchart of the calibration method for the volume of infusion liquid according to the embodiment of the present application. Referring to fig. 3, in an embodiment, obtaining the diameter of the suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of the single concave waveform, and the preset distance may include:
301. subtracting the first starting time point from the second starting time point to obtain a first time difference absolute value;
the first starting time point is the time point when the Nth sunken waveform in the waveform of the first analog signal begins to appear, the second starting time point is the time point when the Nth sunken waveform in the waveform of the second analog signal begins to appear, wherein N is an integer larger than or equal to 1, and the sequence of the sunken waveforms is arranged from first to last according to the time sequence.
Because the fluid flows in a relatively closed environment, the form and the quantity of the suspected bubbles do not change significantly when flowing in the hose, that is, the waveforms of the first analog signal and the second analog signal are similar, the sequence of the concave waveform corresponding to the same suspected bubble in the first analog signal is consistent with the sequence of the concave waveform corresponding to the second analog signal, for example, if a certain suspected bubble corresponds to a third concave waveform in the first analog signal, the suspected bubble also corresponds to a third concave waveform in the second analog signal, and the sequence of the concave waveforms in the first analog signal and the second analog signal are arranged from first to last in time sequence.
It should be noted that, the absolute value of the first time difference may also be calculated by selecting a time point when the nth concave waveform in the waveform of the first analog signal completely disappears and a time point when the nth concave waveform in the waveform of the first analog signal completely disappears, which is not limited herein, as long as it is ensured that the same suspected bubble is selected as the time point corresponding to the same state in the concave waveforms of the first analog signal and the second analog signal.
In addition, the number of the sunken waveforms in the waveform of the first analog signal is the number of the suspected bubbles in the fluid flowing through the hose, and the same applies to the second analog signal.
302. Obtaining the flow velocity of the fluid according to the ratio of the preset distance to the absolute value of the first time difference;
the flow rate of the fluid is the flow rate of the suspected bubbles.
303. Obtaining the diameter of the suspected bubble according to the product of the duration of the Nth concave waveform in the waveform of the first analog signal and the flow rate of the fluid; or obtaining the diameter of the suspected bubble according to the product of the duration of the Nth concave waveform in the waveform of the second analog signal and the flow rate of the fluid.
The method comprises the steps of multiplying the duration of the Nth concave waveform in the waveform of the first analog signal by the flow rate of the suspected bubble to obtain the diameter of the suspected bubble, or multiplying the duration of the Nth concave waveform in the waveform of the second analog signal by the flow rate of the suspected bubble to obtain the diameter of the suspected bubble.
According to the embodiment, the difference between the time points when the same suspected bubble is in the same state in the first analog signal and the second analog signal is selected as the time difference when the suspected bubble flows through the hose for the specific distance, the specific distance is divided by the time difference to obtain the flow velocity of the suspected bubble, and finally the flow velocity of the suspected bubble is multiplied by the time taken by the suspected bubble to flow through the infrared ray irradiation point at the first preset position or the third preset position to obtain the diameter of the suspected bubble.
FIG. 4 is a fourth schematic flowchart of a method for calibrating a volume of infusion liquid provided by an embodiment of the present application;
fig. 5 is a schematic waveform diagram illustrating a modified analog signal and a third analog signal provided by an embodiment of the present application translating to a time between a first preset time point and a second preset time point;
referring to fig. 4-5, in one embodiment, deriving the volume of liquid in the volume of fluid flowing into the infusion bag based on the corrected analog signal of bubble formation and the analog signal of the infusion bag formed when the infusion bag is empty may include:
401. and comparing the first analog signal with the second analog signal, and fitting the first analog signal with the second analog signal to obtain a corrected analog signal if the absolute value of the error between the first analog signal and the second analog signal is less than or equal to the error threshold.
The air bubble and the liquid can interfere the received analog signals during the movement process due to the possible existence of impurities on the surface of the air bubble or in the liquid, so that the waveforms of the first analog signal and the second analog signal are similar, but the deviation exists, and therefore when the deviation is within an acceptable range, the first analog signal and the second analog signal can be fitted, noise and clutter can be filtered, and the deviation can be eliminated. And obtaining a corrected analog signal which can better represent the state of the bubble.
402. Emitting a third infrared ray to the infusion bag at a fifth preset position, and receiving a third analog signal at a sixth preset position;
the infusion bag is in an empty bag state, the fifth preset position and the sixth preset position are located on two sides of an inlet pipeline of the infusion bag, and the third analog signal is an analog signal of third infrared rays after the third infrared rays penetrate through the inlet pipeline.
Since the infusion bag is in an empty state, i.e. the inlet pipeline is in an empty state, the waveform of the third analog signal is not interfered by liquid and bubbles and appears as a horizontal line with a fixed voltage digital value.
403. Translating the corrected analog signal and the third analog signal to a position between a first preset time point and a second preset time point to obtain a corrected analog signal section and a third analog signal section;
the first preset time point t1 is a time point when the fluid starts to enter the infusion bag, and the second preset time point t2 is any time point later than the first preset time point when the infusion bag is in an empty bag state. Since the third analog signal is an analog signal measured when the infusion bag is empty, and the corrected analog signal is an analog signal measured when air bubbles and body fluid are present in the tube, the voltage digital value of the third analog signal section is lower than the voltage digital value of the corrected analog signal section, and appears as a horizontal line below the sag waveform of the corrected analog signal section, as shown in fig. 5.
404. Subtracting the first preset time point from the second preset time point to obtain a second time difference absolute value;
405. subtracting the empty liquid voltage digital value of the third analog signal segment from the maximum voltage digital value in the corrected analog signal segment to obtain a voltage digital difference value;
the empty liquid voltage digital value is a voltage digital value of the third analog signal section at any time point when the infusion bag is in an empty bag state, and the waveform of the third analog signal section is a horizontal line, so that the voltage digital values at any time point are equal, that is, the empty liquid voltage digital values at any time point are equal.
406. Obtaining the total area to be processed according to the product of the second time difference absolute value and the voltage digital difference;
407. and obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the total area of the sunken part of the sunken waveform in the waveform of the corrected analog signal section and the total area to be processed.
The total area to be processed represents the fluid volume flowing into the infusion bag from the first preset time to the second preset time, the total area of the sunken part of the sunken waveform in the waveform of the corrected analog signal section represents the bubble volume in the fluid volume, and the bubble volume can be converted into a volume unit and then calculated.
For example, if the total area of the recess part of the recess waveform in the waveform of the modified analog signal section is a, the total area to be processed is B, and the volume of the fluid flowing into the infusion bag from the first preset time to the second preset time is L, the volume of the fluid flowing into the infusion bag is the volume of the fluid
Assuming the target volume is C, the volume of fluid may be subtracted from C to obtain the volume of fluid to be replenished, and the volume of fluid may be replenished based on this as a standard until the volume of fluid in the bag reaches the target volume, completing the calibration of the infusion fluid.
The volume of the fluid flowing into the infusion bag from the first preset time to the second preset time can be obtained through a peristaltic pump which is arranged at the upstream of the first preset position and used for transporting the liquid, the flow rate of the rotation and the transportation of the peristaltic pump is the volume of the fluid, namely, the unit volume of the mobile liquid can be determined in a one-to-one correspondence mode through the unit number of turns of the rotation of the peristaltic pump, and the volume of the fluid flowing into the infusion bag from the first preset time to the second preset time can be obtained through the product of the unit volume and the number of turns of the rotation from the first preset time to the second preset time.
It should be noted that, from the first preset time point t1, sampling may be performed on the corrected analog signal segment and the third analog signal segment at a specific time interval, for example, 0.5 second, and the area of the recess portion of the recess waveform in the waveform of the corrected analog signal segment is accumulated according to the sampling result, and the area between the corrected analog signal segment and the third analog signal segment is accumulated until the last sampling time reaches the second preset time point t2, and the total area of the recess portion of the recess waveform in the waveform of the corrected analog signal segment and the total area to be processed are obtained by the accumulation of the areas, thereby obtaining the liquid volume in the fluid volume flowing into the infusion bag.
Further, the attenuation and amplification intensity of infrared light can be different for different cell fluids, and the fluid components in the hose can be identified by judging the voltage digital values of the cell fluids and performing a large number of data tests and numerical calibration, for example, the voltage digital values of red cell fluids range from 300 to 550, the voltage digital values of monocyte PBMC fluids range from 900 to 1100, and the voltage digital values of saline range from 1200 to 1300.
According to the embodiment, the analog signal of the bubble is corrected by fitting the first analog signal and the second analog signal, the corrected analog signal and the third analog signal of the empty infusion bag are translated to a position between the first preset time point and the second preset time point, the liquid capacity in the fluid capacity is represented by the area formed by the waveforms of the two analog signals, the liquid capacity can be calculated more accurately, the liquid capacity can be supplemented more accurately, and the liquid capacity can reach the target capacity as soon as possible.
FIG. 6 is a fifth flowchart of a calibration method for volume of infusion liquid provided by an embodiment of the present application; referring to fig. 6, in one embodiment, after determining that a bubble is present within the fluid, may include:
601. if the change rate of the slope absolute value of a single sunken waveform in the waveform of the corrected analog signal section from the maximum value to the minimum value is greater than the change rate threshold value, the type of the bubble corresponding to the sunken waveform is a circular bubble;
602. if the change rate of the slope absolute value of the single sunken waveform in the waveform of the corrected analog signal section from the maximum value to the minimum value is larger than zero and smaller than or equal to the change rate threshold value, the bubble type corresponding to the sunken waveform is an ellipse-like bubble;
603. calculating the depression area of a single depression waveform in the waveform of the modified analog signal section according to the type of the bubbles;
and calculating the depressed area of the quasi-circular bubbles by adopting a circular area calculation formula, and calculating the depressed area of the quasi-elliptical bubbles by adopting an elliptical area calculation formula.
604. Summing the depression areas of all single depression waveforms in the corrected analog signal section to obtain a summed depression area;
605. and comparing the total concave area with the total concave area to verify the total concave area.
If the total depressed area is equal to the total depressed area, the verification is passed, and if the total depressed area is not equal to the total depressed area, the verification is not passed.
In this embodiment, since the single concave waveform is similar to the actual shape of the bubble, the shape of the bubble can be determined by correcting the change speed of the slope of the single concave waveform in the waveform of the analog signal segment, when the slope changes faster, it indicates that the curvature of the surface curve of the bubble is larger, the type of the bubble is a quasi-circular bubble, when the slope changes slower, it indicates that the curvature of the surface curve of the bubble is smaller, the type of the bubble is a quasi-elliptical bubble, the concave area of the single concave waveform is calculated according to the type of the bubble, and the total area of the concave portion is verified by using the total concave area, so that the measurement error of the total area of the concave portion of the analog signal segment can be identified and corrected, which is helpful for correcting the total area of the concave portion, so as to obtain more accurate infusion liquid capacity later.
The following describes the infusion liquid volume calibration device provided in the embodiments of the present application, and the infusion liquid volume calibration device described below and the infusion liquid volume calibration method described above may be referred to correspondingly.
FIG. 7 is a schematic structural diagram of an infusion liquid volume calibration device according to an embodiment of the present application;
FIG. 8 is a schematic structural diagram of a bubble determination module in an infusion liquid volume calibration apparatus according to an embodiment of the present application;
referring to fig. 7-8, embodiments of the present application provide an infusion liquid volume calibration device, which may include:
a bubble determination module 701 configured to: detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose;
a liquid volume calculation module 702 configured to: if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a corrected analog signal formed by the bubble and an analog signal formed when the infusion bag is empty;
an infusion liquid calibration module 703 for: and supplementing the liquid volume in the infusion bag according to the difference value between the liquid volume and the target volume until the liquid volume in the infusion bag reaches the target volume, and completing the calibration of the infusion liquid.
The infusion liquid volume calibrating device provided by the embodiment of the application utilizes the model signal formed by the bubbles in the infrared irradiation hose and the model signal formed by the infusion bag in the infrared irradiation empty bag state to obtain the liquid volume flowing into the fluid volume of the infusion bag, so that the deviation of the liquid volume relative to the target volume can be determined and the volume can be supplemented, finally the liquid volume reaches the target volume, the calibration of the liquid volume is completed, when cell therapy is carried out, the dosage of cell liquid input into a human body can be ensured to be sufficient, and the therapeutic effect is ensured.
In one embodiment, the bubble determination module 701 includes:
a first infrared sensor module 801 comprising:
a first infrared-emitting tube for: emitting first infrared rays to the fluid at a first preset position;
a first photoelectric receiver for: receiving a first analog signal at a second preset position;
the first preset position and the second preset position are positioned on two sides of the hose, and the first analog signal is an analog signal of the first infrared ray after passing through the fluid;
a second infrared sensor module 802 comprising:
a second infrared emitting tube for: emitting second infrared rays to the fluid at a third preset position;
a second photoelectric receiver to: receiving a second analog signal at a fourth preset position;
the third preset position and the fourth preset position are positioned on two sides of the hose, the third preset position is positioned at the downstream of the first preset position, and the second analog signal is an analog signal of the second infrared ray after passing through the fluid;
a diameter calculation module 803 for: obtaining the diameter of the suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of a single concave waveform and a preset distance; the duration of the single concave waveform is the duration of the single concave waveform from appearance to disappearance in the waveform of the first analog signal or the waveform of the second analog signal, and the preset distance is the projection length of the linear distance between the first preset position and the third preset position on the hose;
a diameter comparison module 804 to: and if the diameter of the suspected bubble is larger than the diameter threshold value, determining that the bubble exists in the fluid.
Wherein the first infrared sensor module 801 and the second infrared sensor module 802 can be packaged in the same infrared bubble sensor module, which can be a silicon photosensor module.
The first photoelectric receiver and the second photoelectric receiver can be connected to the differential operational amplifier, weak voltage signals are collected and amplified (common-mode interference is reduced through differential signal input amplification), the signal-to-noise ratio is improved, the amplified signals are output to a voltage digital peripheral of the micro control unit MCU to be converted into digital signals, the main control MCU stores bubble diameter data, cell liquid component data and bubble form data into a register, and when the sensor is actually used, the real-time state of the sensor is obtained through a host.
In one embodiment, diameter calculation module 803 is specifically configured to:
subtracting the first starting time point from the second starting time point to obtain a first time difference absolute value; the first starting time point is a time point when the Nth sunken waveform in the waveform of the first analog signal begins to appear, the second starting time point is a time point when the Nth sunken waveform in the waveform of the second analog signal begins to appear, wherein N is an integer greater than or equal to 1, and the sequence of the sunken waveforms is arranged from first to last according to the time sequence;
obtaining the flow velocity of the fluid according to the ratio of the preset distance to the absolute value of the first time difference;
obtaining the diameter of the suspected bubble according to the product of the duration of the Nth concave waveform in the waveform of the first analog signal and the flow rate of the fluid; or obtaining the diameter of the suspected bubble according to the product of the duration of the nth concave waveform in the waveform of the second analog signal and the flow rate of the fluid.
In one embodiment, the liquid volume calculation module 702 is specifically configured to:
comparing the first analog signal with the second analog signal, and fitting the first analog signal with the second analog signal to obtain a corrected analog signal if the absolute value of the error between the first analog signal and the second analog signal is less than or equal to an error threshold;
emitting a third infrared ray to the infusion bag at a fifth preset position, and receiving a third analog signal at a sixth preset position; the infusion bag is in an empty bag state, the fifth preset position and the sixth preset position are located on two sides of an inlet pipeline of the infusion bag, and the third analog signal is an analog signal of the third infrared ray after passing through the inlet pipeline;
translating the corrected analog signal and the third analog signal to a position between a first preset time point and a second preset time point to obtain a corrected analog signal section and a third analog signal section; the first preset time point is the time point when the fluid starts to enter the infusion bag, and the second preset time point is any time point later than the first preset time point when the infusion bag is in an empty bag state;
and obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the first preset time point, the second preset time point, the correction analog signal section and the third analog signal section.
In one embodiment, the liquid volume calculation module 702 is specifically configured to:
subtracting the first preset time point from the second preset time point to obtain a second time difference absolute value;
subtracting the empty liquid voltage digital value of the third analog signal segment from the maximum voltage digital value in the corrected analog signal segment to obtain a voltage digital difference value; the empty liquid voltage digital value is a voltage digital value of the third analog signal section at any time point when the infusion bag is in an empty bag state;
obtaining the total area to be processed according to the product of the second time difference absolute value and the voltage digital difference value;
and obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the total area of the sunken part of the sunken waveform in the waveform of the corrected analog signal section and the total area to be processed.
In one embodiment, an area check module (not shown) is further included for:
if the change rate of the slope absolute value of a single sunken waveform in the waveform of the corrected analog signal section from the maximum value to the minimum value is greater than the change rate threshold value, the type of the bubble corresponding to the sunken waveform is a circular bubble;
if the change rate of the slope absolute value of a single sunken waveform in the waveform of the corrected analog signal section from the maximum value to the minimum value is larger than zero and smaller than or equal to the change rate threshold, the type of the bubble corresponding to the sunken waveform is an ellipse-like bubble;
calculating the depression area of a single depression waveform in the waveform of the correction analog signal section according to the bubble type;
summing the depression areas of all the single depression waveforms in the corrected analog signal section to obtain a summed depression area;
comparing the summed depression area to the total depression area to verify the total depression area.
Fig. 9 illustrates a physical structure diagram of an electronic device, and as shown in fig. 9, the electronic device may include: a processor (processor) 910, a Communication Interface (Communication Interface) 920, a memory (memory) 930 and a Communication bus 940, wherein the processor 910, the Communication Interface 920 and the memory 930 are communicated with each other via the Communication bus 940. Processor 910 may invoke a computer program in memory 930 to perform the steps of an infusion liquid volume calibration method, including, for example:
detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose;
if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a corrected analog signal formed by the bubble and an analog signal formed when the infusion bag is empty;
and supplementing the liquid volume in the infusion bag according to the difference value between the liquid volume and the target volume until the liquid volume in the infusion bag reaches the target volume, and finishing the calibration of the infusion liquid.
Furthermore, the logic instructions in the memory 930 may be implemented in software functional units and stored in a computer readable storage medium when the logic instructions are sold or used as independent products. Based on such understanding, the technical solution of the present application or portions thereof that substantially contribute to the prior art may be embodied in the form of a software product stored in a storage medium and including instructions for causing a computer device (which may be a personal computer, a server, or a network device) to execute all or part of the steps of the method according to the embodiments of the present application. And the aforementioned storage medium includes: a U-disk, a removable hard disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a magnetic disk, or an optical disk, and various media capable of storing program codes.
In another aspect, the present application further provides a computer program product, where the computer program product includes a computer program, the computer program may be stored on a non-transitory computer readable storage medium, and when the computer program is executed by a processor, the computer is capable of executing the steps of the infusion liquid volume calibration method provided in the foregoing embodiments, for example, the steps include:
detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose;
if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a correction analog signal formed by the bubble and an analog signal formed when the infusion bag is empty;
and supplementing the liquid volume in the infusion bag according to the difference value between the liquid volume and the target volume until the liquid volume in the infusion bag reaches the target volume, and finishing the calibration of the infusion liquid.
On the other hand, embodiments of the present application further provide a processor-readable storage medium, where the processor-readable storage medium stores a computer program, where the computer program is configured to cause a processor to perform the steps of the method provided in each of the above embodiments, for example, including:
detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose;
if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a corrected analog signal formed by the bubble and an analog signal formed when the infusion bag is empty;
and supplementing the liquid volume in the infusion bag according to the difference value between the liquid volume and the target volume until the liquid volume in the infusion bag reaches the target volume, and finishing the calibration of the infusion liquid.
The processor-readable storage medium can be any available medium or data storage device that can be accessed by a processor, including, but not limited to, magnetic memory (e.g., floppy disks, hard disks, magnetic tape, magneto-optical disks (MOs), etc.), optical memory (e.g., CDs, DVDs, BDs, HVDs, etc.), and semiconductor memory (e.g., ROMs, EPROMs, EEPROMs, non-volatile memory (NAND FLASH), solid State Disks (SSDs)), etc.
The above-described embodiments of the apparatus are merely illustrative, and the units described as separate parts may or may not be physically separate, and parts displayed as units may or may not be physical units, may be located in one position, or may be distributed on multiple network units. Some or all of the modules may be selected according to actual needs to achieve the purpose of the solution of the present embodiment. One of ordinary skill in the art can understand and implement it without inventive effort.
Through the above description of the embodiments, those skilled in the art will clearly understand that each embodiment may be implemented by software plus a necessary general hardware platform, and may also be implemented by hardware. With this understanding in mind, the above-described technical solutions may be embodied in the form of a software product, which can be stored in a computer-readable storage medium such as ROM/RAM, magnetic disk, optical disk, etc., and includes instructions for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to execute the methods described in the embodiments or some parts of the embodiments.
Finally, it should be noted that: the above embodiments are only used to illustrate the technical solutions of the present application, and not to limit the same; although the present application has been described in detail with reference to the foregoing embodiments, it should be understood by those of ordinary skill in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some technical features may be equivalently replaced; and such modifications or substitutions do not depart from the spirit and scope of the corresponding technical solutions in the embodiments of the present application.
Claims (7)
1. An infusion liquid volume calibration method, comprising:
detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose;
if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a corrected analog signal formed by the bubble and an analog signal formed when the infusion bag is empty;
supplementing the liquid capacity in the infusion bag according to the difference value between the liquid capacity and the target capacity until the liquid capacity in the infusion bag reaches the target capacity, and finishing the calibration of the infusion liquid;
the detecting whether there is a bubble in the fluid flowing through the hose based on the infrared rays includes:
emitting a first infrared ray to the fluid at a first preset position, and receiving a first analog signal at a second preset position; the first preset position and the second preset position are positioned on two sides of the hose, and the first analog signal is an analog signal of the first infrared ray after passing through the fluid;
emitting a second infrared ray to the fluid at a third preset position, and receiving a second analog signal at a fourth preset position; the third preset position and the fourth preset position are positioned on two sides of the hose, the third preset position is positioned at the downstream of the first preset position, and the second analog signal is an analog signal of the second infrared ray after passing through the fluid;
obtaining the diameter of the suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of a single concave waveform and a preset distance; the duration of the single concave waveform is the duration of the single concave waveform from appearance to disappearance in the waveform of the first analog signal or the waveform of the second analog signal, and the preset distance is the projection length of the linear distance between the first preset position and the third preset position on the hose;
if the diameter of the suspected bubble is larger than a diameter threshold value, determining that the bubble exists in the fluid;
the method for obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the corrected analog signal formed by the bubbles and the analog signal formed when the infusion bag is empty comprises the following steps:
comparing the first analog signal with the second analog signal, and fitting the first analog signal with the second analog signal to obtain a corrected analog signal if the absolute value of the error between the first analog signal and the second analog signal is less than or equal to an error threshold;
emitting a third infrared ray to the infusion bag at a fifth preset position, and receiving a third analog signal at a sixth preset position; the infusion bag is in an empty bag state, the fifth preset position and the sixth preset position are located on two sides of an inlet pipeline of the infusion bag, and the third analog signal is an analog signal of the third infrared ray after passing through the inlet pipeline;
translating the corrected analog signal and the third analog signal to a position between a first preset time point and a second preset time point to obtain a corrected analog signal section and a third analog signal section; the first preset time point is a time point when the fluid starts to enter the infusion bag, and the second preset time point is any time point later than the first preset time point when the infusion bag is in an empty bag state;
and obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the first preset time point, the second preset time point, the correction analog signal section and the third analog signal section.
2. The calibration method for the volume of infusion liquid according to claim 1, wherein the obtaining the diameter of the suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of the single concave waveform and the preset distance comprises:
subtracting the first starting time point from the second starting time point to obtain a first time difference absolute value; the first starting time point is the time point when the Nth concave waveform in the waveform of the first analog signal begins to appear, the second starting time point is the time point when the Nth concave waveform in the waveform of the second analog signal begins to appear, wherein N is an integer greater than or equal to 1, and the sequence of the concave waveforms is arranged from first to last according to the time sequence;
obtaining the flow velocity of the fluid according to the ratio of the preset distance to the absolute value of the first time difference;
obtaining the diameter of the suspected bubble according to the product of the duration of the Nth sunken waveform in the waveform of the first analog signal and the flow rate of the fluid; or obtaining the diameter of the suspected bubble according to the product of the duration of the nth concave waveform in the waveform of the second analog signal and the flow rate of the fluid.
3. The method for calibrating infusion liquid volume according to claim 1, wherein obtaining the liquid volume in the volume of fluid flowing into the infusion bag according to the first preset time point, the second preset time point, the modified analog signal section, and the third analog signal section comprises:
subtracting the first preset time point from the second preset time point to obtain a second time difference absolute value;
subtracting the empty liquid voltage digital value of the third analog signal segment from the maximum voltage digital value in the corrected analog signal segment to obtain a voltage digital difference value; the empty liquid voltage digital value is a voltage digital value of the third analog signal section at any time point when the infusion bag is in an empty bag state;
obtaining the total area to be processed according to the product of the second time difference absolute value and the voltage digital difference value;
and obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the total area of the sunken part of the sunken waveform in the waveform of the corrected analog signal section and the total area to be processed.
4. The infusion liquid volume calibration method according to claim 3, wherein said determining that a bubble is present in said fluid comprises:
if the change rate of the slope absolute value of a single sunken waveform in the waveform of the corrected analog signal section from the maximum value to the minimum value is greater than a change rate threshold value, the type of the bubble corresponding to the sunken waveform is a quasi-circular bubble;
if the change rate of the slope absolute value of a single sunken waveform in the waveform of the corrected analog signal section from the maximum value to the minimum value is larger than zero and smaller than or equal to the change rate threshold, the type of the bubble corresponding to the sunken waveform is an ellipse-like bubble;
according to the bubble type, calculating the depression area of a single depression waveform in the waveform of the modified analog signal segment;
summing the depression areas of all the single depression waveforms in the corrected analog signal section to obtain a summed depression area;
comparing the summed recess area to the total recess area to verify the total recess area.
5. An infusion liquid volume calibration device, comprising:
a bubble determination module to: detecting whether bubbles exist in the fluid flowing through the hose according to the infrared rays; the fluid flows to the infusion bag through the hose;
a liquid volume calculation module to: if the bubble exists, obtaining the liquid volume in the fluid volume flowing into the infusion bag according to a corrected analog signal formed by the bubble and an analog signal formed when the infusion bag is empty;
a transfusion liquid calibration module for: supplementing the liquid capacity in the infusion bag according to the difference value between the liquid capacity and the target capacity until the liquid capacity in the infusion bag reaches the target capacity, and finishing the calibration of the infusion liquid;
the bubble determination module includes:
a first infrared sensor module comprising:
a first infrared-emitting tube for: emitting first infrared rays to the fluid at a first preset position;
a first photoelectric receiver for: receiving a first analog signal at a second preset position;
the first preset position and the second preset position are positioned on two sides of the hose, and the first analog signal is an analog signal of the first infrared ray after passing through the fluid;
a second infrared sensor module comprising:
a second infrared emitting tube for: emitting second infrared rays to the fluid at a third preset position;
a second photoelectric receiver for: receiving a second analog signal at a fourth preset position;
the third preset position and the fourth preset position are positioned on two sides of the hose, the third preset position is positioned at the downstream of the first preset position, and the second analog signal is an analog signal of the second infrared ray after passing through the fluid;
a diameter calculation module to: obtaining the diameter of the suspected bubble according to the waveform of the first analog signal, the waveform of the second analog signal, the duration of a single concave waveform and a preset distance; the duration of the single concave waveform is the duration of the single concave waveform from appearance to disappearance in the waveform of the first analog signal or the waveform of the second analog signal, and the preset distance is the projection length of the linear distance between the first preset position and the third preset position on the hose;
a diameter comparison module to: if the diameter of the suspected bubble is larger than a diameter threshold value, determining that the bubble exists in the fluid;
the method for obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the corrected analog signal formed by the bubbles and the analog signal formed when the infusion bag is empty comprises the following steps:
comparing the first analog signal with the second analog signal, and fitting the first analog signal with the second analog signal to obtain a corrected analog signal if the absolute value of the error between the first analog signal and the second analog signal is less than or equal to an error threshold;
emitting a third infrared ray to the infusion bag at a fifth preset position, and receiving a third analog signal at a sixth preset position; the infusion bag is in an empty bag state, the fifth preset position and the sixth preset position are located on two sides of an inlet pipeline of the infusion bag, and the third analog signal is an analog signal of the third infrared ray after passing through the inlet pipeline;
translating the corrected analog signal and the third analog signal to a position between a first preset time point and a second preset time point to obtain a corrected analog signal section and a third analog signal section; the first preset time point is a time point when the fluid starts to enter the infusion bag, and the second preset time point is any time point later than the first preset time point when the infusion bag is in an empty bag state;
and obtaining the liquid volume in the fluid volume flowing into the infusion bag according to the first preset time point, the second preset time point, the correction analog signal section and the third analog signal section.
6. An electronic device comprising a processor and a memory storing a computer program, wherein the processor when executing the computer program implements the steps of the method of calibrating an infusion liquid volume of any one of claims 1 to 4.
7. A non-transitory computer readable storage medium having stored thereon a computer program, wherein the computer program when executed by a processor implements the steps of the infusion liquid volume calibration method according to any one of claims 1 to 4.
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| JP2004325350A (en) * | 2003-04-25 | 2004-11-18 | Jms Co Ltd | Device for detecting bubble |
| CN202802342U (en) * | 2012-08-29 | 2013-03-20 | 深圳市好克光电仪器有限公司 | Infusion pump and bubble detecting device |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| GB0405596D0 (en) * | 2004-03-12 | 2004-04-21 | Imi Vision Ltd | Fluid flow monitoring device |
| US7343943B2 (en) * | 2004-05-13 | 2008-03-18 | Forhealth Technologies, Inc. | Medication dose underfill detection system and application in an automated syringe preparing system |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2004325350A (en) * | 2003-04-25 | 2004-11-18 | Jms Co Ltd | Device for detecting bubble |
| CN202802342U (en) * | 2012-08-29 | 2013-03-20 | 深圳市好克光电仪器有限公司 | Infusion pump and bubble detecting device |
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