CN115364305A

CN115364305A - Infusion pump system, infusion pump monitoring system and method

Info

Publication number: CN115364305A
Application number: CN202210551970.5A
Authority: CN
Inventors: 张鹏; 何广涛; 杨韬睿
Original assignee: Shenzhen Mindray Scientific Co Ltd
Current assignee: Shenzhen Mindray Scientific Co Ltd
Priority date: 2021-05-18
Filing date: 2022-05-18
Publication date: 2022-11-22

Abstract

An infusion pump system, an infusion pump monitoring system, an infusion method and an infusion monitoring method, wherein a real-time flow rate of liquid in an infusion tube is obtained through a flow rate monitoring part; and a displacement signal representing the displacement of the flow rate monitoring component relative to the preset direction is obtained through a displacement monitoring component, a target motor rotating speed corresponding to the target flow rate of the liquid in the infusion tube is obtained at least according to the real-time flow rate and the displacement signal, and the target motor rotating speed is controlled to work to drive the liquid in the infusion tube to controllably flow, or the real-time flow rate is output when the displacement signal meets a first preset condition. The invention can realize accurate control of the infusion precision.

Description

Infusion pump system, infusion pump monitoring system and method

Technical Field

The invention relates to an infusion pump system, an infusion pump monitoring system, an infusion liquid method and an infusion liquid monitoring method.

Background

Infusion is one of the therapeutic means for directly entering the human body as a medicine, and the liquid in the infusion tube can be driven to controllably flow through an infusion pump system, for example, the medicine is injected into the human body at a constant speed; it is therefore necessary to monitor and/or control the status of the infusion process.

Disclosure of Invention

To solve the above problems, the present invention provides an infusion pump system, an infusion pump monitoring system, an infusion liquid method, and an infusion liquid monitoring method, which are described in detail below.

According to a first aspect, there is provided an infusion pump system comprising:

the peristaltic extrusion mechanism is arranged on the infusion tube and is used for extruding the infusion tube so as to drive liquid in the infusion tube to flow; the infusion tube is used for communicating an infusion bag which provides liquid to be infused;

the driving mechanism is used for driving the peristaltic extrusion mechanism to extrude the infusion tube;

the flow rate and speed monitoring component is used for monitoring the real-time flow rate and speed of the liquid in the infusion tube;

the displacement monitoring component is used for detecting the displacement of the flow speed monitoring component relative to a preset direction and outputting a corresponding displacement signal;

the processor obtains the target motor rotating speed of the driving mechanism corresponding to the target flow rate of the liquid in the infusion tube at least according to the real-time flow rate and the displacement signal, and controls the driving mechanism to drive the peristaltic squeezing mechanism to squeeze the infusion tube at the target motor rotating speed.

In one embodiment, the processor obtains a target motor rotation speed of the driving mechanism corresponding to a target flow rate of the liquid in the infusion tube at least according to the real-time flow rate and the displacement signal, and includes:

after the infusion is started, the driving mechanism is controlled to drive the peristaltic extrusion mechanism to extrude the infusion tube at an initial rotating speed;

acquiring real-time flow speed corresponding to the initial rotating speed through the flow speed monitoring part;

matching with one or more pre-stored consumable rotating speed-flow speed relations according to the initial rotating speed and the consumable rotating speed-flow speed relation of the corresponding real-time flow speed;

selecting the successfully matched consumable rotating speed-flow rate relation as the current consumable rotating speed-flow rate relation; and

calculating a target motor rotating speed corresponding to the target flow speed of the liquid in the infusion tube according to the current consumable rotating speed-flow speed relation; and when the initial rotating speed and the consumable rotating speed-flow speed relation of the real-time flow speed corresponding to the initial rotating speed fail to be matched with one or more pre-stored consumable rotating speed-flow speed relations, the processor is further used for generating prompt information, and the prompt information is used for prompting a user to update the relation library and/or carry out troubleshooting.

In one embodiment, the processor further obtains a real-time motor rotation speed and a corresponding real-time flow rate, and generates first alarm information when a consumable rotation speed-flow rate relation between the real-time motor rotation speed and the corresponding real-time flow rate exceeds a preset range.

In one embodiment, the processor obtains a target motor rotation speed of the driving mechanism corresponding to a target flow rate of the liquid in the infusion tube according to the real-time flow rate and the displacement signal, and includes:

after the infusion is started, the driving mechanism is controlled to drive the peristaltic extrusion mechanism to extrude the infusion tube at an initial rotating speed; and

calculating a target motor rotation speed of the driving mechanism by taking the flow rate regulation period as a time unit;

wherein the processor calculating the target motor rotation speed of the driving mechanism in units of flow rate adjustment cycles includes:

acquiring the motor rotating speed of the current flow speed adjusting period, and acquiring the real-time flow speed of the current flow speed adjusting period through the flow speed monitoring part;

calculating the consumable rotating speed-flow speed relation of the current flow speed regulation period according to the motor rotating speed of the current flow speed regulation period and the corresponding real-time flow speed;

for the next flow rate regulation period of the current flow rate regulation period, calculating the consumable rotating speed-flow rate relation of the next flow rate regulation period according to the consumable rotating speed-flow rate relation of at least one previous flow rate regulation period of the next flow rate regulation period;

and calculating the target motor rotating speed of the next flow speed adjusting period according to the target flow speed of the liquid in the infusion tube and the consumable rotating speed-flow speed relation of the next flow speed adjusting period.

In one embodiment, the processor further generates a first alarm message when the consumable rotation speed-flow speed relationship of the current flow rate adjustment period exceeds a preset range.

In one embodiment, after the infusion is started, the processor calculates the initial rotation speed according to the target flow speed and an initial default consumable rotation speed-flow speed relation.

when the displacement signal output by the displacement monitoring component meets a first preset condition, calculating the target motor rotating speed of the driving mechanism according to the real-time flow rate; and/or

When the displacement signal output by the displacement monitoring component meets a second preset condition, calculating the target motor rotating speed of the driving mechanism according to the real-time flow speed and the displacement signal;

the processor is further configured to: and when the displacement signal output by the displacement monitoring component meets a third preset condition, stopping obtaining the target motor rotating speed of the driving mechanism according to the real-time flow speed and the displacement signal, and/or generating second alarm information.

In one embodiment, the processor calculates a target motor speed of the driving mechanism according to the real-time flow rate and the displacement signal, and includes:

compensating the real-time flow speed according to the displacement signal, and calculating the target motor rotating speed of the driving mechanism based on the compensated real-time flow speed;

or,

and calculating the intermediate motor rotating speed of the driving mechanism according to the real-time flow speed, and compensating the calculated intermediate motor rotating speed according to the displacement signal to obtain the target motor rotating speed.

In one embodiment, the first predetermined condition is that the displacement signal is smaller than a first threshold; the second preset condition is that the displacement signal is larger than a second threshold and smaller than a third threshold; the third preset condition is that the displacement signal is greater than a fourth threshold value; the first threshold is less than or equal to a second threshold, and the third threshold is less than or equal to a fourth threshold.

In one embodiment, the displacement monitoring component comprises an angle sensor and/or a motion sensor; the displacement signal comprises an angle signal and/or a movement signal, wherein the angle sensor is used for detecting the angle signal of the flow rate monitoring component relative to a preset direction, and the movement sensor is used for detecting the movement signal of the flow rate monitoring component relative to the preset direction.

In one embodiment:

the flow rate and speed monitoring part comprises a weight change monitoring part which is used for being connected with the infusion bag and monitoring the weight change of the infusion bag; the flow speed monitoring part calculates the real-time flow speed according to the weight change of the infusion bag; or,

the flow speed monitoring part comprises a pipe diameter measuring part which is used for measuring the pipe diameter of the infusion pipe; the flow rate monitoring part calculates the real-time flow rate by measuring the pipe diameter of the infusion pipe.

In one embodiment, the pipe diameter measuring component comprises a hall sensor, or a thin film pressure sensor.

In one embodiment, the infusion pump system further comprises a sleep wake-up unit; the dormancy awakening unit is used for detecting the suspension state of an infusion bag of the infusion pump system, and the processor is further used for: when the infusion pump system does not hang an infusion bag, the flow speed monitoring part is controlled to enter a sleep mode, and when the infusion pump system is detected to hang an infusion bag, the flow speed monitoring part is controlled to exit the sleep mode.

In one embodiment, the infusion pump system further comprises RF circuitry that converts electrical signals to or from electromagnetic waves and communicates with a communication network and other communication devices via the electromagnetic waves.

In one embodiment, the infusion pump system further comprises a battery unit for supplying power.

According to a second aspect, an embodiment provides an infusion pump monitoring system comprising:

the flow rate monitoring component is used for monitoring the real-time flow rate of liquid in an infusion tube of the infusion pump;

displacement monitoring means for detecting a displacement signal of the flow rate monitoring means with respect to a predetermined direction; and the number of the first and second groups,

and the processor is used for outputting the real-time flow speed when the displacement signal output by the displacement monitoring part meets a first preset condition.

In an embodiment, the first predetermined condition is that the displacement signal is smaller than a first threshold.

In an embodiment, the processor is further configured to compensate the real-time flow rate according to the displacement signal when the displacement signal output by the displacement monitoring component satisfies a second preset condition, and output the compensated real-time flow rate.

In an embodiment, the second preset condition is that the displacement signal is greater than a second threshold and less than a third threshold.

In one embodiment, the processor is further configured to issue an alarm when the displacement signal output by the displacement monitoring component satisfies a third preset condition.

In one embodiment, the infusion pump monitoring system further comprises a fluid stop control component; and when the displacement signal output by the displacement monitoring part meets a third preset condition, the liquid stopping control part stops the liquid of the infusion tube.

In an embodiment, the third predetermined condition is that the displacement signal is greater than a fourth threshold.

In one embodiment, the displacement monitoring component comprises an angle sensor and/or a motion sensor; the displacement signal comprises an angle signal and/or a motion signal, wherein the angle sensor is used for detecting the angle signal of the flow rate monitoring component relative to a preset direction, and the motion sensor is used for detecting the motion signal of the flow rate monitoring component relative to the preset direction.

In one embodiment:

the flow speed monitoring part comprises a weight change monitoring part which is connected with the infusion bag and used for monitoring the weight change of the infusion bag; the flow rate and speed monitoring part calculates real-time flow rate and speed according to the weight change of the infusion bag; or,

In one embodiment, the infusion pump monitoring system further comprises a sleep wake-up unit; the dormancy awakening unit is used for detecting the suspension state of the infusion bag of the infusion pump, and the processor is further used for: when the infusion pump does not suspend an infusion bag, the flow speed monitoring part is controlled to enter a sleep mode, and when the infusion pump is detected to suspend the infusion bag, the flow speed monitoring part is controlled to exit the sleep mode.

In one embodiment, the infusion pump monitoring system further comprises an RF circuit that converts electrical signals to or from electromagnetic waves and communicates with a communication network and other communication devices via electromagnetic waves.

In one embodiment, the infusion pump monitoring system further comprises a battery unit for supplying power.

According to a third aspect, an embodiment provides an infusion liquid method, which is applied to an infusion pump system for driving liquid in an infusion tube to controllably flow, wherein the infusion tube is communicated with an infusion bag for providing the liquid to be infused; the infusion method comprises the following steps:

acquiring the real-time flow rate of the liquid in the infusion tube through a flow rate monitoring part;

acquiring a displacement signal representing the displacement of the flow speed monitoring component relative to a preset direction through a displacement monitoring component;

and obtaining a target motor rotating speed corresponding to the target flow rate of the liquid in the infusion tube at least according to the real-time flow rate and the displacement signal, and controlling the target motor rotating speed to work so as to drive the liquid in the infusion tube to controllably flow.

According to a fourth aspect, an embodiment provides an infusion liquid monitoring method applied to an infusion pump system for driving a controllable flow of liquid in an infusion tube; the infusion liquid monitoring method comprises the following steps:

and outputting the real-time flow speed when the displacement signal meets a first preset condition.

According to the infusion pump system, the infusion pump monitoring system, the infusion liquid method and the infusion liquid monitoring method of the embodiment, accurate control of infusion precision can be achieved.

Drawings

FIG. 1 is a schematic diagram of an embodiment of an infusion pump system;

FIG. 2 is a schematic diagram of an embodiment of an infusion pump system;

FIG. 3 is a schematic diagram of an embodiment of an infusion pump system;

FIG. 4 is a schematic diagram of an embodiment of an infusion pump system;

FIG. 5 is a schematic diagram of an embodiment of an infusion pump system;

FIG. 6 is a schematic diagram of an embodiment of an infusion pump system;

FIG. 7 (a) is a schematic diagram of an embodiment of a flow rate and speed monitoring component; FIG. 7 (b) is a schematic diagram of an embodiment of a flow rate and speed monitoring component;

FIG. 8 is a schematic structural diagram of a displacement monitoring unit according to an embodiment;

FIG. 9 (a) is a diagram showing the relationship between the rotational speed and the flow rate of the consumable according to an embodiment;

FIG. 9 (b) a graph of the real-time flow rate over a longer period of time for one embodiment;

FIG. 10 is a schematic diagram of an embodiment of an infusion pump system;

FIG. 11 is a schematic diagram illustrating a portion of an embodiment of an infusion pump system;

FIG. 12 is a schematic diagram of an embodiment of an infusion pump monitoring system;

FIG. 13 is a schematic diagram of an embodiment of an infusion pump monitoring system;

FIG. 14 is a schematic diagram of an embodiment of an infusion pump monitoring system;

FIG. 15 is a flow chart of an infusion method of an embodiment;

fig. 16 is a flow chart of an infusion fluid monitoring method of an embodiment.

Detailed Description

The present invention will be described in further detail with reference to the following detailed description and accompanying drawings. Wherein like elements in different embodiments are numbered with like associated elements. In the following description, numerous specific details are set forth in order to provide a better understanding of the present application. However, those skilled in the art will readily recognize that some of the features may be omitted or replaced with other elements, materials, methods in different instances. In some instances, certain operations related to the present application have not been shown or described in detail in order to avoid obscuring the core of the present application from excessive description, and it is not necessary for those skilled in the art to describe these operations in detail, so that they may be fully understood from the description in the specification and the general knowledge in the art.

Furthermore, the features, operations, or characteristics described in the specification may be combined in any suitable manner to form various embodiments. Also, the various steps or actions in the method descriptions may be transposed or transposed in order, as will be apparent to one of ordinary skill in the art. Thus, the various sequences in the specification and drawings are for the purpose of describing certain embodiments only and are not intended to imply a required sequence unless otherwise indicated where such sequence must be followed.

The numbering of the components as such, e.g., "first", "second", etc., is used herein only to distinguish the objects as described, and does not have any sequential or technical meaning. The term "connected" and "coupled" when used in this application, unless otherwise indicated, includes both direct and indirect connections (couplings).

There are many problems with monitoring and/or controlling the status of an infusion process, and several examples are tried below.

For example, the manufacturers of the current infusion tube and infusion pump are different manufacturers, which results in that the speed of the infusion liquid needs to be adjusted by controlling the pump after the infusion pump is installed on the infusion tube when a user uses the infusion tube. For example, the pump extrudes the infusion tube to infuse through peristalsis, but the infusion tubes produced by different consumable manufacturers have different specifications, different thicknesses, different materials, different thicknesses, different hardness degrees and the like, so that when the pump adopts the same parameters to drive and extrude the infusion tube to infuse, the speeds of liquid in the infusion tube are different, and the new infusion tube is used to correct again every time, so that the infusion precision can be realized

For another example, when monitoring the state of the infusion tube, the monitoring is susceptible to many other factors, which results in inaccurate or meaningless data obtained by monitoring.

For another example, the infusion precision of the existing infusion pump is guaranteed by mechanical precision, the infusion tube is fatigued due to long-time infusion, and the infusion precision cannot be guaranteed.

One important parameter of the infusion-related parameters is the infusion completion time, for example, when 1 hour is required to complete the infusion, if the infusion is completed too fast (for example, 40 minutes) or too slow (for example, 80 minutes), the treatment effect is affected, so that the accuracy of the infusion needs to be controlled, and the infusion completion time is not greatly deviated and is within an acceptable range.

One solution may be to employ a droplet detection device for an infusion dropper, for example using an infrared emitting device and an infrared receiving device, mounted on both sides between the drip opening and the liquid level of the infusion dropper. The infrared receiving device continuously detects the energy of the light from the infrared emitting device, and when no liquid drop falls, the energy value is a steady-state energy value; when liquid drops fall and pass through a connecting line of the infrared transmitting device and the infrared receiving device, the energy of light rays detected by the infrared receiving device is reduced due to the fact that the liquid drops shield the light rays. Based on the energy drop, it is possible to identify whether or not a droplet has fallen. Medical personnel can judge whether current infusion is unusual according to the data of liquid drop check out test set. For example, when no liquid drop is detected, the current infusion is abnormal; for another example, the medical staff can roughly grasp the current liquid flow rate in the pipeline according to the speed of the liquid drops.

Specifically, the dropping method, that is, the flow rate of the liquid is determined by the number of drops per unit time; however, there are some problems, one is that the volume of each drop of liquid is a preset estimated value, and the other is that the flow rate of the liquid in the infusion tube cannot really reflect a flow rate input to a patient when considering the problems of the tube diameter of the input tube, etc., for example, in the infusion state that the tube diameter is large but the flow rate is small, the flow rate entering the patient is larger than the infusion state that the tube diameter is small but the flow rate is large; in our treatment regimen, a relatively large parameter is that the current dosage needs to be infused into the patient within a specified time, not too early, nor too late.

In addition, since the sensor used in the detection device of the droplet detection device is an optical device or the like, the device is very easily interfered by external light, and thus the droplet can not be accurately detected.

In another embodiment, the concept of flow rate is proposed, the volume of change per unit time. Therefore, the unit of the flow rate can be ml/h, ml/min, ml/s and the like, and an infusion pump system and a corresponding method are provided, so that the infusion pump system can adapt to different infusion tubes, manual adjustment is not needed, and a self-calibration scheme without tube selection is realized.

Therefore, in some embodiments, the inventor considers that an external weighing sensor is introduced, an external pluggable or wireless connected weighing sensor of the infusion pump transmits flow monitoring information to the pump, the pump controls the motor according to flow adjustment, and rotation speed adjustment, infusion to be completed, empty bottle reminding and the like are completed.

In some embodiments, an infusion pump system is disclosed, which may be any medical device that performs a user-set infusion operation based on a user-configured fluid substance, or fluid (e.g., medical fluid), that is controllably delivered to a patient.

Referring to fig. 1, 2 and 3, an infusion pump system in some embodiments of the invention includes a peristaltic squeezing mechanism 1000, a drive mechanism 1100, a flow rate monitoring component 1200 and a processor 1300; in some embodiments, the infusion pump system may further include a displacement monitoring component 1500; in some embodiments, the infusion pump system may further include a sleep wake-up unit 1700; in some embodiments, the infusion pump system may further include a battery unit 1800; in some embodiments, the infusion pump system may further include a display component 1400; the infusion pump system in some embodiments may further comprise one or more of a drop count sensor 1600, a pressure sensor 1610, a bubble sensor 1620, and RF circuitry 1630, all of which may be communicatively coupled to the processor 1300, such as by wired or wireless communication.

Referring to fig. 4 or fig. 5, in some embodiments, the peristaltic squeezing mechanism 1000 is disposed on the infusion tube 1001 for squeezing the infusion tube 1001 to drive the liquid in the infusion tube 1001 to flow; wherein the infusion tube 1001 is communicated with an infusion bag 1002 for providing liquid to be infused. That is, the infusion bag 1002 contains the liquid (e.g., medical liquid) to be infused, the infusion bag 1002 is communicated with the infusion tube 1001, and the liquid in the infusion bag 1002 enters, for example, a human body through the infusion tube 1001; and the peristaltic squeezing mechanism 1000 may drive the fluid in the infusion tube 1001 in a controlled manner.

In some embodiments, referring to fig. 6, the peristaltic compression mechanism 1000 includes a cam shaft 1003, a set of pump blades 1004, and a compression plate 1005. During the rotation of the camshaft 1003, the pump blade group 1004 on the camshaft 1003 performs a linear reciprocating motion, that is, the pump blades on the pump blade group 1004 sequentially perform a linear reciprocating motion. The pump plate assembly 1004 cooperates with the pressing plate 1005 to sequentially and reciprocally press and release the outer wall of the infusion tube 1001, so as to drive the liquid in the infusion tube 1001 to continuously flow in a directional manner.

The driving mechanism 1100 is used for driving the peristaltic squeezing mechanism 1000 to squeeze the infusion tube 1001. For example, the driving mechanism 1100 is used to drive the peristaltic squeezing mechanism 1000 to squeeze the infusion tube 1001 according to a control parameter. In some embodiments, the control parameter may be, for example, a motor speed or position parameter. In some embodiments, the driving mechanism 1100 can include a power component, which can be an electromagnetic device that can convert or transmit electric energy according to the law of electromagnetic induction, such as a Permanent Magnet (PM) motor, a reactive (VR) motor, a Hybrid (HB) motor, and the like, and the peristaltic squeezing mechanism 1000 can be driven by the power component to move, so as to squeeze the infusion tube 1001. Further, the drive mechanism 1100 may also include one or more force transmission/conversion components to cooperate with the power components; specifically, when the power component moves, the peristaltic squeezing mechanism 1000 is driven to move by the one or more force transmission/conversion components, so as to squeeze the infusion tube 1001, and drive the liquid in the infusion tube 1001 to flow. In some embodiments, the one or more force transmission/conversion components may include, for example, gears, transmission shafts, lead screws, nuts or sliders, or the like.

One driving procedure is such that: a processor 1300 in the infusion pump system sends out instructions or control parameters such as the rotating speed or position of a motor, so that the driving mechanism 1100 works according to the specified rotating speed and the rotating direction of the motor, and the driving mechanism 1100 drives a cam shaft 1003 in a peristaltic squeezing mechanism 1000 connected with the driving mechanism to rotate in the rotating process; during the rotation of the camshaft 1003, the pump blade group 1004 on the camshaft 1003 performs linear reciprocating motion, that is, the pump blades on the pump blade group 1004 sequentially perform linear reciprocating motion. The pump plate assembly 1004 cooperates with the pressing plate 1005 to sequentially and reciprocally press and release the outer wall of the infusion tube 1001, so as to drive the liquid in the infusion tube 1001 to continuously flow in a directional manner. A speed reducing mechanism can be further arranged between the driving mechanism 1100 and the camshaft 1003 in the peristaltic extrusion mechanism 1000 to ensure that the rotation speed of the pump blade set 1004 is stable and uniform.

The flow rate monitoring unit 1200 is used to monitor the real-time flow rate of the liquid in the infusion tube, i.e. the volume of the liquid changing per unit time. The real-time flow rate may therefore be in ml/min and ml/s, etc. In some embodiments, the flow rate monitoring component 1200 is configured to calculate a real-time flow rate based on a change in weight of the bag 1002. In some embodiments, referring to fig. 7 (a), the flow rate monitoring unit 1200 includes a weight change monitoring unit 1201 for connecting to the bag 1002 and monitoring a change in weight of the bag 1002. The weight change monitoring part 1201 may be designed to monitor the weight change of the infusion bag 1002 by hanging, for example, the weight change monitoring part 1201 may comprise a tension sensor, so that the weight change monitoring part 1201 may not only monitor the weight change of the infusion bag 1002, but also serve as a hanging or fixing device for the infusion bag, which will be described below. After the weight change of the infusion bag 1002 is obtained, the flow rate monitoring part 1200 may convert the weight change into a volume change, and then divide the volume change by corresponding time to obtain a real-time flow rate, thereby realizing monitoring of the real-time flow rate.

The flow rate monitoring part 1200 may perform conversion in accordance with uniform density when converting a weight change into a volume change, for example, uniformly regarding the density of a liquid as the density of water or physiological saline; for more accurate monitoring, the current density of the liquid may also be obtained, and then the weight change is converted into a volume change according to the current density of the liquid. In order to conveniently obtain the current density of the fluid, the density of a plurality of infusion drugs (referred to as drug solutions for short) may be measured in advance and then stored in the flow rate monitoring part 1200, and the flow rate monitoring part 1200 obtains the density corresponding to the fluid in the current infusion bag 1002 according to the ID (for example, the name of the drug solution) of the drug solution. In some embodiments, the flow rate monitoring component 1200 may obtain the medical fluid ID (e.g., medical fluid name) in one or more of the following ways:

the user manually inputs a medical fluid ID (e.g., medical fluid name);

the processor 1300 identifies a drug fluid ID (e.g., drug fluid name) from the drug data management system or from the infusion protocol and sends it to the flow rate monitoring component 1200; alternatively, the flow rate monitoring section 1200 identifies the drug solution ID (e.g., drug solution name) directly from the drug data management system or from the infusion protocol;

the flow rate monitoring part 1200 acquires a drug solution ID (for example, drug solution name) by means of near field communication; for example, the flow rate monitoring unit 1200 may include an RF reader for reading an RF tag provided on the iv bag 1002 to acquire a medical fluid ID (e.g., a medical fluid name); the RF tag on the bag 1002 may include a medical fluid ID (e.g., a name of the medical fluid), and may also include other parameters, such as a validity period of the medical fluid, a total amount of the medical fluid, etc.

Thus, in some embodiments, the flow rate monitoring component 1200 obtains the weight change, obtains the density of the fluid (or the medical fluid), converts the weight change to a volume change based on the density of the fluid, and calculates the real-time flow rate based on the volume change.

In some embodiments, the flow rate monitoring component 1200 is also used to calculate one or more of a remaining amount of fluid, an entered amount of fluid, an infused time, and a remaining infusion time of the infusion bag 1002.

In some embodiments, the processor 1300 calculates one or more of the remaining amount of the infusion bag 1002, the inputted amount of the liquid, the infused time, and the remaining infusion time based on the weight change acquired by the flow rate monitoring part 1200.

In some embodiments, referring to fig. 7 (b), the flow rate monitoring unit 1200 includes a tube diameter measuring unit 1203, the tube diameter measuring unit 1203 is used for measuring the tube diameter of the infusion tube 1001, so that the flow rate monitoring unit 1200 calculates the real-time flow rate by measuring the tube diameter of the infusion tube 1001. In some embodiments, the pipe diameter measuring member 1203 includes a hall sensor, or a thin film pressure sensor. In such an example, the flow rate speed monitor 1200 is provided in the infusion tube 1001, and thus when the infusion tube 1001 is shaken or tilted, the flow rate speed monitor 1200 is also shaken or tilted, and displacement occurs.

The displacement monitoring part 1500 is used to detect the displacement of the flow rate and speed monitoring part 1200 with respect to a predetermined direction, such as a vertical direction, and output a corresponding displacement signal. In some embodiments, referring to fig. 8, the displacement monitoring component 1500 includes an angle sensor 1501 and/or a motion sensor 1502; the displacement signal includes an angle signal and/or a motion signal, wherein the angle sensor 1501 is used to detect an angle signal of the flow rate monitoring part 1200 with respect to a predetermined direction, for example, a vertical direction, and the motion sensor 1502 is used to detect a motion signal of the flow rate monitoring part 1200 with respect to a predetermined direction, for example, a vertical direction.

In clinic, a medical pump is commonly used for medicine infusion with accurate flow, a motor is arranged in the medical pump, and the motor can drive a mechanical structure to move to extrude an infusion tube, so that the directional movement of liquid in the infusion tube is realized; when the same infusion apparatus is used for infusion, the running rotating speed of the motor and the outflow flow rate of the infusion pump have a certain relation, namely the rotating speed of the consumable material-flow rate relation mentioned herein, for example, fig. 9 (a) is an example.

During long-time infusion, the elasticity of the infusion tube is gradually reduced due to the extrusion of an external force, so that when the infusion tube works at the same motor speed, the liquid outlet flow rate of the infusion pump system is gradually reduced, namely the relationship between the liquid outlet flow rate of the infusion pump system and the motor speed is fixed in a short time, but the proportional relationship between the liquid outlet flow rate and the motor speed is changed along with the increase of the infusion time, for example, fig. 9 (b) is an example and illustrates a real-time flow rate curve graph for a long time.

One solution is to calibrate an infusion pump system in advance, obtain and store the relation between the motor rotating speed and the liquid outlet flow rate when the infusion pump system is used for injecting liquid; when the medical staff uses the infusion set, the brand and the type of the infusion set corresponding to the infusion pump system used by the medical staff are selected on the pump, and the infusion pump system automatically reads the relation between the rotating speed and the flow rate of the built-in motor; after the flow rate is set, the medical staff starts the infusion, and the infusion pump system automatically calculates the motor rotating speed corresponding to the flow rate according to the built-in calibration information; because clinically used infusion apparatus consumables are of a plurality of brands, different manufacturers also have various types of infusion apparatus, and calibration information of various infusion apparatus is often built in the pump when the pump leaves a factory in order to improve product competitiveness; based on this workflow, infusion velocity of flow precision relies on medical personnel's operation, and when selecting the transfusion system and the in-service use transfusion system and not matching, the infusion velocity of flow will produce great error. Inaccurate flow rate will affect the quality of treatment, delaying treatment if not, and life risk if not.

In some embodiments of the present invention, the processor 1300 obtains a target motor rotation speed of the driving mechanism 1100 corresponding to a target flow rate of the liquid in the infusion tube 1001 at least according to the real-time flow rate and the displacement signal, and controls the driving mechanism 1100 to drive the peristaltic squeezing mechanism 1000 to squeeze the infusion tube 1001 at the target motor rotation speed; this will be explained in detail below.

In some embodiments, after the infusion is initiated, the processor 1300 controls the driving mechanism 1100 to drive the peristaltic squeezing mechanism 1000 at an initial rotation speed to squeeze the infusion tube 1001; the processor 1300 obtains a real-time flow rate corresponding to the initial rotation speed through the flow rate monitoring part 1200; the processor 1300 matches one or more pre-stored consumable rotation speed-flow speed relations according to the initial rotation speed and the consumable rotation speed-flow speed relation of the real-time flow speed corresponding to the initial rotation speed; the processor 1300 selects the successfully matched consumable material rotating speed-flow speed relation as the current consumable material rotating speed-flow speed relation; the processor 1300 calculates a target motor rotation speed corresponding to the target flow rate of the liquid in the infusion tube 1001 according to the current consumable rotation speed-flow rate relationship. In some embodiments, when the consumable rotational speed-flow rate relationship between the initial rotational speed and the real-time flow rate corresponding to the initial rotational speed fails to match one or more consumable rotational speed-flow rate relationships stored in advance, the processor 1300 is further configured to generate a prompt message, where the prompt message is used to prompt the user to update the relationship library and/or perform troubleshooting. In some embodiments, the processor 1300 further obtains a real-time motor rotation speed and a corresponding real-time flow rate, and generates the first alarm information when a consumable rotation speed-flow rate relationship between the real-time motor rotation speed and the corresponding real-time flow rate exceeds a preset range.

In some embodiments, after initiating the infusion, the processor 1300 controls the driving mechanism 1100 to drive the peristaltic squeezing mechanism 1000 at an initial rotation speed to squeeze the infusion tube 1001; the processor 1300 calculates a target motor rotation speed of the driving mechanism in a unit of time of the flow rate adjustment period; specifically, the method comprises the following steps: the processor 1300 obtains the motor speed of the current flow rate adjustment period, and obtains the real-time flow rate of the current flow rate adjustment period through the flow rate monitoring part 1200; the processor 1300 calculates the consumable rotating speed-flow speed relation of the current flow speed regulation period according to the motor rotating speed of the current flow speed regulation period and the corresponding real-time flow speed; for the next flow rate adjustment period of the current flow rate adjustment period, the processor 1300 calculates the consumable rotation speed-flow rate relationship of the next flow rate adjustment period according to the consumable rotation speed-flow rate relationship of at least one previous flow rate adjustment period of the next flow rate adjustment period; the processor 1300 calculates the target motor speed in the next flow rate adjustment period according to the target flow rate of the liquid in the infusion tube 1001 and the consumable speed-flow rate relationship in the next flow rate adjustment period. In some embodiments, the processor 1300 further generates a first alarm message when the consumable rotation speed-flow rate relationship of the current flow rate adjustment cycle is out of a preset range.

The above process refers to "initial rotation speed", and in some embodiments, the initial rotation speed may be obtained by: after the infusion is started, the processor 1300 calculates the initial rotational speed according to the target flow rate and the initial default relationship between the rotational speed and the flow rate of the consumable.

In consideration of the influence of the shaking or position deviation, such as tilting, of the flow rate monitoring component 1200 on the real-time flow rate monitoring and the motor speed adjustment, in some embodiments, the processor 1300 obtains the target motor speed of the driving mechanism 1100 corresponding to the target flow rate of the liquid in the infusion tube 1001 at least according to the real-time flow rate and the displacement signal, and includes: when the displacement signal output by the displacement monitoring part 1500 meets a first preset condition, the processor 1300 calculates the target motor rotation speed of the driving mechanism 1100 according to the real-time flow rate; and/or, when the displacement signal output by the displacement monitoring part 1500 satisfies the second preset condition, the processor 1300 calculates the target motor rotation speed of the driving mechanism 1100 according to the real-time flow rate and the displacement signal. In some embodiments, the processor 1300 calculates the target motor speed of the driving mechanism 1100 according to the real-time flow rate and the displacement signal, and comprises: the processor 1300 compensates the real-time flow rate according to the displacement signal, and calculates the target motor rotation speed of the driving mechanism 1100 based on the compensated real-time flow rate; or, the processor 1300 calculates the intermediate motor speed of the driving mechanism 1100 according to the real-time flow rate, and then compensates the calculated intermediate motor speed according to the displacement signal to obtain the target motor speed.

In some embodiments, processor 1300 is further configured to: when the displacement signal output by the displacement monitoring part 1500 meets the third preset condition, the target motor rotation speed of the driving mechanism 1100 stops being obtained according to the real-time flow rate and the displacement signal, and/or second alarm information is generated.

In some embodiments, the first predetermined condition is that the displacement signal is less than a first threshold. In some embodiments, the second preset condition is that the displacement signal is greater than the second threshold and less than the third threshold. In some embodiments, the third predetermined condition is that the displacement signal is greater than a fourth threshold. In some embodiments, the first threshold is less than or equal to the second threshold. In some embodiments, the third threshold is less than or equal to the fourth threshold.

In some embodiments, the sleep wake-up unit 1700 is configured to detect a hanging state of an infusion bag 1002 of an infusion pump system, and the processor 1300 is further configured to: when the infusion pump system does not hang the infusion bag 1002, the flow rate and speed monitoring part 1200 enters the sleep mode, and when it is detected that the infusion pump system hangs the infusion bag 1002, the flow rate and speed monitoring part 1200 exits the sleep mode.

In some embodiments, battery unit 1800 is used to provide power.

In some embodiments, the processor 1300 obtains a real-time flow rate, which the display component 1400 displays.

In some embodiments, referring to fig. 10, a droplet count sensor 1600 may be used with drip chamber 1601 to detect the flow rate of droplets or the flow rate of droplets in drip chamber 1601.

In some embodiments, the pressure sensor 1610 can respond to the pressure value of the measured object, such as the infusion tube 1001, and convert the pressure value into an electrical signal for detection and send to the processor 1300. Pressure sensor 1610 may be a resistive strain gage pressure sensor, a semiconductor strain gage pressure sensor, a piezoresistive pressure sensor, an inductive pressure sensor, a capacitive pressure sensor, a resonant pressure sensor, a fiber optic pressure sensor, or a capacitive acceleration sensor. In some embodiments, the pressure sensor 1610 may be used to detect the internal pressure of the infusion tube 1001 or the external pressure of the infusion tube 1001. In some embodiments, the infusion tube 1001 may also be used to detect the in-situ status of a subject, such as the infusion tube 1001. In some embodiments, the pressure sensor 1610 may detect an occlusion inside the infusion set, or detect if the infusion line 1001 is leaking.

In some embodiments, the number of bubble sensors 1620 may be one or more, and may be used to detect, for example, whether or not bubbles are present in the infusion tube 1001, and may even detect the size of the bubbles. The bubble sensor 1620 may be an ultrasonic sensor or an infrared sensor, etc.

The RF circuitry 1630 is capable of receiving and transmitting electromagnetic waves. The RF circuit 1630 converts an electrical signal into an electromagnetic wave or converts an electromagnetic wave into an electrical signal and communicates with a communication network and other communication devices via the electromagnetic wave. The RF circuitry 1630 may include well-known circuitry for performing these functions, including but not limited to an antenna system, an RF transceiver, one or more amplifiers, a tuner, one or more oscillators, a digital signal processor, a CODEC chipset, a Subscriber Identity Module (SIM) card, memory, etc. The RF circuitry 1630 may communicate with networks and other devices via wireless communications, which may be the World Wide Web (WWW), an intranet, and/or a wireless network such as a cellular telephone network, a wireless Local Area Network (LAN), and/or a Metropolitan Area Network (MAN). Wireless communication may use any of a variety of communication standards, protocols, and technologies, including, but not limited to, global system for mobile communications (GSM), enhanced Data GSM Environment (EDGE), wideband Code Division Multiple Access (WCDMA), code Division Multiple Access (CDMA), time Division Multiple Access (TDMA), bluetooth (e.g., IEEE 802.15.1), wireless fidelity (WIFI) (e.g., IEEE802.11a, IEEE802.11 b, IEEE802.11g, and/or IEEE802.11 n), voice over internet protocol (VoIP), wi-MAX, protocols for email, instant messaging, and/or Short Message Service (SMS), or any other suitable communication protocol, including those not yet developed on the filing date herein.

In some embodiments, the processor 1300 can obtain the remaining amount of the infusion bag 1002, the inputted amount of the infusion solution, the infused time, the remaining infusion time, the real-time flow rate, the name of the drug solution, the infusion stage, the concentration of the drug solution, the flow rate or the flow rate of the drops detected by the drop number sensor 1600, the plasma concentration of the drug, and any one or more of the plasma target concentration, the drug effector chamber concentration, and the effector chamber target concentration, and display the same through the display unit 1400.

The processor may also be capable of determining and generating prompts or alarm messages in some embodiments, such as too fast an infusion rate, too slow an infusion rate, an impending infusion completion, an empty bottle, an occlusion, a bubble, and a system malfunction, which in some embodiments are displayed by the display component 1400.

In some embodiments, display assembly 1400 is touchless, and a user may complete the input of commands through peripherals that access the peripheral interface, including but not limited to a mouse, a keyboard, a gesture recognition device, and the like. In some embodiments, the display section 1400 may include a touch layer and a display layer that are arranged in a stack, the touch layer providing an input/output interface; the touch layer may include a resistive screen, a surface acoustic wave screen, an infrared touch screen, an optical touch screen, a capacitive screen, or a nano-film, and is an inductive display device capable of receiving input signals such as a contact. The visual output optionally includes graphics, text, charts, video, and combinations thereof. Some or all of the visual output may correspond to user interface objects. In some embodiments, display component 1400 can also receive user input based on tactile sensation and/or contact; the touch layer of the display 1400 forms a touch sensitive surface that receives user input; the touch layer and display controller detect contact (and any movement or interruption of the touch) on the touch layer and translate the detected contact into interaction with user interface objects, such as one or more soft keys, displayed on the touch layer. In one exemplary embodiment, the point of contact between the touch layer and the user corresponds to one or more fingers of the user. The touch layer may use LCD (liquid crystal display) technology or LPD (light emitting polymer display) technology, but in other embodiments other display technologies may be used. The touch layer and display controller may detect contact and movement or break thereof using any of a number of touch sensitive technologies, including but not limited to capacitive, resistive, infrared, and surface acoustic wave technologies, as well as other proximity sensor arrays, or other technologies for determining one or more points of contact with the touch layer.

In some embodiments, the display portion 1400 may further integrate a speaker or the like to play the content by voice, such as the above-mentioned prompt and alarm information.

In some embodiments, in designing the specific mechanical structure of the infusion pump system of the present application, a first housing 1 may be introduced, the first housing having a first fixed end and a second fixed end. In some embodiments, referring to fig. 11, the first fixing end, for example, facing upwards when in use, may be provided with a hook engaging portion 2 for engaging with a hook on a wall or a bag hanging bracket to be hung. The second fixed end faces downward when in use, for example, the flow rate and speed monitoring part 1200 may be disposed on the first housing 1, and in some embodiments, the flow rate and speed monitoring part 1200 includes a hook portion 1202 extending from the second fixed end of the first housing 1 for hanging the infusion bag 1002; for example, when the flow rate and speed monitoring component 1200 includes a tension sensor, the tension sensor can include a sensor main force portion and a hook portion 1202, and the tension applied by the hook portion can monitor the change of the corresponding force; therefore, the flow rate and speed monitoring member 1200 can monitor the change in the weight of the infusion bag 1002 by the weight of the infusion bag 1002 acting on the hook portion 1202 after the infusion bag 1002 is hung by the hook portion 1202.

In some embodiments, the display part 1400 may also be disposed in the first casing 1.

Referring to fig. 12 and 13, an infusion pump monitoring system in some embodiments of the present invention includes a flow rate monitoring component 1200, a displacement monitoring component 1500, and a processor 1300; in some embodiments, the infusion pump system may further include a display component 1400 and/or a fluid stop control component 1503. The flow rate monitoring component 1200 is configured to monitor a real-time flow rate of the liquid in the infusion tube, the displacement monitoring component 1500 is configured to detect a displacement of the flow rate monitoring component 1200 with respect to a predetermined direction, for example, a vertical direction, and output a corresponding displacement signal, and further descriptions of the flow rate monitoring component 1200 and the displacement monitoring component 1500 may refer to the above descriptions, and are not repeated herein. The processor 1300 is configured to output a real-time flow rate when the displacement signal output by the displacement monitoring component 1500 satisfies a first preset condition, for example, the real-time flow rate is displayed by the display component 1400.

In some embodiments, the processor 1300 is further configured to compensate the real-time flow rate according to the displacement signal when the displacement signal output by the displacement monitoring component 1500 satisfies a second preset condition, and output the compensated real-time flow rate.

In some embodiments, the processor 1300 is further configured to issue an alarm when the displacement signal output by the displacement monitoring part 1500 satisfies a third preset condition.

In some embodiments, the fluid stopping control component 1503 stops the fluid delivery tube when the displacement signal output by the displacement monitoring component 1500 satisfies a third preset condition.

In some embodiments, referring to fig. 14, the infusion pump monitoring system may further include one or more of a sleep wake-up unit 1700, a battery unit 1800, and RF circuitry 1630. The descriptions of the sleep wake-up unit 1700, the battery unit 1800, and the RF circuit 1630 are referred to above and will not be repeated herein.

The invention also provides an infusion method, which can be applied to an infusion pump system, wherein the infusion pump system is used for driving liquid in an infusion tube to controllably flow, and the infusion tube is communicated with an infusion bag for providing the liquid to be infused; the infusion pump system may be an infusion pump system as described in any of the embodiments herein.

Referring to fig. 15, the infusion method of some embodiments includes the following steps:

step S100: acquiring the real-time flow rate of liquid in the infusion tube through a flow rate monitoring part;

step S110: and acquiring a displacement signal representing the displacement of the flow rate and speed monitoring part relative to the preset direction through the displacement monitoring part.

Step S120: and obtaining a target motor rotating speed corresponding to the target flow rate of the liquid in the infusion tube at least according to the real-time flow rate and the displacement signal, and controlling the motor to work at the target motor rotating speed so as to drive the liquid in the infusion tube to controllably flow.

In some embodiments, after the infusion is initiated, step S120 controls operation at an initial rotational speed to drive a controlled flow of fluid in the infusion tube; step S120, acquiring a real-time flow rate corresponding to the initial rotating speed through a flow rate monitoring part; step S120, matching one or more pre-stored consumable rotating speed-flow speed relations according to the initial rotating speed and the consumable rotating speed-flow speed relation corresponding to the initial rotating speed; step S120, selecting the consumable rotating speed-flow rate relation which is successfully matched as the current consumable rotating speed-flow rate relation; step S120, according to the current consumable rotating speed-flow speed relation, a target motor rotating speed corresponding to the target flow speed of the liquid in the infusion tube is calculated. In some embodiments, when the consumable rotational speed-flow speed relationship between the initial rotational speed and the real-time flow speed corresponding to the initial rotational speed fails to match with one or more consumable rotational speed-flow speed relationships stored in advance, step S120 is further configured to generate a prompt message, where the prompt message is used to prompt a user to update the relationship library and/or perform troubleshooting. In some embodiments, step S120 further obtains a real-time motor rotation speed and a real-time flow rate corresponding to the real-time motor rotation speed, and generates a first alarm message when a consumable rotation speed-flow rate relationship between the real-time motor rotation speed and the real-time flow rate exceeds a preset range.

In some embodiments, after the infusion is initiated, step S120 controls operation at an initial rotational speed to drive a controlled flow of fluid in the infusion tube; step S120, calculating the target motor rotating speed by taking the flow rate regulation period as a time unit; specifically, the method comprises the following steps: step S120, acquiring the motor rotating speed of the current flow speed adjusting period, and acquiring the real-time flow speed of the current flow speed adjusting period through a flow speed monitoring part; step S120, calculating the consumable rotating speed-flow speed relation of the current flow speed regulation period according to the motor rotating speed of the current flow speed regulation period and the corresponding real-time flow speed; for the next flow rate adjustment period of the current flow rate adjustment period, step S120 calculates the consumable rotation speed-flow rate relationship of the next flow rate adjustment period according to the consumable rotation speed-flow rate relationship of at least one previous flow rate adjustment period of the next flow rate adjustment period; step S120, calculating the target motor rotating speed of the next flow rate adjusting period according to the target flow rate of the liquid in the infusion tube and the consumable rotating speed-flow rate relation of the next flow rate adjusting period. In some embodiments, step S120 further generates a first alarm message when the consumable rotation speed-flow rate relationship of the current flow rate adjustment cycle exceeds a preset range.

The above process refers to "initial rotation speed", and in some embodiments, the initial rotation speed may be obtained by: after the infusion is started, step S120 calculates an initial rotational speed according to the target flow rate and an initial default relationship between the rotational speed and the flow rate of the consumable.

In consideration of the influence of the shaking or position deviation, such as inclination, of the flow rate monitoring component on the real-time flow rate monitoring and the motor speed adjustment, in some embodiments, the step S120 obtains a target motor speed corresponding to the target flow rate of the liquid in the infusion tube according to at least the real-time flow rate and the displacement signal, and controls the operation at the target motor speed to drive the liquid in the infusion tube to controllably flow, including: when the displacement signal output by the displacement monitoring component meets a first preset condition, step S120 calculates a target motor rotation speed according to the real-time flow rate; and/or when the displacement signal output by the displacement monitoring component meets a second preset condition, step S120 calculates the target motor rotation speed according to the real-time flow rate and the displacement signal. In some embodiments, the step S120 of calculating the target motor speed according to the real-time flow rate and the displacement signal includes: step S120, compensating the real-time flow rate according to the displacement signal, and calculating the rotating speed of the target motor based on the compensated real-time flow rate; or, step S120 calculates an intermediate motor rotation speed according to the real-time flow rate, and then compensates the calculated intermediate motor rotation speed according to the displacement signal to obtain the target motor rotation speed.

In some embodiments, when the displacement signal output by the displacement monitoring component 1500 meets the third preset condition, step S120 further stops obtaining the target motor rotation speed according to the real-time flow rate and the displacement signal, and/or generates the second alarm information.

In some embodiments, the first predetermined condition is that the displacement signal is less than a first threshold. In some embodiments, the second preset condition is that the displacement signal is greater than the second threshold and less than a third threshold. In some embodiments, the third predetermined condition is that the displacement signal is greater than a fourth threshold. In some embodiments, the first threshold is less than or equal to the second threshold. In some embodiments, the third threshold is less than or equal to the fourth threshold.

In some embodiments, the infusion fluid method further comprises the steps of: when the infusion pump system does not hang an infusion bag, the flow rate and speed control monitoring part is controlled to enter a sleep mode, and when the infusion pump system is detected to hang an infusion bag, the flow rate and speed control monitoring part exits the sleep mode.

Some embodiments of the invention also provide an infusion monitoring method, which can be applied to an infusion pump system, wherein the infusion pump system is used for driving liquid in an infusion tube to controllably flow, and the infusion tube is communicated with an infusion bag for providing the liquid to be infused; the infusion pump system may be an infusion pump system as described in any of the embodiments herein.

Referring to fig. 16, the infusion monitoring method of some embodiments includes the following steps:

step S200: acquiring the real-time flow rate of liquid in the infusion tube through a flow rate monitoring part;

step S210: and acquiring a displacement signal representing the displacement of the flow rate and speed monitoring part relative to the preset direction through the displacement monitoring part.

Step S230: and outputting the real-time flow rate when the displacement signal meets a first preset condition.

In some embodiments, the step S230 is further configured to compensate the real-time flow rate according to the displacement signal when the displacement signal output by the displacement monitoring component satisfies a second preset condition, and output the compensated real-time flow rate.

In some embodiments, step S230 is further configured to issue an alarm when the displacement signal output by the displacement monitoring component satisfies a third preset condition.

In some embodiments, when the displacement signal output by the displacement monitoring part 1500 satisfies the third preset condition, the step S230 stops the liquid in the infusion tube through the liquid stop control part.

Reference is made herein to various exemplary embodiments. However, those skilled in the art will recognize that changes and modifications may be made to the exemplary embodiments without departing from the scope hereof. For example, the various operational steps, as well as the components used to perform the operational steps, may be implemented in differing ways depending upon the particular application or consideration of any number of cost functions associated with operation of the system (e.g., one or more steps may be deleted, modified or incorporated into other steps).

In the above embodiments, the implementation may be wholly or partially realized by software, hardware, firmware, or any combination thereof. Additionally, as will be appreciated by one skilled in the art, the principles herein may be reflected in a computer program product on a computer readable storage medium, which is pre-loaded with computer readable program code. Any tangible, non-transitory computer-readable storage medium may be used, including magnetic storage devices (hard disks, floppy disks, etc.), optical storage devices (CD-to-ROM, DVD, blu-Ray discs, etc.), flash memory, and/or the like. These computer program instructions may be loaded onto a general purpose computer, special purpose computer, or other programmable data processing apparatus to produce a machine, such that the instructions which execute on the computer or other programmable data processing apparatus create means for implementing the functions specified. These computer program instructions may also be stored in a computer-readable memory that can direct a computer or other programmable data processing apparatus to function in a particular manner, such that the instructions stored in the computer-readable memory produce an article of manufacture including means for implementing the function specified. The computer program instructions may also be loaded onto a computer or other programmable data processing apparatus to cause a series of operational steps to be performed on the computer or other programmable apparatus to produce a computer implemented process such that the instructions which execute on the computer or other programmable apparatus provide steps for implementing the functions specified.

While the principles herein have been illustrated in various embodiments, many modifications of structure, arrangement, proportions, elements, materials, and components and otherwise, used in the practice of the disclosure, which are particularly adapted to specific environments and operative requirements, may be employed without departing from the principles and scope of the present disclosure. The above modifications and other changes or modifications are intended to be included within the scope of this document.

The foregoing detailed description has been described with reference to various embodiments. However, one skilled in the art will recognize that various modifications and changes may be made without departing from the scope of the present disclosure. Accordingly, the disclosure is to be considered in all respects as illustrative and not restrictive, and all such modifications are intended to be included within the scope thereof. Also, advantages, other advantages, and solutions to problems have been described above with regard to various embodiments. However, the benefits, advantages, solutions to problems, and any element(s) that may cause any element(s) to occur or become more pronounced are not to be construed as a critical, required, or essential feature or element of any or all the claims. As used herein, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, system, article, or apparatus. Furthermore, the term "coupled," and any other variation thereof, as used herein, refers to a physical connection, an electrical connection, a magnetic connection, an optical connection, a communicative connection, a functional connection, and/or any other connection.

Those skilled in the art will recognize that many changes may be made to the details of the above-described embodiments without departing from the underlying principles of the invention. Accordingly, the scope of the invention should be determined only by the claims.

Claims

1. An infusion pump system, comprising:

2. The infusion pump system of claim 1, wherein said processor obtains a target motor speed of said drive mechanism corresponding to a target flow rate of fluid in said infusion tube based on at least said real-time flow rate and said displacement signal, comprising:

selecting the successfully matched consumable material rotating speed-flow speed relation as the current consumable material rotating speed-flow speed relation; and

3. The infusion pump system of claim 2, wherein the processor further obtains a real-time motor speed and a corresponding real-time flow rate, and generates a first warning message when a consumable speed-flow rate relationship between the real-time motor speed and the corresponding real-time flow rate is outside a predetermined range.

4. The infusion pump system of claim 1, wherein said processor deriving a target motor speed of said drive mechanism corresponding to a target flow rate of fluid in said infusion tube based on said real-time flow rate and said displacement signal comprises:

calculating a target motor rotation speed of the driving mechanism by taking a flow rate regulation period as a time unit;

5. The infusion pump system of claim 4, wherein the processor further generates a first alert message when the consumable rotational speed-flow rate relationship for the current flow rate adjustment cycle is outside a preset range.

6. The infusion pump system of claim 2 or 4, wherein the processor calculates the initial rotational speed based on the target flow rate and an initial default consumable rotational speed-flow rate relationship after initiation of infusion.

7. The infusion pump system according to any of claims 1-6, wherein said processor obtains a target motor speed of said drive mechanism corresponding to a target flow rate of liquid in said infusion tube based at least on said real-time flow rate and said displacement signal, comprising:

When the displacement signal output by the displacement monitoring part meets a second preset condition, calculating the target motor rotating speed of the driving mechanism according to the real-time flow speed and the displacement signal;

the processor is further configured to: and when the displacement signal output by the displacement monitoring part meets a third preset condition, stopping obtaining the target motor rotating speed of the driving mechanism according to the real-time flow speed and the displacement signal, and/or generating second alarm information.

8. The infusion pump system of claim 7, wherein said processor calculates a target motor speed for said drive mechanism based on said real-time flow rate and said displacement signal, comprising:

or,

9. The infusion pump system of claim 7, wherein the first preset condition is the displacement signal being less than a first threshold; the second preset condition is that the displacement signal is larger than a second threshold and smaller than a third threshold; the third preset condition is that the displacement signal is greater than a fourth threshold value; the first threshold is less than or equal to a second threshold, and the third threshold is less than or equal to a fourth threshold.

10. The infusion pump system of claim 1, wherein the displacement monitoring component comprises an angle sensor and/or a motion sensor; the displacement signal comprises an angle signal and/or a motion signal, wherein the angle sensor is used for detecting the angle signal of the flow rate monitoring component relative to a preset direction, and the motion sensor is used for detecting the motion signal of the flow rate monitoring component relative to the preset direction.

11. The infusion pump system of claim 1, wherein:

the flow rate and speed monitoring part comprises a weight change monitoring part which is used for being connected with the infusion bag and monitoring the weight change of the infusion bag; the flow rate and speed monitoring part calculates real-time flow rate and speed according to the weight change of the infusion bag; or,

the flow rate and speed monitoring part comprises a pipe diameter measuring part, and the pipe diameter measuring part is used for measuring the pipe diameter of the infusion pipe; the flow rate monitoring part calculates the real-time flow rate by measuring the pipe diameter of the infusion pipe.

12. The infusion pump system of claim 11, wherein the tube diameter measurement component comprises a hall sensor, or a membrane pressure sensor.

13. The infusion pump system of claim 1, further comprising a sleep wake-up unit; the dormancy awakening unit is used for detecting the suspension state of an infusion bag of the infusion pump system, and the processor is further used for: and when the infusion pump system is detected to suspend the infusion bag, the flow speed monitoring part is controlled to exit from the sleep mode.

14. The infusion pump system of claim 1, further comprising RF circuitry that converts electrical signals to or from electromagnetic waves and communicates with communication networks and other communication devices via electromagnetic waves.

15. The infusion pump system of claim 1, further comprising a battery unit for powering.

16. An infusion pump monitoring system, comprising:

and the processor is used for outputting the real-time flow rate when the displacement signal output by the displacement monitoring part meets a first preset condition.

17. The infusion pump monitoring system of claim 16, wherein the first predetermined condition is the displacement signal being less than a first threshold.

18. The infusion pump monitoring system according to claim 16, wherein the processor is further configured to compensate the real-time flow rate according to the displacement signal when the displacement signal output by the displacement monitoring component satisfies a second preset condition, and output the compensated real-time flow rate.

19. The infusion pump monitoring system according to claim 18, wherein said second predetermined condition is said displacement signal being greater than a second threshold and less than a third threshold.

20. The infusion pump monitoring system of claim 16, wherein the processor is further configured to issue an alarm when the displacement signal output by the displacement monitoring component satisfies a third predetermined condition.

21. The infusion pump monitoring system of claim 20, further comprising a fluid stop control component; and when the displacement signal output by the displacement monitoring part meets a third preset condition, the liquid stopping control part stops the liquid of the infusion tube.

22. The infusion pump monitoring system of claim 20, wherein the third predetermined condition is the displacement signal being greater than a fourth threshold.

23. The infusion pump monitoring system of claim 16, wherein the displacement monitoring component comprises an angle sensor and/or a motion sensor; the displacement signal comprises an angle signal and/or a movement signal, wherein the angle sensor is used for detecting the angle signal of the flow rate monitoring component relative to a preset direction, and the movement sensor is used for detecting the movement signal of the flow rate monitoring component relative to the preset direction.

24. The infusion pump monitoring system of claim 16, wherein:

the flow rate and speed monitoring part comprises a pipe diameter measuring part, and the pipe diameter measuring part is used for measuring the pipe diameter of the infusion pipe; the flow speed monitoring part calculates the real-time flow speed by measuring the pipe diameter of the infusion pipe.

25. The infusion pump monitoring system of claim 24, wherein the tube diameter measuring component comprises a hall sensor, or a membrane pressure sensor.

26. The infusion pump monitoring system of claim 16, further comprising a sleep wake-up unit; the dormancy awakening unit is used for detecting the suspension state of the infusion bag of the infusion pump, and the processor is further used for: and when the infusion pump is detected to hang the infusion bag, the flow speed monitoring part is controlled to exit from the sleep mode.

27. The infusion pump monitoring system of claim 16, further comprising an RF circuit that converts electrical signals to or from electromagnetic waves and communicates with a communication network and other communication devices via electromagnetic waves.

28. The infusion pump monitoring system of claim 16, further comprising a battery unit for powering.

29. An infusion method is applied to an infusion pump system, the infusion pump system is used for driving liquid in an infusion tube to controllably flow, and the infusion tube is communicated with an infusion bag for providing the liquid to be infused; the infusion method is characterized by comprising the following steps:

and obtaining a target motor rotating speed corresponding to the target flow rate of the liquid in the infusion tube at least according to the real-time flow rate and the displacement signal, and controlling the motor to work at the target motor rotating speed so as to drive the liquid in the infusion tube to controllably flow.

30. An infusion liquid monitoring method is applied to an infusion pump system, wherein the infusion pump system is used for driving liquid in an infusion tube to controllably flow; the infusion liquid monitoring method is characterized by comprising the following steps:

acquiring the real-time flow rate of the liquid in the infusion tube through a flow rate and speed monitoring component;