Intermittent detection method and device for body fluid parameters and related system

Abstract

The invention provides an intermittent detection method and device for body fluid parameters and a related system.The method is applied to a body fluid parameter detection system, the system comprises an infusion tube, a detection module, an extraction and injection device, a liquid path switch and a flushing device.The method comprises the steps that the liquid path switch is controlled to execute a closing action, and the liquid path switch is controlled to close the infusion tube; controlling the extraction and injection device to extract a preset first volume of target body fluid from a preformed hole of a target user into the infusion tube, controlling the detection module to detect parameters of the target body fluid when the target body fluid in the infusion tube is detected to pass through the detection module, obtaining the parameters of the target body fluid, controlling the liquid path switch to execute an opening action, and controlling the liquid path switch to execute a closing action; and controlling the flushing device to inject a preset second volume of functional liquid into the infusion tube, and controlling the extraction and injection device to enable the target body fluid to flow back to the target user when the functional liquid in the infusion tube is detected to pass through the detection module. When blood gas parameter detection is carried out, blood waste and detection cost are reduced.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and in particular to a method, device and related system for intermittent detection of body fluid parameters. Background Technology

[0002] Blood gas parameter monitoring is extremely important in patient treatment, especially for critically ill patients. By monitoring blood parameters such as pH, pCO2, pO2, and serum ion concentration, medical staff can provide targeted treatment to diagnose and manage the patient. Current medical technology primarily uses manual single-point blood sampling and the use of extracorporeal membrane oxygenation (EMOC) systems for continuous blood gas monitoring.

[0003] However, manual single-point blood collection and testing involves large blood volumes and long testing cycles. After the blood is collected, it is discarded, resulting in a great waste for patients, especially those with weak blood and qi. The EMOC method has limited blood gas parameters and poor accuracy. In addition, it requires the establishment of an external circulation circuit with the human body, which has high operational risks and costs.

[0004] Therefore, how to reduce blood waste and testing costs when performing blood gas parameter testing is an urgent issue to be addressed. Summary of the Invention

[0005] This application provides a method, apparatus, and related system for intermittent detection of body fluid parameters, which reduces blood waste and lowers detection costs when performing blood gas parameter detection.

[0006] In a first aspect, embodiments of this application provide a method for intermittent detection of body fluid parameters, applied to the main controller of a body fluid parameter detection system. The body fluid parameter detection system includes: an infusion tubing, a pipetting module connected to the infusion tubing, and a detection module disposed on the infusion tubing. The pipetting module includes an injection device, a fluid circuit switch, and a flushing device connected to the injection device. The injection device is connected to the fluid circuit switch and to the infusion tubing. The method includes: Control the liquid circuit switch to perform a closing action, and control the extraction and injection device to extract a preset first volume of target body fluid from the target user's reserved hole into the infusion tube; When the target body fluid in the infusion tube is detected to pass through the detection module, the detection module is controlled to detect the parameters of the target body fluid to obtain the target body fluid parameters; Control the liquid circuit switch to perform the opening action, and control the flushing device to inject a preset second volume of functional liquid into the infusion tube; When the detection module detects that the functional fluid in the infusion tube has passed through the detection module, the extraction and injection device is controlled to return the target body fluid to the target user.

[0007] Secondly, embodiments of this application provide an intermittent detection device for body fluid parameters, applied to a body fluid parameter detection system. The body fluid parameter detection system includes: an infusion tubing, a pipetting module connected to the infusion tubing, and a detection module disposed on the infusion tubing. The pipetting module includes an injection device, a fluid circuit switch, and a flushing device connected to the injection device. The injection device is connected to the fluid circuit switch and to the infusion tubing. The device includes: The control unit is used to control the liquid circuit switch to perform a closing action, and to control the extraction and injection device to extract a preset first volume of target body fluid from the target user's reserved hole into the infusion tube; A monitoring unit is used to control the detection module to detect the parameters of the target body fluid when the target body fluid in the infusion tube passes through the detection module, and obtain the target body fluid parameters; The control unit is also used to control the liquid circuit switch to perform an opening action, and to control the flushing device to inject a preset second volume of functional liquid into the infusion tube; An execution unit is configured to control the extraction and injection device to return the target body fluid to the target user when the detection module is detected that the functional fluid in the infusion tube has passed through the detection module.

[0008] Thirdly, embodiments of this application provide an intermittent detection device for body fluid parameters, including a processor, a memory, a communication interface, and one or more programs, wherein the one or more programs are stored in the memory and configured to be executed by the processor, and the programs include instructions for performing steps in any method of the first aspect of this application.

[0009] Fourthly, embodiments of this application provide an intermittent detection system for body fluid parameters, wherein the intermittent detection system for body fluid parameters performs some or all of the steps described in any method of the first aspect of embodiments of this application.

[0010] Fifthly, embodiments of this application provide a computer program product, wherein the computer program product includes a non-transitory computer-readable storage medium storing a computer program operable to cause a computer to perform some or all of the steps described in any method of the first aspect of this application. The computer program product may be a software installation package.

[0011] By implementing the embodiments of this application, the following beneficial effects are achieved: This application provides a method, apparatus, and related system for intermittent detection of body fluid parameters. The method is applied to the main controller of a body fluid parameter detection system, which includes: an infusion tube, a pipetting module connected to the infusion tube, and a detection module mounted on the infusion tube. The pipetting module includes an extraction and injection device, a fluid circuit switch, and a flushing device connected to the extraction and injection device. The extraction and injection device is connected to the fluid circuit switch and the infusion tube. The method includes: controlling the fluid circuit switch to perform a closing action; controlling the extraction and injection device to extract a preset first volume of target body fluid from a pre-reserved hole of a target user into the infusion tube; when the target body fluid in the infusion tube is detected to have passed through the detection module, controlling the detection module to detect the parameters of the target body fluid to obtain the target body fluid parameters; controlling the fluid circuit switch to perform an opening action; and controlling the flushing device to inject a preset second volume of functional liquid into the infusion tube; when the functional liquid in the infusion tube is detected to have passed through the detection module, controlling the extraction and injection device to return the target body fluid to the target user. Thus, on the one hand, by using electrochemical or optical sensors installed in the infusion line, detection can be performed when the body fluid is drawn and passes through the sensor's sensing position. After the measurement is completed, the body fluid is injected back into the human or animal body, thereby reducing blood waste. On the other hand, by connecting the tubing to the patient's pre-drilled hole for detection, there is no need to connect an additional extracorporeal circulation device, thereby reducing the cost of detection. Attached Figure Description

[0012] To more clearly illustrate the technical solutions of the embodiments of this application, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0013] Figure 1 This is an architecture diagram of an intermittent detection system for body fluid parameters provided in an embodiment of this application; Figure 2 This is a schematic diagram of the structure of an intermittent detection device for body fluid parameters provided in an embodiment of this application; Figure 3This is a schematic flowchart of an intermittent detection method for body fluid parameters provided in an embodiment of this application; Figure 4 This is a schematic diagram of the connection circuit between an infusion tube and an indwelling needle provided in an embodiment of this application; Figure 5 This is a schematic diagram of the structure of a transmissive optical sensor provided in an embodiment of this application; Figure 6 This is a schematic diagram of a scenario where blood is drawn from an indwelling needle, as provided in an embodiment of this application. Figure 7 This is a schematic diagram illustrating a scenario where blood is injected back into a patient, as provided in an embodiment of this application. Figure 8 This is a block diagram of the functional modules of an intermittent detection device for body fluid parameters provided in an embodiment of this application. Detailed Implementation

[0014] To enable those skilled in the art to better understand the present application, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present application, and not all embodiments. Based on the embodiments of the present application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present application.

[0015] The terms "first," "second," etc., in the specification, claims, and accompanying drawings of this application are used to distinguish different objects, not to describe a specific order. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover non-exclusive inclusion. For example, a process, method, system, product, or apparatus that includes a series of steps or units is not limited to the listed steps or units, but may optionally include steps or units not listed, or may optionally include other steps or units inherent to these processes, methods, products, or apparatuses.

[0016] It should be understood that the term "and / or" in this document is merely a description of the relationship between related objects, indicating that three relationships can exist. For example, A and / or B can represent: A existing alone, A and B existing simultaneously, or B existing alone. Additionally, the character " / " in this document indicates that the preceding and following related objects are in an "or" relationship. In the embodiments of this application, "multiple" refers to two or more.

[0017] In the embodiments of this application, "at least one item" or its similar expression refers to any combination of these items, including any combination of a single item or a plurality of items. "One or more" means one or more, while "multiple" means two or more. For example, "at least one item" of a, b, or c can represent the following seven cases: a, b, c; a and b; a and c; b and c; a, b, and c. Each of a, b, and c can be an element or a set containing one or more elements.

[0018] In this application, the term "connection" refers to various connection methods, such as direct connection or indirect connection, to achieve communication between devices. This application does not impose any limitations on this.

[0019] In this document, the term "embodiment" means that a particular feature, structure, or characteristic described in connection with an embodiment may be included in at least one embodiment of this application. The appearance of this phrase in various places throughout the specification does not necessarily refer to the same embodiment, nor is it a separate or alternative embodiment mutually exclusive with other embodiments. It will be explicitly and implicitly understood by those skilled in the art that the embodiments described herein can be combined with other embodiments.

[0020] Currently, blood gas parameters are typically measured using manual single-sampling and EMOC methods. However, manual single-point blood sampling and testing involve large blood volumes, long testing cycles, and the blood is discarded after collection, resulting in significant waste for patients, especially those with weak blood and qi. EMOC methods, on the other hand, have limited blood gas parameters and poor accuracy. Furthermore, it requires the establishment of an external circulation system, which carries higher operational risks and costs.

[0021] To address the aforementioned issues, embodiments of this application provide a method, apparatus, and related system for intermittent detection of body fluid parameters, which reduces blood waste and lowers detection costs during blood gas parameter testing.

[0022] The following is combined with Figure 1 The system architecture of an intermittent detection method for body fluid parameters in an embodiment of this application is described. Figure 1This is an architectural diagram of an intermittent monitoring system for body fluid parameters provided in an embodiment of this application. The intermittent monitoring system 100 for body fluid parameters includes: a blood gas parameter sensor 101, an indwelling needle 102, a reservoir 103, a monitor 104, an infusion bag 105, a flushing device 106, a sensor and reservoir fixing bracket 107, and a control valve 108. This intermittent monitoring system 100 for body fluid parameters can automatically extract, detect, and return key physiological parameters such as partial pressure and electrolyte concentration in a patient's body fluids (such as blood and tissue fluid) without the need for complex extracorporeal circulation tubing. After the detection is completed, the body fluid can be reinjected into the body, thereby achieving a closed-loop, low-invasive intermittent monitoring process.

[0023] Among them, the blood gas parameter sensor 101 is used to detect parameters of the target body fluid extracted from the patient, and can detect parameters including partial pressure of oxygen (pO2), partial pressure of carbon dioxide (pCO2), pH value, and electrolyte concentration (such as Na+). + K + Ca 2+ The sensor can detect various physiological indicators, such as blood gas parameters (e.g., optical absorption and electrochemical response signals). It can employ an electrochemical sensing element or an optical sensing module, positioned at the detection location along the infusion tube path. When body fluid flows through the detection area, the blood gas parameter sensor 101 collects characteristic information such as optical absorption signals and electrochemical response signals of the body fluid, and transmits these signals to the monitor 104 for data analysis and processing. In one possible embodiment, the blood gas parameter sensor 101 includes both a photoelectric sensor and an electrochemical sensor. The photoelectric sensor detects the optical absorption characteristics of the body fluid to identify the oxygenation status of hemoglobin; the electrochemical sensor uses a microelectrode array to detect ion concentration and potential changes in the body fluid, thereby obtaining parameters related to blood acid-base balance. The sensor module can be fixed to a transparent tube segment to ensure stable light path and minimal signal interference as the body fluid flows through the detection area, improving detection accuracy and repeatability.

[0024] The indwelling needle 102 serves as the interface between the system and the patient's blood circulation, enabling multiple fluid extraction and return operations without frequent punctures. One end of the needle is inserted into the patient's artery or vein, while the other end connects to the infusion tubing via a Luer connector, forming a controllable fluid pathway. Controlled by a fluid circuit switch connected to the infusion tubing, a preset volume of blood sample can be extracted to the testing area at the start of the test. After the test, the fluid is smoothly returned to the patient's body via a flushing device and the reverse drive of the reservoir, achieving zero-waste testing. The reservoir 103 is a key module for fluid storage and return control. It employs a double-layer structure with a rigid outer shell and a flexible inner liner, achieving precise volume control of the fluid through piston-driven or diaphragm-driven mechanisms. During extraction, a negative pressure is created inside the reservoir, causing the fluid to flow into the infusion tubing via the indwelling needle; during return, a positive pressure is created inside the reservoir, pushing the fluid back into the body. A pressure sensor interface is installed on the reservoir to monitor pressure changes within the tank. In one possible embodiment, the storage tank may share a drive unit with the flushing device 106, and the monitor 104 may implement bidirectional control via a motor or solenoid valve to achieve dynamic switching between extraction and injection.

[0025] The monitor 104 receives optical and electrochemical signals from the blood gas parameter sensor 101, performs signal amplification, filtering, conversion, and data analysis, and outputs the body fluid parameter detection results. The monitor 104 internally includes a signal acquisition module, a data analysis module, and a display module. The signal acquisition module converts analog signals into digital signals using an A / D converter; the data analysis module calculates blood gas parameters, electrolyte concentrations, and pH values ​​based on a preset mapping relationship between optical and electrochemical parameters; the display module displays the detection results in graphical or numerical form and can output them to an external monitoring terminal or hospital information system. In one possible embodiment, the monitor 104 also includes a wireless communication module for real-time transmission of detection data to a cloud server, enabling remote monitoring and synchronized display on medical personnel's terminals.

[0026] The infusion bag 105 serves as a storage unit for functional fluids, providing flushing or diluent to the system and ensuring the cleanliness of the detection module and infusion tubing. The infusion bag can store physiological saline or deionized water, with anticoagulants (such as heparin or sodium citrate) added in proportion to prevent blood clotting. The infusion bag is connected to the flushing device 106 via a fluid circuit switch. During system reflux or cleaning operations, fluid flows from the infusion bag into the fluid circuit to flush the detection tubing and replace residual body fluids. The flushing device 106 includes a flushing valve and a pressure sensor. After detection, the flushing device 106 injects functional fluid into the infusion tubing, flushing the detection module and pushing the body fluids back into the patient's body. This device can be an injection pump or a miniature peristaltic pump, with its flow rate and volume controlled by a monitor to achieve a precise flushing process. A check valve may be installed inside the flushing device to ensure unidirectional fluid flow and prevent cross-contamination. The sensor and reservoir mounting bracket 107 is used to achieve structural integration and stable installation of the blood gas parameter sensor 101 and the reservoir 103. The bracket is equipped with slots, clamps, and limiting structures to secure the sensor assembly, infusion tubing, and reservoir, preventing loosening of the fluid lines or signal deviation due to external vibrations or user movement. Furthermore, when pressure detection within the tubing is required, the control valve 108 is closed and the pressure sensor detects the pressure within the tubing; when blood pressure detection is required, the control valve 108 is opened to allow real-time detection of the user's blood gas parameters through the intermittent fluid parameter detection system 100.

[0027] visible, Figure 1 The intermittent body fluid parameter detection system 100 shown forms a controllable, closed-loop body fluid detection circuit through the coordinated operation of a blood gas parameter sensor 101, an indwelling needle 102, a fluid reservoir 103, a monitor 104, an infusion bag 105, a flushing device 106, and a sensor and fluid reservoir fixing bracket 107. It can automatically complete the entire process from body fluid extraction, detection, and recirculation, avoiding blood waste caused by traditional manual blood collection methods and eliminating the high risks and costs associated with establishing extracorporeal circulation devices. Furthermore, by intelligently controlling the fluid circuit and sensor action sequence during the detection process, real-time, intermittent monitoring of body fluid parameters is achieved, providing a safe, efficient, and reliable detection solution for clinical scenarios requiring dynamic blood gas assessment.

[0028] The following is combined with Figure 2 The intermittent detection device for body fluid parameters in the embodiments of this application will be described. Figure 2 A schematic diagram of the structure of an intermittent detection device for body fluid parameters provided in this application embodiment is shown below. Figure 2As shown, the intermittent detection device 200 for body fluid parameters includes one or more processors 210, a memory 220, a communication interface 230, and one or more programs 221. The processor 210 is communicatively connected to the memory 220 and the communication interface 230 via an internal communication bus.

[0029] The processor 210 can be a central processing unit (CPU), a general-purpose processor, a digital signal processor (DSP), an application-specific integrated circuit (ASIC), a field-programmable gate array (FPGA), or other programmable logic devices, transistor logic devices, hardware components, or any combination thereof. It can implement or execute the various exemplary logic blocks, units, and circuits described in conjunction with the disclosure of this application. The processor can also be a combination that implements computational functions, such as a combination of one or more microprocessors, a combination of a DSP and a microprocessor, etc. The communication unit can be a communication interface, transceiver, transceiver circuit, etc., and the storage unit can be a memory.

[0030] The memory 220 can be volatile memory or non-volatile memory, or it can include both. The non-volatile memory can be read-only memory (ROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), or flash memory. The volatile memory can be random access memory (RAM), which is used as an external cache. By way of example, but not limitation, many forms of random access memory (RAM) are available, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate synchronous DRAM (DDR SDRAM), enhanced synchronous DRAM (ESDRAM), synchronous linked DRAM (SLDRAM), and direct rambus RAM (DR RAM).

[0031] The one or more programs 221 are stored in the memory 220 and configured to be executed by the processor 210. The one or more programs include instructions for performing any step in the above method embodiments.

[0032] It is understood that the intermittent detection device 200 for body fluid parameters may include more or fewer structural components than those shown in the block diagram above, such as a power module, physical buttons, a Wi-Fi module, a speaker, a Bluetooth module, a sensor, and a display module, etc., without limitation. It is understood that this intermittent detection device for body fluid parameters may be equipped with, for example... Figure 1 The architecture of an intermittent detection system for body fluid parameters.

[0033] After understanding the software and hardware architecture of this application, the following will be combined with... Figure 3 This application describes an intermittent detection method for body fluid parameters. Figure 3This is a flowchart illustrating an intermittent detection method for body fluid parameters provided in an embodiment of this application. The method is applied to the main controller of a body fluid parameter detection system. The system includes: an infusion tubing, a pipetting module connected to the infusion tubing, and a detection module mounted on the infusion tubing. The pipetting module includes an injection device, a fluid circuit switch, and a flushing device connected to the injection device. The injection device is connected to the fluid circuit switch and the infusion tubing. The method specifically includes the following steps: Step S310: Control the liquid circuit switch to perform a closing action, and control the extraction and injection device to extract a preset first volume of target body fluid from the target user's reserved hole into the infusion tube.

[0034] The liquid circuit switch's closing action cuts off the fluid channel from the infusion bag before fluid extraction, creating a closed extraction circuit independent of the target user's fluid pathway. During intermittent blood gas parameter monitoring, an extraction start command is first generated based on the monitoring cycle signal, and a control signal is sent to the liquid circuit switch module via the control bus, causing the liquid circuit switch to close. In the closed state, the infusion tubing, reservoir, extraction injection device, and detection module together form a closed liquid circuit, providing a pressure isolation environment for unidirectional fluid extraction. The extraction process of the extraction injection device is executed collaboratively by a control drive device and a pressure sensor to ensure the accuracy of the extraction volume and the smoothness of the fluid flow. The extraction injection device includes a reservoir, a drive device, and a pressure sensor. The drive device can be a motor-driven push rod structure or a linear motor module, used to move axially under the action of a control signal to achieve the reciprocating motion of the piston inside the reservoir. When the controller issues an extraction command, the drive device moves the piston backward, creating a negative pressure zone inside the reservoir, causing the fluid to enter the infusion tubing through the pre-drilled hole and Luer connector. At this point, a pressure sensor located near the storage tank end of the infusion tubing monitors pressure changes within the fluid path in real time and feeds the pressure signal back to the main controller for blood pressure or tubing pressure detection. The controller then determines whether the body fluid has reached the sensing position of the detection module based on changes detected by the photoelectric sensor in the detection module. When a change in the light signal is detected, it indicates that the body fluid has filled the front section of the infusion tubing and flowed through the detection module, thus completing an effective extraction process. During the extraction process, to prevent detection fluctuations caused by air contamination or fluid turbulence, a pressure buffering and flow-limiting control mechanism is employed. Specifically, a micro-damping structure is installed at the inlet of the storage tank. This structure delays the flow rate response during instantaneous pressure changes to balance the liquid flow rate. Simultaneously, the controller adaptively adjusts the moving speed of the drive device according to the pressure change curve, keeping the body fluid flow rate within a preset range (e.g., 0.2–0.5 mL / s). This dual control mechanism ensures stable propagation of the body fluid within the infusion tubing, preventing the generation of bubbles and eddies.

[0035] To better understand the process of drawing bodily fluids from the pre-drilled hole into the infusion tubing, please refer to [link to relevant documentation]. Figure 4 , Figure 4 This is a schematic diagram of an infusion tubing and indwelling needle connection circuit. As shown, the infusion tubing and indwelling needle connection circuit 400 includes: an infusion tubing connector, a fluid circuit switch, a reservoir, a sensor bracket, and an indwelling needle connector. The infusion tubing connector is used to quickly connect and disconnect the body fluid parameter monitoring system from the patient's indwelling tubing. Its shape adopts a standard Luer cone structure, and a sealed connection can be achieved through rotational locking. When the system performs body fluid aspiration, the infusion tubing connector and the indwelling needle connector cooperate to form a closed fluid circuit, preventing air ingress or body fluid leakage. To prevent loosening, the connector's outer wall is designed with anti-slip threads and can be used with a medical silicone sealing ring to achieve a double seal, ensuring stable fluid conductivity even under repeated use or pressure changes.

[0036] Specifically, the fluid circuit switch is located between the infusion tubing connector and the storage tank, and its function is to control the flow direction and on / off state of the fluid in the circuit. The fluid circuit switch can be a mechanical knob or an electrically controlled solenoid valve; no limitation is made here. During extraction or reflux operations, the main controller issues commands to switch the fluid circuit state. When the fluid circuit switch is closed, the tubing forms a closed path for extracting bodily fluids from the target user's indwelling needle. When the fluid circuit switch is open, the functional fluid in the storage tank can be injected into the detection module and indwelling needle through the infusion tubing, achieving flushing and reflux. The sealing components of the fluid circuit switch are made of medical-grade PTFE material, which has corrosion resistance and low friction properties to reduce resistance during switching and prevent fluid retention. The storage tank is used to temporarily store the extracted bodily fluids or functional fluids. It can be equipped with a piston or diaphragm structure to work with the extraction and injection device to achieve precise volume control. The reservoir, fluid circuit switch, and infusion tubing form an integrated module. During the extraction phase, negative pressure draws bodily fluid into the system, and during the return phase, positive pressure pushes the fluid back into the patient's body. To ensure the biosafety of the fluid, the reservoir is made of transparent medical-grade polycarbonate, facilitating real-time observation of fluid level changes. Graduation markings are also present on the reservoir for volume calibration by the control system during detection. A sensor bracket, positioned in the middle of the infusion tubing, secures a photoelectric or electrochemical sensor module for parameter acquisition as the fluid flows through the detection location. The bracket's inner diameter matches that of the infusion tubing to prevent air bubbles caused by sudden changes in fluid flow rate. Internally, it features a light window or electrode mounting slot. The light window is made of high-transmittance medical-grade silicone, while the electrodes utilize a corrosion-resistant metal coating to enhance signal stability and repeatability. An indwelling needle connector, located at the distal end of the infusion tubing, connects to the indwelling needle line within the patient, forming the terminal pathway for fluid detection and return. In terms of design, the indwelling needle connector and the infusion tubing connector have corresponding structures and can form a sealed fit through a Luer conical connection. The inner wall of the connector has a flow-guiding conical surface structure to reduce resistance to liquid flow and minimize air bubble retention, thereby ensuring the integrity of the test sample. Through the synergistic cooperation of the above structures, the infusion tubing and indwelling needle connection circuit 400 can maintain the closure and stability of the fluid circuit throughout the entire process of body fluid extraction, testing, flushing, and refluxing. This not only reduces the risk of external contamination during body fluid testing but also avoids the costs and risks associated with wasting body fluid or discarding blood.

[0037] In one possible embodiment, the extraction and injection device includes a reservoir and a driving device connected to the reservoir. Controlling the extraction and injection device to extract a predetermined first volume of target bodily fluid from a pre-drilled hole in the target user into the infusion tube specifically includes the following steps: 311. Obtain the container attribute parameters of the driving device; 312. Determine the limiting position of the driving device based on the first volume and the container attribute parameters; 313. Control the driving device to drive the storage tank to generate negative pressure, so as to draw the target body fluid into the infusion tube; 314. When the driving device moves to the limit position and the target body fluid passes through the position of the detection module of the infusion tube, the driving device is controlled to stop drawing the target body fluid so that the target body fluid passes through the position of the detection module of the infusion tube.

[0038] The container attribute parameters include parameters such as the inner diameter of the cylinder wall of the drive device and the stroke. Specifically, after the extraction command is initiated, the main controller sends an extraction signal to the drive device. The drive device drives the piston or flexible diaphragm in the storage tank to move axially backward, creating a negative pressure zone in the inner cavity of the storage tank. The negative pressure is transmitted to the infusion tube port through the infusion tube, causing the body fluid to be drawn into the infusion tube through the reserved hole and Luer connector. The limiting position of the drive device is determined based on the structural parameters (container attribute parameters) of the storage tank. When the extraction and injection device is a syringe-type structure, the volume that can be extracted is determined by the linear stroke of the piston and the inner diameter of the syringe barrel. Before extraction begins, the controller calculates the distance the piston should advance based on the preset target volume, and the limiting mechanism limits the maximum stroke to prevent over-extraction. When the drive device adopts a spiral lifting structure, the current extraction volume is accurately calculated by detecting the number of piston rotations or the displacement stroke along the spiral path, combined with the inner diameter parameter of the storage tank. When the piston rotates to the preset number of rotations or stroke position, the control system triggers a limit signal, causing the drive device to automatically stop, thereby achieving mechanical closed-loop control of the extraction volume. This volume determination method based on container geometry and drive limiting effectively avoids volume calculation errors caused by pressure fluctuations or differences in liquid viscosity, further improving the stability and repeatability of extracted body fluids. In addition, the drive device can also be a structure driven by a stepper motor or servo motor, and linear adjustment of the volume can be achieved through pulse control. During the extraction process, pressure signals are acquired at 10–20 ms intervals and digitally filtered to eliminate false alarms caused by transient disturbances. When the detected pressure value exceeds a preset threshold and the rate of change slows down, it indicates that the fluid front has reached the sensing area of ​​the detection module, at which point the controller enters the fluid arrival confirmation phase. By using a drive device to accurately and quantitatively extract or remove blood, the probability of false triggering of the system due to fluctuations in the patient's physiological pressure is also significantly reduced.

[0039] Step S320: When the target body fluid in the infusion tube is detected to pass through the detection module, the detection module is controlled to detect the parameters of the target body fluid to obtain the target body fluid parameters.

[0040] The detection module's triggering is based on a timing signal of the body fluid flowing through the sensing area, with signal capture and response activation completed collaboratively by a photoelectric sensor and an electrochemical sensor. After the extraction is completed, the body fluid flows along the infusion tube and passes the detection module's location. At this point, the photoelectric sensor first detects a sudden change in the liquid medium's transmittance, thus determining that the body fluid has entered the detection area. Upon receiving the trigger signal, the monitor controls the photoelectric sensor to emit a light signal and obtains a voltage signal from the electrochemical sensor to simultaneously initiate both types of detection processes.

[0041] The photoelectric sensor is used to collect optical characteristic signals of body fluids to reflect the absorption and scattering characteristics of different components in the body fluid to light. The photoelectric sensor contains a multi-band light source and a photosensitive receiver array. The light source emits light signals of different wavelengths (e.g., red light, near-infrared light) sequentially. When the body fluid passes through the detection module, some of the light signals are absorbed or scattered. The transmitted light intensity detected by the receiver array forms a second light signal. After filtering and amplifying this second light signal, the monitor extracts the optical absorption coefficients corresponding to each wavelength, thereby forming the optical characteristic parameters of the target body fluid. Since different wavelengths have different absorption characteristics for oxyhemoglobin, deoxyhemoglobin, or other dissolved substances in the blood, optically related indicators such as blood oxygen saturation and dissolved gas concentration can be calculated through ratio analysis.

[0042] The electrochemical sensor is used to collect electrochemical response signals from body fluids to reflect chemical properties such as ion concentration, oxygen partial pressure, and pH. It detects the potential of the body fluid flowing across the sensor surface using the Nernst equation's electrode potential method, and the sensor generates a voltage signal in response to the potential difference. Alternatively, it can detect the current generated by a redox reaction; the potential difference of this voltage signal is related to the ion activity and reaction rate in the body fluid. After collecting the voltage signal, the monitor performs analog-to-digital conversion and noise suppression filtering to obtain the electrochemical characteristic parameters of the target body fluid. These parameters may include indicators such as redox potential, current response amplitude, and response time constant, reflecting blood gas parameters such as pH, pO2, and pCO2.

[0043] By parallel acquisition, feature extraction, compensation correction, and data fusion of optical and electrochemical signals from body fluids, this embodiment of the application, unlike traditional blood gas analyzers that rely on external sampling and offline analysis, can complete parameter detection within a closed fluid pathway within the body. This avoids contamination caused by sample exposure to the external environment and reduces detection delay. Due to the small size and short response time of the detection module, intermittent detection can also be performed periodically, enabling real-time dynamic monitoring of patients' blood gas or other body fluid parameters.

[0044] For easier understanding, please refer to Figure 5 , Figure 5This is a schematic diagram of a transmissive optical sensor 500 provided in an embodiment of this application. As can be seen, the transmissive optical sensor 500 includes a photodiode 501 and an LED 502. The purpose of this structure is to achieve real-time detection of optical characteristic parameters of body fluid samples through the emission and reception of light signals, thereby detecting hemoglobin concentration and other optical absorption characteristics in the body fluid. The LED 502, as a light source emitting unit, is fixedly mounted below the sensor bracket and is used to emit light signals of a specific wavelength upwards. The LED 502 can emit multi-band light, such as red light, blue light, or near-infrared light, according to detection requirements to adapt to different body fluid detection indicators. For example, red light is used to detect the absorption characteristics of oxyhemoglobin, while near-infrared light is used to assess the water content and scattering characteristics in the body fluid. The luminous intensity and pulse frequency of the LED 502 are adjusted in real time by the monitoring instrument control module to ensure a stable optical response signal under different body fluid concentrations and flow rates. To reduce external light interference, a light shield or aperture structure can be installed on the outside of the LED lamp 502 to concentrate the light beam and ensure that the light energy fully penetrates the detection liquid path area. A photodiode 501 is located on the opposite side of the LED lamp to receive the light signal after it passes through the body fluid and convert it into an electrical signal output. The photodiode 501 has high sensitivity and low noise characteristics, and can accurately respond to slight changes in light intensity, thereby enabling quantitative analysis of the light absorption or transmittance of the body fluid. When the body fluid passes through the detection channel, suspended particles, dissolved gases, and hemoglobin molecules in the body fluid will absorb and scatter the light signal, causing changes in the light intensity received by the photodiode 501. The sensor calculates the optical characteristic parameters of the body fluid, such as the light absorption coefficient, scattering coefficient, and specific absorptivity, by comparing the difference between the received signal and the transmitted signal. Figure 5 The transmissive optical sensor 500 shown is designed to enable non-contact, non-destructive optical detection in fluid flow. Furthermore, this structure not only features fast response and high sensitivity but also allows for multi-band spectral measurements, supporting the acquisition of multi-dimensional fluid parameters. Compared to traditional reflective detection methods, transmissive optical sensors reduce external scattering interference, improve measurement accuracy and signal stability, and are particularly suitable for clinical applications such as blood gas parameter monitoring, hemoglobin concentration analysis, and multi-component fluid detection.

[0045] In one possible embodiment, the detection module includes a photoelectric sensor, an electrochemical sensor, and a monitoring instrument connected to the photoelectric sensor and the electrochemical sensor; the photoelectric sensor includes a light-emitting device and a photodiode; controlling the detection module to detect the parameters of the target body fluid to obtain the target body fluid parameters specifically includes the following steps: 321. When the target body fluid passes the sensing position of the photoelectric sensor, the light-emitting device is controlled to emit a first light signal to the photodiode; 322. Acquire a second light signal generated in the infusion tube in response to the first light signal passing through the target body fluid via the photodiode; 323. Determine the optical characteristic parameters of the target body fluid based on the second optical signal, and send the optical characteristic parameters to the monitoring instrument; 324. Detect the voltage signal of the target body fluid using the electrochemical sensor; 325. Determine the electrochemical characteristic parameters of the target body fluid based on the voltage signal, and send the electrochemical characteristic parameters to the monitoring instrument; 326. The monitoring instrument generates the target body fluid parameters in response to the optical characteristic parameters and the electrochemical characteristic parameters.

[0046] When the target bodily fluid flows past the sensing position of the detection module, the multi-wavelength light source within the photoelectric sensor emits light signals sequentially at preset frequencies. Different wavelengths of light experience varying degrees of attenuation within the bodily fluid. The sensor's receiving end simultaneously acquires the intensity signals of the transmitted or reflected light, forming a second light signal. The monitoring instrument amplifies and denoises the second light signal, extracting the optical absorptivity and scattering ratio for each wavelength to obtain optical characteristic parameters. These parameters may include the absorption coefficient, spectral intensity ratio, or transmittance change rate at a specific wavelength, reflecting indicators such as the concentration of oxyhemoglobin, the proportion of deoxyhemoglobin, or the lactic acid content in the blood.

[0047] The electrochemical sensor is used to detect changes in ion activity and potential in body fluids to obtain electrochemical characteristic parameters that reflect gas partial pressure, pH, conductivity, and metabolite concentration. When a body fluid sample comes into contact with the working electrode surface of the electrochemical sensor, the ion-selective membrane on the electrode surface only allows specific ions (such as H+) to pass through. + Na + K + Ca 2+ Cl -The electrochemical sensor allows ions (such as hydrogen permeate) to pass through while preventing other ions or molecules from entering. The principle of this detection is based on the Nernst equation; the difference in ion concentration across the membrane generates a measurable potential difference. The monitor applies a voltage signal to the electrochemical sensor to create a stable potential field, while a reference potential is established in a standard solution via a reference electrode. The electrochemical sensor measures the potential difference between the working electrode and the reference electrode in real time and calculates the activity concentration of the analyte ion based on the electrode potential method, thus obtaining the ion parameters in blood or other body fluid samples. When detecting blood gas parameters, such as pCO2, the electrochemical sensor is often used in conjunction with a chemical method. CO2 molecules first pass through the selective permeation membrane on the sensor surface into the internal buffer solution, where they react with water to generate H2O. + and HCO3 - This causes pH changes, and the monitor calculates the CO2 concentration by detecting the potential change of the pH electrode, thus obtaining the pCO2 parameter of the blood. For the detection of oxygen partial pressure (pO2) and metabolite concentrations (such as glucose (Glu) and lactate (Lac)), the sensor uses the electrode current method. By applying a constant voltage between the working electrode and the counter electrode, a redox reaction occurs under the action of a catalytic enzyme, and the resulting redox current value is measured. The amplitude of this current has a quantitative correlation with the reaction rate and the concentration of the analyte. After eliminating noise interference through multi-point sampling and digital filtering algorithms, the monitor calculates electrochemical characteristic parameters, such as current peak value, potential difference, and response time constant. In addition, to compensate for the influence of ambient temperature on the electrochemical reaction rate, a temperature sensor is integrated into the detection module to monitor the body fluid temperature in real time and generate a temperature compensation coefficient. The monitor corrects the measured electrochemical signal according to this compensation coefficient to ensure that the measurement results remain accurate and consistent under different environmental or body temperature changes. It is worth noting that the ion-selective membrane on the surface of the electrochemical sensor electrode is generally made of highly biocompatible materials. It can selectively transmit specific ions based on the size exclusion effect or electrostatic interaction mechanism. This not only improves the selectivity and sensitivity of the measurement, but also effectively avoids drift errors caused by protein adsorption or the deposition of impurities in the blood.

[0048] Specifically, the monitor inputs optical and electrochemical feature parameters into a fusion algorithm model to generate the final target body fluid parameters. This fusion algorithm can be implemented based on a confidence-weighted linear regression model or a neural network model. The monitor first determines the signal-to-noise ratio and stability of the two types of parameters. If the optical parameter has a high signal-to-noise ratio, its weight in the fusion model is increased; if the electrochemical parameter contributes more to the current measurement index (e.g., blood gas parameters), its weighting ratio is increased accordingly. The target body fluid parameters output by the fusion model include multiple indicators such as blood oxygen saturation (SpO2), pH value, pCO2, pO2, and ion concentration, and a confidence score is generated simultaneously. The confidence score reflects the reliability of the current detection data. If it falls below a preset threshold, the system automatically issues a retest command to ensure the accuracy and repeatability of the output data.

[0049] In addition, the monitor can store the target body fluid parameters obtained from this test to the system data module and compare them with the data from the previous test cycle. If the difference between adjacent cycles exceeds the preset physiological variation range (e.g., more than 5%), the system triggers an abnormality marker, prompting clinical monitoring personnel or automatically adjusting the testing frequency to achieve real-time dynamic monitoring of the patient's body fluid status.

[0050] Through the detection process of the detection module, photoelectric and electrochemical sensors work together to achieve multimodal detection of body fluid parameters. Compared with traditional offline blood gas analysis methods, no additional sampling or external detection is required. Parameter measurement and data generation can be completed directly in the body's fluid pathways. Furthermore, due to the small size and short response time of the detection module, it can support periodic or intermittent detection modes, avoiding blood waste and improving the real-time performance and patient safety of monitoring.

[0051] In one possible embodiment, the monitor generates the target body fluid parameters in response to the optical and electrochemical characteristic parameters, specifically including the following steps: 3261. Determine multiple wavelength parameters in the optical characteristic parameters; 3262. Determine multiple first body fluid parameters corresponding to the multiple wavelength parameters according to the preset mapping relationship between wavelength parameters and body fluid parameters; 3263. Obtain the accuracy parameters of the electrochemical sensor and the temperature parameters of the target body fluid; 3264. Determine the temperature compensation parameters of the electrochemical sensor based on the temperature parameters and the accuracy parameters; 3265. The electrochemical characteristic parameters are compensated according to the temperature compensation parameters to obtain multiple compensated electrochemical parameters; 3266. Determine multiple second body fluid parameters corresponding to the multiple compensating electrochemical parameters based on the preset mapping relationship between electrochemical parameters and body fluid parameters; 3267. Determine the target body fluid parameter based on the plurality of first body fluid parameters and the plurality of second body fluid parameters.

[0052] In this method, after receiving the second optical signal from the photoelectric sensor, the monitoring instrument decomposes the absorption ratio of each wavelength through a spectral analysis module. This method pre-stores multiple models relating wavelengths to body fluid parameters. For example, in the red light (approximately 660 nm) and near-infrared light (approximately 940 nm) bands, the ratio of oxyhemoglobin (HbO2) to deoxyhemoglobin (Hb) concentrations in the blood can be determined by ratio calculation, thereby calculating blood oxygen saturation (SpO2). Furthermore, the optical attenuation coefficient at different wavelengths can also reflect characteristics such as body fluid turbidity, lactic acid concentration, or protein content.

[0053] Temperature compensation and accuracy correction of electrochemical characteristic parameters are used to offset the influence of external environmental and individual body temperature changes on the sensing response. Since both the electrochemical reaction rate and electrode potential are affected by temperature, the detection results will be biased without compensation. Therefore, by acquiring the accuracy parameters of the electrochemical sensor (including sensitivity coefficient, response hysteresis time, and electrode polarization voltage) and obtaining the temperature parameters in real time from the electrochemical sensor, the temperature compensation parameters of the sensor under the current temperature conditions are calculated based on a preset temperature response function. Typical compensation models can use linear or exponential correction functions: ΔE = k1 × (T - T0) + k2 × (T - T0) 2 Where ΔE is the correction potential, T is the detection temperature, T0 is the calibration temperature, and k1 and k2 are the temperature coefficients of the sensor. The monitor uses these parameters to compensate the original electrochemical signal, obtaining multiple compensated electrochemical parameters to ensure consistency in the electrochemical response measured under different environments. Then, using a preset electrochemical mapping relationship, the compensated electrochemical parameters are converted into multiple secondary fluid parameters, such as pH, pO2, pCO2, and Na+. + K + These are some of the indicators. Through compensation and mapping processes, the electrochemical measurement results exhibit higher repeatability and long-term stability.

[0054] Step S330: Control the liquid circuit switch to perform the opening action, and control the flushing device to inject a preset second volume of functional liquid into the infusion tube.

[0055] The opening action of the liquid circuit switch is used to re-establish the connection between the infusion bag and the infusion tubing, providing an independent fluid channel for the injection of functional fluids. After the detection module completes a body fluid parameter measurement, the main controller receives a detection completion signal and then sends an opening action command to the liquid circuit switch, causing its internal valve core to rotate or slide to the conducting position. The injection control process of the flushing device achieves precise regulation of the volume and flow rate of the functional fluid through the coordination of the drive device and pressure feedback. When the liquid circuit switch is turned on, the main controller sends an injection command to the drive mechanism of the flushing device. The drive mechanism drives the injection piston forward axially, injecting the functional fluid in the reservoir into the infusion tubing at a preset rate. To prevent the liquid flow rate from impacting the detection module or the liquid circuit due to excessive speed, the controller dynamically adjusts the injection rate based on pressure sensor feedback, keeping the liquid flow rate within the range of 0.3 to 0.6 mL / s, thus forming a stable fluid front. After the flushing fluid enters the infusion tubing, it first pushes the residual body fluid away from the detection module area and gradually flows towards the Luer connector along the original flow direction. At this point, the detection module continuously monitors the change in optical transmittance. When the system detects that the liquid transmittance has recovered to the standard threshold of the functional liquid, it confirms that the rinsing phase has ended and enters the body fluid return phase.

[0056] Specifically, the fluid reflux stage is achieved through the combined control of the flushing device and the extraction-injection device, allowing the detected target fluid to be reinjected into the target user's body. Driven by the functional fluid, the target fluid at the front end of the detection module is pushed to the end of the infusion tube near the pre-drilled hole. When the main controller detects that the fluid flow has reached the Luer connector, it sends a reflux trigger signal, controlling the extraction-injection device to switch from extraction mode to injection mode. The drive device drives the piston in the reservoir to move in the opposite direction, creating positive pressure output, thereby smoothly injecting the fluid into the target user's body through the pre-drilled hole. Throughout the reflux process, the pressure sensor monitors the pressure changes within the fluid circuit in real time. When the pressure returns to physiological levels (e.g., 10–15 kPa) and stabilizes, the system determines that the reflux process is complete. Subsequently, the fluid circuit switch automatically closes, forming a new sealed state, preparing for the next fluid detection cycle. Compared to traditional testing devices that require manual drainage and reinfusion, the method described in this application can automatically complete the injection of functional fluids and the reinfusion of bodily fluids in a fully closed loop, improving operational safety and avoiding blood waste. Simultaneously, the system can automatically set the flushing frequency and volume according to the testing cycle, ensuring the fluid path remains clean before each test and preventing sample cross-contamination.

[0057] Step S340: When the functional fluid in the infusion tube is detected to have passed through the detection module, the extraction and injection device is controlled to return the target body fluid to the target user.

[0058] The triggering of fluid reflux is based on the flow state of the functional fluid in the infusion tubing. When the detection module detects the functional fluid's leading edge passing the sensor's sensing area, the fluid reflux control phase begins. After the functional fluid is injected into the storage tank, it propels along the infusion tubing, gradually pushing residual fluid in the detection area towards the pre-drilled hole. When the photoelectric sensor detects that the fluid transmittance has risen to the standard value for the functional fluid, and the pressure sensor indicates that the fluid pressure has reached a stable range, the main controller confirms that the functional fluid has passed through the detection module and immediately issues a reflux start command. At this point, the fluid path branch connected to the infusion bag is closed, leaving only the reflux path connected to the target user open to prevent backflow or fluid mixing.

[0059] Specifically, during the fluid return phase, the injection device switches from negative pressure extraction to positive pressure injection. By reversing the piston's movement, smooth fluid return is achieved. The main controller controls the drive motor to rotate in the opposite direction, moving the piston inside the reservoir along the pushing direction, creating a positive pressure environment within the reservoir. This positive pressure acts on the target fluid through the infusion tubing, causing the fluid, propelled by the functional fluid, to flow back into the target user's body via the Luer connector and pre-drilled holes. To ensure the return rate matches the body's blood pressure, the pressure sensor output is continuously monitored during control, and the drive motor's pushing speed is adjusted based on the feedback signal. Generally, the target pressure for fluid return is set slightly higher than the patient's venous pressure (e.g., 12–16 kPa) to ensure smooth fluid return without reverse flow. Thus, through fluid path status recognition, positive pressure control, and dynamic safety protection, automatic return and fluid path reset of the target fluid are achieved, featuring high safety, controllable precision, and stable operation. At the same time, it ensures the cleanliness of the fluid path and the integrity of the sample in multiple testing cycles of the body fluid detection system, providing key support for achieving continuous and non-wasteful monitoring of body fluid parameters.

[0060] In one possible embodiment, the body fluid parameter detection system further includes an infusion bag connected to the fluid circuit switch, the infusion bag containing the functional fluid, and controlling the extraction and injection device to return the target body fluid to the target user specifically includes the following steps: 341. In response to the opening action of the liquid circuit switch, control the extraction and injection device to extract the functional liquid from the infusion bag to the flushing device; 342. The flushing device responds to the injection action of the extraction and injection device by injecting the second volume of the functional liquid into the infusion tube; 343. At the position where the functional liquid passes through the detection module, control the injection action of the extraction and injection device to drive the target body fluid to flow back to the target user through the reserved hole.

[0061] The functional fluid in the infusion bag is used for cleaning the fluid pathway and driving fluid return after testing. Its connection to the fluid circuit switch is centrally managed by the main controller. When the system completes testing and enters the return preparation stage, the main controller receives a "test complete" signal from the testing module and immediately sends an opening command to the fluid circuit switch, connecting the infusion bag and the flushing device. At this time, the infusion bag is in a high position or equipped with a micro-positive pressure structure (such as a flexible reservoir and elastic membrane), allowing the functional fluid to flow smoothly into the inlet of the extraction and injection device after the passage is opened. After the extraction and injection device draws a predetermined volume of functional fluid from the infusion bag, the main controller issues an injection command, driving the piston to move forward, injecting the functional fluid from the reservoir into the infusion tubing at a constant rate. During the injection process, data from the pressure and flow sensors are collected in real time and dynamically adjusted to maintain the fluid flow rate within a safe range of 0.3–0.6 mL / s, preventing excessively fast flow from impacting the testing module or causing discomfort to the patient. When the functional liquid flows through the detection module, it cleans and washes the sensor surface, removing any residual bodily fluids and microbubbles that adhered to the sensor in the previous detection, thereby ensuring the accuracy and stability of the sensor response.

[0062] Specifically, when the functional fluid advances past the detection module and pushes the target body fluid to the end of the infusion tube, the extraction and injection device, under the control logic, reverses the flow to drive the reservoir piston, creating positive pressure output to achieve the reflux injection of the target body fluid. The main controller determines whether the functional fluid has completely passed through the detection module by monitoring changes in the optical signal of the detection module and real-time feedback from the pressure sensor. When the photoelectric sensor detects that the transmittance has recovered to the standard threshold of the functional fluid and the pressure curve has entered a stable phase, the system confirms that the body fluid in the detection module has been completely replaced by the functional fluid. At this time, the controller switches the drive mode, causing the extraction and injection device to execute the reflux command. The reservoir piston moves forward, creating a pushing pressure in the tubing that is consistent with the direction of blood flow, pushing the residual body fluid back into the target user's body through the Luer connector and the pre-drilled hole. To avoid pressure fluctuations, the control algorithm introduces a fluid damping compensation factor to ensure a smooth transition of the body fluid reflux pressure curve, preventing excessively rapid local reflux due to instantaneous pressure increases.

[0063] In one possible embodiment, the infusion tubing includes a first infusion tubing and a second infusion tubing. The first infusion tubing includes a detachable connector for connecting to the pipe connector of the pre-reserved hole of the target user. A sensor bracket and a control valve are provided on the first infusion tubing. The sensor bracket is used to fix the photoelectric sensor in the detection module. The control valve is used to control the fluid communication state of the first infusion tubing to open or close the body fluid flow path. The end of the second infusion tube furthest from the detection module is connected to the reservoir of the extraction and injection device, and the end of the second infusion tube closest to the detection module is connected to the extraction and injection device, so that the extraction and injection device can form a closed fluid path with the reserved hole through the detachable connection joint, thereby realizing the extraction, detection and reinjection of the target body fluid; a pressure sensor is provided between the flushing device and the detection module, and the pressure sensor is used to measure the blood pressure parameters of the target user, or, when the control valve is in the closed state, the pressure sensor detects the tubing pressure in the first infusion tube.

[0064] The first infusion tube serves as the fluid pathway connecting the user's pre-drilled needle to the reservoir. Its structure is translucent, with an inner lining coated with fluorescent material and a thin plastic film for insulation from bodily fluids. A detachable connector allows connection to the user's pre-drilled needle; preferably, this connector is a Luer connector, a common quick-connect interface in the medical industry. Its conical sealing characteristic ensures reliable liquid sealing without the need for additional gaskets. When the infusion tube connects to the patient's pre-drilled hole, a rotating locking mechanism creates negative pressure adsorption, ensuring uniform pressure distribution on the contact surface and preventing air bubbles from entering the fluid system due to minor leaks. To prevent loosening over time, this embodiment incorporates an anti-rotation groove in the Luer connector's locking structure and an anti-slip texture on the outer wall for easy operation by medical personnel. The sensor bracket is positioned in the middle of the first infusion tube, corresponding to the optical path of the detection module. Made of medical-grade polycarbonate, the bracket offers high transparency and good mechanical stability, preventing light scattering interference during optical measurements. The bracket surface features precision slots for mounting the photoelectric sensor module, ensuring the sensor remains stable during prolonged operation. The photoelectric sensor and the light window of the infusion tubing are fixed in position relative to each other. The light window is made of anti-fogging silicone transparent film to reduce the impact of moisture in the body fluid on the light signal detection. A control valve is used to control the opening and closing of the tubing; preferably, it is a three-way control valve. The three-way control valve is located at the end of the infusion tubing connected to the target user and is used to switch the on / off state of the fluid path according to control commands. When the three-way control valve is closed and connected to the pre-drilled hole in the patient's body, it can be used to detect the pressure in the tubing. At this time, the pressure sensor detects the static pressure change in the infusion tubing to determine the tubing's sealing performance and calibrate the pressure reference. By switching the state of this control valve, safe isolation can be achieved between body fluid extraction, detection, and blood pressure monitoring, avoiding interference with blood pressure detection accuracy during the fluid extraction process.

[0065] The second infusion tube serves as the fluid passage connecting the storage tank and the extraction / injection device. Its function is to achieve a closed-loop operation of body fluid extraction, functional fluid flushing, and reflux control. To meet the high-precision transmission requirements of micro-volume fluids, the second infusion tube is made of flexible medical-grade silicone tubing with a hydrophobic coating on its inner wall, effectively reducing fluid retention and adhesion. Both ends of the infusion tube are connected to the storage tank and the extraction / injection device via detachable connectors for easy cleaning and replacement. Structurally, a one-way valve is installed at the end near the storage tank to prevent body fluid from flowing back into the storage tank during extraction; a pressure sensor interface is installed at the end near the detection module to monitor changes in fluid pressure within the tube in real time. When the extraction / injection device performs the extraction operation, the drive device moves the piston inside the storage tank backward, creating a negative pressure zone within the second infusion tube. This draws the target body fluid sequentially from the pre-drilled hole through the Luer connector, the first infusion tube, and the detection module into the fluid path. During the extraction process, the system adjusts the drive rate based on feedback from the pressure sensor to ensure that the extraction rate matches the fluid flow rate, preventing blood aeration or hemolysis caused by excessive negative pressure. After the test is completed, the extraction injection device reverses the piston, creating a positive pressure zone in the reservoir. Under pressure, the fluid flows back through the second infusion tube to the detection module and Luer connector, achieving the return injection of the target fluid. This closed-loop fluid circuit structure enables multiple tests and reuse without damaging the integrity of the fluid, thus significantly improving the safety and economy of the system.

[0066] Furthermore, to prevent the risk of contamination caused by prolonged retention of bodily fluids, a miniature anti-backflow valve and a detachable filter unit are installed at the connection port between the second infusion tube and the storage tank. The filter unit contains a 0.2μm-level medical-grade filter membrane, which can trap particles and bacteria during each extraction and recirculation process, keeping the fluid path clean. This structure not only improves the safety and lifespan of the bodily fluid detection system but also provides reliable assurance for multi-cycle continuous detection. The infusion tube structure achieves a stable connection between the bodily fluid interface and optical detection through the first infusion tube, and dynamic control and closed-loop management of bodily fluid flow through the second infusion tube. The synergistic effect of these two components ensures that the bodily fluid parameter detection system maintains fluid path stability and measurement accuracy during extraction, detection, cleaning, and recirculation, enabling automated and non-destructive intermittent bodily fluid detection. It is worth noting that during bodily fluid extraction and recirculation, the monitor suspends the operation of the invasive pressure sensor after receiving a control command to avoid pressure fluctuations in the fluid path caused by the extraction or drainage of the storage tank interfering with the accuracy of blood pressure measurement.

[0067] In one possible embodiment, the functional liquid includes at least one of physiological saline or deionized water, and an anticoagulant; the anticoagulant is used to prevent clotting during blood measurement.

[0068] Physiological saline or deionized water serves as the base solution for the functional fluid, used to flush and replace the fluid system before and after body fluid testing. Before testing, a certain volume of functional fluid is injected into the infusion tubing to bring the ion concentration of the fluid environment within the tubing close to the ion strength of the target body fluid. This ensures fluid system equilibrium at the initial extraction stage, preventing osmotic pressure shocks or ion migration deviations caused by sudden changes in electrolyte concentration. After testing, physiological saline or deionized water is used to replace residual body fluid in the tubing, effectively cleaning the detection module, optical window, and electrochemical electrode surfaces. This prevents residual blood from coagulating or oxidizing within the tubing, which could affect the accuracy of subsequent tests. Furthermore, if the test subject is an animal experimental model or a body fluid type with a risk of electrochemical interference, deionized water can be used as a dilution and flushing medium to reduce interference from conductive ions in the solution on the electrochemical signal. The high purity of deionized water effectively reduces background current noise, improving the sensitivity and signal-to-noise ratio of the electrochemical sensor at low concentrations.

[0069] The anticoagulant is primarily used to prevent coagulation of blood or other protein-containing body fluids within the fluid path, ensuring the continuity and safety of fluid testing and reflux. The anticoagulant can be at least one of heparin, sodium citrate, or disodium ethylenediaminetetraacetate (EDTA), with the specific selection determined based on the testing cycle and the type of body fluid being tested. Heparin, as a natural anticoagulant, effectively blocks the coagulation cascade by enhancing the inhibitory effect of antithrombin III on thrombin, and is widely used in blood gas monitoring and extracorporeal circulation devices. Sodium citrate inhibits prothrombin activation by chelating calcium ions in the blood, making it an ideal anticoagulant for short-term blood sample preservation; EDTA primarily works by chelating divalent metal ions (such as calcium ions). 2+ Mg 2+ This method blocks the coagulation pathway and is suitable for fluid systems requiring multiple tests or long-term indwelling. In practical applications, the anticoagulant can be added to the functional fluid in a proportion ranging from 0.1% to 0.5% (by mass), which effectively inhibits coagulation without significantly interfering with the electrochemical detection signal.

[0070] Furthermore, to further enhance the safety and reliability of the testing, the functional fluid is stored in an independent infusion bag connected to the fluid circuit switch. The infusion bag is equipped with a one-way gas filter and an optical level detection window. The gas filter prevents air bubbles from entering the fluid circuit, ensuring the continuity of the flushing process; the level detection window, in conjunction with the optical sensing unit of the monitor, monitors the fluid level changes in real time, issuing a replenishment signal when the functional fluid is insufficient. In this way, the cleanliness and controllability of the liquid medium are maintained throughout the three stages of testing, flushing, and reflux, thereby ensuring the accuracy and reliability of the body fluid parameter testing.

[0071] For easier understanding, please refer to Figure 6, Figure 6 This is a schematic diagram of a scenario where blood is drawn from an indwelling needle, as provided in an embodiment of this application. Figure 6 This is a detection system comprising an indwelling needle establishing a venous access pathway, an infusion tubing connected to the indwelling needle, a fluid circuit switch for controlling the direction of fluid flow, an aspiration and injection device for drawing and reinfusing bodily fluids, a detection module connected in parallel with the infusion tubing, and a monitor electrically connected to the detection module. Specifically, during operation, medical personnel first establish a venous access pathway using the indwelling needle, ensuring that bodily fluids (such as venous blood) can be precisely controlled within a closed tubing system. The aspiration and injection device, connected to the infusion tubing via the fluid circuit switch, performs the blood aspiration action. When the aspiration and injection device generates negative pressure, fresh venous blood is drawn into the infusion tubing through the indwelling needle and flows along the fluid circuit to the location of the detection module. At this time, the transmissive optical sensor of the detection module detects the optical characteristic signals of the blood in real time, including light absorptivity, transmittance, and chromaticity parameters, and transmits the signals to the monitor for data analysis and parameter display. This process enables dynamic monitoring of blood parameters without disrupting the closed blood circuit, avoiding the additional trauma and risks to the human body caused by traditional blood drawing tests.

[0072] visible, Figure 6 The blood extraction and testing system shown achieves body fluid detection based on venous access through the coordinated action of indwelling needle, infusion tubing, fluid circuit switch, extraction and injection device, and detection module.

[0073] For easier understanding, please refer to Figure 7 , Figure 7 This is a schematic diagram illustrating a scenario of blood reinjection into a patient, provided by an embodiment of this application. As can be seen, the process of blood extraction, parameter monitoring, and non-destructive reinjection achieves blood reinfusion after body fluid monitoring. It mainly includes a patient indwelling catheter, an extraction and injection device, a monitoring unit, and a tubing control system. Each module ensures the safety and efficiency of blood reinjection through the coordinated linkage of fluid and electrical circuits. Specifically, the patient establishes a connection with the external tubing through an indwelling arterial or venous catheter. This indwelling catheter, serving as the blood reinjection channel, is made of biocompatible materials to ensure no risk of hemolysis or thrombosis during blood reinjection, while also possessing stable blood flow conduction capabilities. The blood extraction and injection device is the core of the blood reinjection process. It achieves bidirectional blood flow through a mechanical push-pull structure: during monitoring, the device extracts a preset volume of blood from the indwelling channel to complete parameter detection; after the detection is completed, the device injects the blood back into the patient's body at a controllable flow rate (e.g., adjustable within the range of 0.5-2 mL / s). Throughout the entire process, no blood is discharged, and the "extraction-reinjection" process is fully controlled, which significantly reduces blood waste compared to the method of single blood draw for testing.

[0074] In addition, the monitor is electrically connected to the aspiration and injection device. On the one hand, it collects and displays blood gas, electrolyte, and other parameters in real time; on the other hand, it outputs control signals to regulate the timing, flow rate, and pressure of reinjection from the aspiration and injection device, ensuring that the reinjection process is adapted to the patient's circulatory status and avoiding risks such as blood pressure fluctuations and increased circulatory load caused by improper reinjection. The fluid circuit switch and infusion bag (containing anticoagulant saline) play a key auxiliary role in the reinjection process. Before reinjection, the fluid circuit switch closes the infusion passage to prevent infusion fluid from mixing with the blood and affecting monitoring accuracy. After reinjection, the fluid circuit switch opens, and the saline in the infusion component flushes the tubing at a stable flow rate to maintain the patency of the indwelling passage and prepare for the next "aspiration-injection" cycle, that is, to complete the intermittent detection of blood gas parameters.

[0075] As can be seen, by implementing the intermittent detection method for body fluid parameters provided in this application embodiment, the method is applied to the main controller of a body fluid parameter detection system. The body fluid parameter detection system includes: an infusion tube, a pipetting module connected to the infusion tube, and a detection module disposed on the infusion tube. The pipetting module includes an extraction and injection device, a liquid circuit switch, and a flushing device connected to the extraction and injection device. The extraction and injection device is connected to the liquid circuit switch and the infusion tube. The method includes: controlling the liquid circuit switch to perform a closing action; controlling the extraction and injection device to extract a preset first volume of target body fluid from a pre-reserved hole of the target user into the infusion tube; when the target body fluid in the infusion tube is detected to have passed through the detection module, controlling the detection module to detect the parameters of the target body fluid to obtain the target body fluid parameters; controlling the liquid circuit switch to perform an opening action; and controlling the flushing device to inject a preset second volume of functional liquid into the infusion tube; when the functional liquid in the infusion tube is detected to have passed through the detection module, controlling the extraction and injection device to return the target body fluid to the target user. Thus, on the one hand, by using electrochemical or optical sensors installed in the infusion line, detection can be performed when the body fluid is drawn and passes through the sensor's sensing position. After the measurement is completed, the body fluid is injected back into the human or animal body, thereby reducing blood waste. On the other hand, by connecting the tubing to the patient's pre-drilled hole for detection, there is no need to connect an additional extracorporeal circulation device, thereby reducing the cost of detection.

[0076] The above mainly describes the solutions of the embodiments of this application from the perspective of the method execution process. It is understood that, in order to achieve the above functions, the intermittent detection device for body fluid parameters includes hardware structures and / or software modules corresponding to the execution of each function. Those skilled in the art should readily recognize that, in conjunction with the units and algorithm steps of the various examples described in the embodiments provided herein, this application can be implemented in hardware or a combination of hardware and computer software. Whether a function is executed in hardware or by computer software driving hardware depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.

[0077] This application embodiment can divide the intermittent detection device for body fluid parameters into functional units according to the above method example. For example, each function can be divided into a separate functional unit, or two or more functions can be integrated into one processing unit. The integrated unit can be implemented in hardware or as a software functional unit. It should be noted that the unit division in this application embodiment is illustrative and only represents one logical functional division; other division methods may be used in actual implementation.

[0078] When dividing each function into modules according to its corresponding function. Figure 8 This is a functional module block diagram of an intermittent detection device for body fluid parameters provided in an embodiment of this application. The intermittent detection device 800 for body fluid parameters is applied to a body fluid parameter detection system. The body fluid parameter detection system includes: an infusion tube, a pipetting module connected to the infusion tube, and a detection module disposed on the infusion tube. The pipetting module includes an injection device, a fluid circuit switch, and a flushing device connected to the injection device. The injection device is connected to the fluid circuit switch and the injection device is connected to the infusion tube. The device includes: The control unit 810 is used to control the liquid circuit switch to perform a closing action, and to control the extraction and injection device to extract a preset first volume of target body fluid from the target user's reserved hole into the infusion tube; The monitoring unit 820 is used to control the detection module to detect the parameters of the target body fluid when the target body fluid in the infusion tube passes through the detection module, and obtain the target body fluid parameters. The control unit 810 is also used to control the liquid circuit switch to perform an opening action, and to control the flushing device to inject a preset second volume of functional liquid into the infusion tube; The execution unit 830 is used to control the extraction and injection device to return the target body fluid to the target user when the functional fluid in the infusion tube is detected to pass through the detection module.

[0079] In one possible embodiment, the extraction and injection device includes a reservoir and a drive device connected to the reservoir. The control unit 810, in controlling the extraction and injection device to extract a predetermined first volume of target bodily fluid from a pre-drilled hole in the target user into the infusion tube, is specifically used for: Obtain the container attribute parameters of the driving device; The limiting position of the driving device is determined based on the first volume and the container attribute parameters. The drive device is controlled to drive the storage tank to generate negative pressure, so as to draw the target body fluid into the infusion tube; When the driving device moves to the limit position and the target body fluid passes through the position of the detection module of the infusion tube, the driving device is controlled to stop drawing the target body fluid so that the target body fluid passes through the position of the detection module of the infusion tube.

[0080] In one possible embodiment, the detection module includes a photoelectric sensor, an electrochemical sensor, and a monitoring instrument connected to the photoelectric sensor and the electrochemical sensor; the photoelectric sensor includes a light-emitting device and a photodiode; the monitoring unit 820 is specifically used for controlling the detection module to detect the parameters of the target body fluid and obtain the target body fluid parameters, in order to: When the target body fluid passes the sensing position of the photoelectric sensor, the light-emitting device is controlled to emit a first light signal to the photodiode; The photodiode acquires the second light signal generated by the target body fluid in response to the first light signal within the infusion tube. The optical characteristic parameters of the target body fluid are determined based on the second optical signal, and the optical characteristic parameters are sent to the monitoring instrument. The voltage signal of the target body fluid is detected by the electrochemical sensor; The electrochemical characteristic parameters of the target body fluid are determined based on the voltage signal, and the electrochemical characteristic parameters are sent to the monitoring instrument. The monitoring instrument generates the target body fluid parameters in response to the optical and electrochemical characteristic parameters.

[0081] In one possible embodiment, the monitoring unit 820 is specifically configured to, in relation to the monitoring instrument generating the target body fluid parameters in response to the optical characteristic parameters and the electrochemical characteristic parameters: Determine multiple wavelength parameters among the optical characteristic parameters; Multiple first body fluid parameters corresponding to the multiple wavelength parameters are determined according to the preset mapping relationship between wavelength parameters and body fluid parameters; The accuracy parameters of the electrochemical sensor and the temperature parameters of the target body fluid are obtained; The temperature compensation parameters of the electrochemical sensor are determined based on the temperature parameters and the accuracy parameters. The electrochemical characteristic parameters are compensated based on the temperature compensation parameters to obtain multiple compensated electrochemical parameters; Multiple second body fluid parameters corresponding to the multiple compensating electrochemical parameters are determined based on the preset mapping relationship between electrochemical parameters and body fluid parameters; The target body fluid parameter is determined based on the plurality of first body fluid parameters and the plurality of second body fluid parameters.

[0082] In one possible embodiment, the body fluid parameter detection system further includes an infusion bag connected to the fluid circuit switch, the infusion bag containing the functional fluid, and the execution unit 830, in controlling the extraction and injection device to return the target body fluid to the target user, is specifically used for: In response to the opening action of the liquid circuit switch, the extraction and injection device is controlled to extract the functional liquid from the infusion bag and into the flushing device; The flushing device responds to the injection action of the extraction and injection device by injecting the second volume of the functional liquid into the infusion tube; At the location where the functional liquid passes through the detection module, the injection action of the extraction and injection device is controlled to drive the target body fluid to flow back to the target user through the reserved hole.

[0083] In one possible embodiment, the infusion tubing includes a first infusion tubing and a second infusion tubing. The first infusion tubing includes a detachable connector for connecting to the pipe connector of the pre-reserved hole of the target user. A sensor bracket and a control valve are provided on the first infusion tubing. The sensor bracket is used to fix the photoelectric sensor in the detection module. The control valve is used to control the fluid communication state of the first infusion tubing to open or close the body fluid flow path. The end of the second infusion tube furthest from the detection module is connected to the reservoir of the extraction and injection device, and the end of the second infusion tube closest to the detection module is connected to the extraction and injection device, so that the extraction and injection device can form a closed fluid path with the reserved hole through the detachable connection joint, thereby realizing the extraction, detection and reinjection of the target body fluid; a pressure sensor is provided between the flushing device and the detection module, and the pressure sensor is used to measure the blood pressure parameters of the target user, or, when the control valve is in the closed state, the pressure sensor detects the tubing pressure in the first infusion tube.

[0084] In one possible embodiment, the functional liquid includes at least one of physiological saline or deionized water, and an anticoagulant; the anticoagulant is used to prevent clotting during blood measurement.

[0085] It should be noted that the specific implementation of each operation can adopt the corresponding description of the above embodiment of the intermittent detection method for body fluid parameters. An intermittent detection device 800 for body fluid parameters can be used to execute one or all of the embodiments of the above-described intermittent detection method for body fluid parameters, which will not be described again.

[0086] As can be seen, the intermittent detection device for body fluid parameters described in this application embodiment is applied to a body fluid parameter detection system. This system includes: an infusion tube, a detection module, an extraction and injection device, a fluid circuit switch, and a flushing device. The device controls the fluid circuit switch to close, and controls the extraction and injection device to extract a preset first volume of target body fluid from a pre-drilled hole in the target user into the infusion tube. When the target body fluid in the infusion tube is detected passing through the detection module, the detection module detects the parameters of the target body fluid to obtain the target body fluid parameters. The device then controls the fluid circuit switch to open, and controls the flushing device to inject a preset second volume of functional liquid into the infusion tube. When the functional liquid in the infusion tube is detected passing through the detection module, the extraction and injection device returns the target body fluid to the target user. This reduces blood waste and lowers detection costs during blood gas parameter detection.

[0087] This application also provides an intermittent detection system for body fluid parameters, wherein the intermittent detection system for body fluid parameters performs some or all of the steps of any of the methods described in the above method embodiments.

[0088] This application also provides a computer program product, which includes a non-transitory computer-readable storage medium storing a computer program operable to cause a computer to perform some or all of the steps of any of the methods described in the above method embodiments. The computer program product may be a software installation package, and the computer includes an intermittent detection device for bodily fluid parameters.

[0089] It should be noted that, for the sake of simplicity, the above embodiments are all described as a series of actions. Those skilled in the art should understand that this application is not limited to the described order of actions, as some steps in the embodiments of this application can be performed in other orders or simultaneously. Furthermore, those skilled in the art should also understand that the embodiments described in the specification are preferred embodiments, and the actions, steps, modules, or units involved are not necessarily essential to the embodiments of this application.

[0090] In the above embodiments, the descriptions of each embodiment in this application have different focuses. For parts not described in detail in a certain embodiment, please refer to the relevant descriptions in other embodiments.

[0091] Those skilled in the art will understand that all or part of the processes in the methods of the above embodiments can be implemented by a computer program instructing related hardware. This program can be stored in a computer-readable storage medium, and when executed, it can include the processes described in the above method embodiments. The aforementioned storage medium includes various media capable of storing program code, such as ROM or random access memory (RAM), magnetic disks, or optical disks.

[0092] The steps of the methods or algorithms described in the embodiments of this application can be implemented in hardware or by a processor executing software instructions. The software instructions can consist of corresponding software modules, which can be stored in RAM, flash memory, ROM, EPROM, electrically erasable programmable read-only memory (EEPROM), registers, hard disk, portable hard disk, read-only optical disk (CD-ROM), or any other form of storage medium well known in the art. An exemplary storage medium is coupled to a processor, enabling the processor to read information from and write information to the storage medium. Of course, the storage medium can also be a component of the processor. The processor and storage medium can reside in an ASIC. Furthermore, the ASIC can reside in a terminal device or management device. Alternatively, the processor and storage medium can exist as discrete components in the terminal device or management device.

[0093] The modules / units included in the various devices and products described in the above embodiments can be software modules / units, hardware modules / units, or a combination of both. For example, for devices and products applied to or integrated into a chip, all modules / units can be implemented using hardware methods such as circuits, or at least some modules / units can be implemented using software programs that run on a processor integrated within the chip, while the remaining (if any) modules / units can be implemented using hardware methods such as circuits. For devices and products applied to or integrated into a chip module, all modules / units can be implemented using hardware methods such as circuits. Different modules / units can be located in the same component (e.g., chip, circuit module, etc.) or different components of the chip module, or at least some modules / units can be implemented using hardware methods such as circuits. The implementation is achieved through a software program that runs on the processor integrated within the chip module. The remaining modules / units (if any) can be implemented using hardware methods such as circuits. For various devices and products applied to or integrated into terminal equipment, each of their modules / units can be implemented using hardware methods such as circuits. Different modules / units can be located in the same component (e.g., chip, circuit module, etc.) or different components within the terminal equipment. Alternatively, at least some modules / units can be implemented through a software program that runs on the processor integrated within the terminal equipment, while the remaining modules / units (if any) can be implemented using hardware methods such as circuits.

[0094] The specific embodiments described above further illustrate the purpose, technical solution, and beneficial effects of the embodiments of this application. It should be understood that the above descriptions are merely specific embodiments of the embodiments of this application and are not intended to limit the protection scope of the embodiments of this application. Any modifications, equivalent substitutions, improvements, etc., made on the basis of the technical solutions of the embodiments of this application should be included within the protection scope of the embodiments of this application.

Claims

1. A method for intermittent detection of body fluid parameters, characterized in that, A main controller for a body fluid parameter detection system, the body fluid parameter detection system comprising: an infusion tubing, a pipetting module connected to the infusion tubing, and a detection module disposed on the infusion tubing; the pipetting module comprising an injection device, a fluid circuit switch, and a flushing device connected to the injection device; the injection device is connected to the fluid circuit switch and the injection device is connected to the infusion tubing; the method comprises: Control the liquid circuit switch to perform a closing action, and control the extraction and injection device to extract a preset first volume of target body fluid from the target user's reserved hole into the infusion tube; When the target body fluid in the infusion tube is detected to pass through the detection module, the detection module is controlled to detect the parameters of the target body fluid to obtain the target body fluid parameters; Control the liquid circuit switch to perform the opening action, and control the flushing device to inject a preset second volume of functional liquid into the infusion tube; When the detection module detects that the functional fluid in the infusion tube has passed through the detection module, the extraction and injection device is controlled to return the target body fluid to the target user.

2. The method as described in claim 1, characterized in that, The extraction and injection device includes a reservoir and a drive device connected to the reservoir. Controlling the extraction and injection device to extract a preset first volume of target bodily fluid from a pre-drilled hole in the target user into the infusion tube includes: Obtain the container attribute parameters of the driving device; The limiting position of the driving device is determined based on the first volume and the container attribute parameters. The drive device is controlled to drive the storage tank to generate negative pressure, so as to draw the target body fluid into the infusion tube; When the driving device moves to the limit position and the target body fluid passes through the position of the detection module of the infusion tube, the driving device is controlled to stop drawing the target body fluid so that the target body fluid passes through the position of the detection module of the infusion tube.

3. The method as described in claim 1 or 2, characterized in that, The detection module includes a photoelectric sensor, an electrochemical sensor, and a monitoring instrument connected to the photoelectric sensor and the electrochemical sensor; The photoelectric sensor includes a light-emitting device and a photodiode. The control module detects the parameters of the target body fluid to obtain the target body fluid parameters, including: When the target body fluid passes the sensing position of the photoelectric sensor, the light-emitting device is controlled to emit a first light signal to the photodiode; The photodiode acquires the second light signal generated by the target body fluid in response to the first light signal within the infusion tube. The optical characteristic parameters of the target body fluid are determined based on the second optical signal, and the optical characteristic parameters are sent to the monitoring instrument. The voltage signal of the target body fluid is detected by the electrochemical sensor; The electrochemical characteristic parameters of the target body fluid are determined based on the voltage signal, and the electrochemical characteristic parameters are sent to the monitoring instrument. The monitoring instrument generates the target body fluid parameters in response to the optical and electrochemical characteristic parameters.

4. The method as described in claim 3, characterized in that, The monitoring instrument generates the target body fluid parameters in response to the optical characteristic parameters and the electrochemical characteristic parameters, including: Determine multiple wavelength parameters among the optical characteristic parameters; Multiple first body fluid parameters corresponding to the multiple wavelength parameters are determined according to the preset mapping relationship between wavelength parameters and body fluid parameters; The accuracy parameters of the electrochemical sensor and the temperature parameters of the target body fluid are obtained; The temperature compensation parameters of the electrochemical sensor are determined based on the temperature parameters and the accuracy parameters. The electrochemical characteristic parameters are compensated based on the temperature compensation parameters to obtain multiple compensated electrochemical parameters; Multiple second body fluid parameters corresponding to the multiple compensating electrochemical parameters are determined based on the preset mapping relationship between electrochemical parameters and body fluid parameters; The target body fluid parameter is determined based on the plurality of first body fluid parameters and the plurality of second body fluid parameters.

5. The method as described in claim 1 or 2, characterized in that, The body fluid parameter detection system also includes an infusion bag connected to the fluid circuit switch, the infusion bag containing the functional fluid, and controlling the extraction and injection device to return the target body fluid to the target user includes: In response to the opening action of the liquid circuit switch, the extraction and injection device is controlled to extract the functional liquid from the infusion bag and into the flushing device; The flushing device responds to the injection action of the extraction and injection device by injecting the second volume of the functional liquid into the infusion tube; When the functional liquid passes through the position of the detection module, the injection action of the extraction and injection device is controlled to drive the target body fluid to flow back to the target user through the reserved hole.

6. The method as described in claim 1, characterized in that, The infusion tubing includes a first infusion tubing and a second infusion tubing. The first infusion tubing includes a detachable connector for connecting to the pipe connector of the pre-reserved hole of the target user. A sensor bracket and a control valve are provided on the first infusion tubing. The sensor bracket is used to fix the photoelectric sensor in the detection module. The control valve is used to control the fluid communication state of the first infusion tubing to open or close the body fluid flow path. The end of the second infusion tube furthest from the detection module is connected to the reservoir of the extraction and injection device, and the end of the second infusion tube closest to the detection module is connected to the extraction and injection device, so that the extraction and injection device can form a closed fluid path with the reserved hole through the detachable connection joint, thereby realizing the extraction, detection and reinjection of the target body fluid; a pressure sensor is provided between the flushing device and the detection module, and the pressure sensor is used to measure the blood pressure parameters of the target user, or, when the control valve is in the closed state, the pressure sensor detects the tubing pressure in the first infusion tube.

7. The method as described in claim 1, characterized in that, The functional liquid includes at least one of physiological saline or deionized water, and an anticoagulant; the anticoagulant is used to prevent clotting during blood measurement.

8. An intermittent detection device for body fluid parameters, characterized in that, An application is made in a body fluid parameter detection system, the system comprising: an infusion tubing, a pipetting module connected to the infusion tubing, and a detection module mounted on the infusion tubing. The pipetting module includes an injection device, a fluid circuit switch, and a flushing device connected to the injection device. The injection device is connected to the fluid circuit switch and to the infusion tubing. The intermittent detection device includes: The control unit is used to control the liquid circuit switch to perform a closing action, and to control the extraction and injection device to extract a preset first volume of target body fluid from the target user's reserved hole into the infusion tube; A monitoring unit is used to control the detection module to detect the parameters of the target body fluid when the target body fluid in the infusion tube passes through the detection module, and obtain the target body fluid parameters; The control unit is also used to control the liquid circuit switch to perform an opening action, and to control the flushing device to inject a preset second volume of functional liquid into the infusion tube; An execution unit is configured to control the extraction and injection device to return the target body fluid to the target user when the detection module is detected that the functional fluid in the infusion tube has passed through the detection module.

9. An intermittent detection device for body fluid parameters, characterized in that, include: Processor, memory, communication interface, and one or more programs; The one or more programs are stored in the memory and configured to be executed by the processor, the programs including instructions for performing the steps of the method as described in any one of claims 1-7.

10. An intermittent detection system for body fluid parameters, characterized in that, The intermittent detection system for body fluid parameters performs the method as described in any one of claims 1-7.

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