A separable infusion device based on impeller metering

Abstract

The application discloses a separable infusion device based on impeller metering applied to the technical field of medical devices. The device is characterized in that an induction impeller is arranged in the device box body. The drug liquid drives the induction impeller to rotate. Then, the photoelectric reflection inductor records the rotation times of the induction impeller through the light transmission window and combines the time to infer the rotation speed of the induction impeller. Finally, the flow and flow rate of the drug liquid are calculated, which is convenient for the patient to accurately measure and control the infusion flow rate. Compared with the traditional infusion monitoring method, the obtained infusion measurement and infusion flow rate data are more accurate. The measurement induction assembly adopts the combined clamp clamping device box body combination mode, which is convenient for the separable operation between the measurement induction assembly and the device box body, so that the measurement induction assembly can be repeatedly used, and the use cost is effectively reduced.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a detachable infusion device based on impeller metering. Background Technology

[0002] An infusion set is a medical device used to control and regulate the speed and flow rate of intravenous infusion. Traditional infusion methods involve infusing the entire bottle of medication, meaning the entire bottle is infused. However, some medications, such as mannitol, do not require full infusion during infusion therapy. To control the infusion volume, real-time monitoring of the infusion is necessary. For example, Chinese patent CN116173352B discloses an automatic infusion monitoring method and system based on weight monitoring, which calculates the infusion volume by weighing the change in the weight of the infusion bottle. Another example is Chinese patent CN221600870U, which discloses a flow-adjustable infusion device that uses a micro-pump for precise infusion control. Both of these methods of monitoring fluid flow rate and dosage have the following problems: the weighing equipment is bulky, easily affected by tubing tension, and the weighing data is susceptible to vibration interference, resulting in low data accuracy; the micro-pump has a complex structure and high operating costs. Summary of the Invention

[0003] The core of this invention lies in using a photoelectric reflector to monitor in real time the number of rotations of the sensing impeller driven by the liquid medicine, and then calculating the flow rate and velocity of the liquid medicine accurately through data calculation, thus solving the problems of inaccurate infusion metering and infusion flow rate monitoring and high monitoring equipment costs in the prior art.

[0004] To solve the above problems, the present invention adopts the following technical solution.

[0005] A separable infusion device based on impeller metering includes a device housing, with an inlet connector and an outlet connector fixedly connected to the top and bottom of the device housing, respectively. An induction impeller is rotatably connected inside the device housing, and a metering sensing component is provided on the outside of the device housing.

[0006] The metering sensing component includes a combination clamp and two clamping ends of the combination clamp, which are respectively fixedly connected to a sensing clamp and a power clamp. The sensing clamp and the power clamp contact the front and rear ends of the device housing, respectively. A photoelectric reflection sensor and a main control unit are fixedly connected inside the sensing clamp. The output end of the photoelectric reflection sensor is electrically connected to the main control unit. A light-transmitting window is opened at one end of the device housing. The photoelectric reflection sensor and the light-transmitting window are arranged colinearly. The main control unit includes a human-machine interface and an audible and visual alarm. The human-machine interface is located on the surface of the sensing clamp.

[0007] Furthermore, the induction impeller consists of a central shaft and multiple blades fixedly distributed around the central shaft. One of the blades has a reflective patch fixedly connected to its exterior. The reflective patch is made of aluminum-plated plastic film.

[0008] Preferably, both ends of the device housing are provided with connecting holes, and an elastic diaphragm is fixedly connected inside the connecting holes. The middle part of the elastic diaphragm is concave and extends into the device housing. The inner wall of the central axis of the elastic diaphragm is in rotatable contact with the central axis. When the elastic diaphragm deforms into the device housing, it squeezes and contacts the impeller.

[0009] Furthermore, the device housing is made of rigid plastic, while the elastic diaphragm and impeller are made of elastic silicone material.

[0010] Furthermore, both the sensing clamp and the power clamp have movable holes at the center of one end near the device housing. A protruding post is inserted into the movable hole, and a concave sleeve is fixedly connected to the outer wall of the central axis of the elastic diaphragm. The protruding post is inserted into the concave sleeve.

[0011] Furthermore, each of the two protruding pillars has an electromagnet module fixedly connected inside. The two electromagnet modules are attracted to each other by magnetic force after being energized, and the on / off terminals of the electromagnet modules are electrically connected to the main control unit.

[0012] Furthermore, an annular groove is provided on the inner wall of the bottom end of the movable hole, and a reset spring is fixedly connected inside the annular groove. One end of the protrusion extending into the movable hole is fixedly connected to the reset spring, and the reset spring is made of elastic rubber material.

[0013] Compared with the prior art, the advantages of this invention are:

[0014] (1) This invention sets up a sensing impeller in the device box. The drug liquid drives the sensing impeller to rotate. Then, the photoelectric reflection sensor records the number of rotations of the sensing impeller through the light-transmitting window and infers the speed of the sensing impeller by combining the time. Finally, the flow rate and velocity of the drug liquid are calculated, which makes it easier for patients to perform accurate infusion measurement and infusion flow rate control. Compared with the traditional infusion monitoring method, the obtained infusion measurement and infusion flow rate data are more accurate. In addition, the measurement sensing component adopts a combination clamp to hold the device box, which facilitates the separable operation between the measurement sensing component and the device box, thereby realizing the reuse of the measurement sensing component and effectively reducing the cost of use.

[0015] (2) When the flow rate and velocity of the liquid medicine are detected to be abnormal or the liquid medicine has reached the preset infusion volume, the main control unit controls the electromagnet module to be energized to generate magnetic force. Through the magnetic attraction, the convex column applies pressure to the elastic diaphragm inside the device box, causing the elastic diaphragm to deform and squeeze into contact with the impeller, so that the elastic diaphragm and the impeller are tightly sealed. At the same time, the impeller is deformed synchronously under the influence of pressure, and the impeller also closely contacts the inner wall of the device box, thereby realizing the sealing of the internal space of the device box by the induction impeller, effectively hindering the flow of the liquid medicine and stopping the infusion of the liquid medicine in time. Attached Figure Description

[0016] Figure 1 This is a three-dimensional structural diagram of the present invention;

[0017] Figure 2 This is a three-dimensional structural diagram of the device housing and metering sensing component of the present invention;

[0018] Figure 3 This is a three-dimensional structural diagram of the metering sensing component of the present invention;

[0019] Figure 4 This is a three-dimensional structural diagram of the sensing clamp block of the present invention;

[0020] Figure 5 This is a three-dimensional structural diagram of the device housing of the present invention in its split-body state;

[0021] Figure 6 This is a three-dimensional structural diagram of the induction impeller of the present invention;

[0022] Figure 7 This is a top sectional three-dimensional structural view of the housing of the device of the present invention;

[0023] Figure 8 This is a diagram illustrating the pressure change applied to the elastic diaphragm by the protruding post of the present invention.

[0024] Figure 9 This is an enlarged view of the three-dimensional cross-sectional structure of the movable hole of the present invention;

[0025] Figure 10 This is a demonstration diagram of the protruding post extending from the movable hole of the present invention.

[0026] Explanation of the labels in the diagram:

[0027] 1. Device housing, 101 liquid inlet connector, 102 liquid outlet connector, 2. Induction impeller, 201 central shaft, 202 impeller blade, 203 reflective patch, 3. Combination clamp, 301 induction clamp, 302 power clamp, 303 photoelectric reflector, 304 light-transmitting window, 305 human-machine interface, 4. Connecting hole, 401 elastic diaphragm, 402 movable hole, 403 protruding post, 404 concave sleeve, 405 electromagnet module, 406 annular groove, 407 reset spring. Detailed Implementation

[0028] The technical solutions will now be clearly and completely described with reference to the accompanying drawings in the embodiments of the present invention.

[0029] First implementation method:

[0030] Please see Figures 1 to 7A separable infusion device based on impeller metering includes a device housing 1. The top and bottom of the device housing 1 are respectively fixedly connected to an inlet connector 101 and an outlet connector 102. An infusion bottle is inserted through the inlet connector 101 and an infusion set is inserted through the outlet connector 102, so that the infusion device can be used in the daily infusion treatment process of patients.

[0031] An induction impeller 2 is rotatably connected inside the device housing 1. A metering induction assembly is located outside the device housing 1. The metering induction assembly includes a combined clamp 3 and two clamping ends of the combined clamp 3, with induction clamping blocks 301 and power clamping blocks 302 fixedly connected to them respectively. The induction clamping blocks 301 and power clamping blocks 302 contact the front and rear ends of the device housing 1 respectively. A photoelectric reflection sensor 303 and a main control unit are fixedly connected inside the induction clamping block 301. The output end of the photoelectric reflection sensor 303 is electrically connected to the main control unit. A light-transmitting window 304 is opened at one end of the device housing 1. The photoelectric reflection sensor 303 is collinear with the light-transmitting window 304. The photoelectric reflection sensor 303 includes an infrared emitting tube and a receiving tube. It records the number of rotations of the induction impeller 2 by detecting changes in reflected light. The liquid medicine drives the induction impeller 2 to rotate. The rotation speed of the induction impeller 2 is proportional to the flow rate of the liquid medicine. The flow rate of the liquid medicine can be calculated by counting the number of rotations. To accurately determine the patient's infusion dosage and flow rate, the sensing impeller 2 consists of a central shaft 201 and multiple blades 202 fixedly distributed around the central shaft 201. One of the blades 202 has a reflective patch 203 fixedly connected to its exterior. The reflective patch 203 is made of aluminized plastic film, which effectively enhances the reflectivity of the blade 202, facilitating the photoelectric reflection sensor 303 to accurately monitor the rotation data of the sensing impeller 2. The main control unit includes a human-machine interface 305 and an audible and visual alarm. The human-machine interface 305 is located on the surface of the sensing clamp 301 and includes a display screen and various operation buttons. The display screen shows the real-time flow rate, cumulative infusion volume, preset target volume, and running time. The operation buttons are used to set the preset alarm volume, turn the device on / off, and reset the infusion. When the patient's infusion condition is abnormal, the main control unit will sound an alarm through the audible and visual alarm. The main control unit and the audible and visual alarm are not shown in the attached drawings.

[0032] When a patient receives intravenous infusion therapy, the inlet connector 101 of the device housing 1 is connected to the infusion bottle, and the outlet connector 102 of the device housing 1 is connected to the infusion set. During routine intravenous infusion therapy, the medication enters the device housing 1 and drives the induction impeller 2 to rotate. The photoelectric reflector 303 records the number of rotations of the induction impeller 2 through the light-transmitting window 304, and combines this with the time to infer the rotation speed of the induction impeller 2. Finally, the flow rate and velocity of the medication are calculated, which facilitates precise infusion measurement and infusion flow rate control for the patient. This solves the problems of poor infusion accuracy caused by reliance on manual labor in traditional infusion methods, and high cost caused by reliance on high-precision infusion pumps.

[0033] Second implementation method:

[0034] Compared to the first embodiment, the main addition is an elastic diaphragm 401, the specific addition structure is as follows, and the rest of the structure is the same as the first embodiment.

[0035] Please see Figures 7 to 9 Both ends of the device housing 1 have connecting holes 4. An elastic diaphragm 401 is fixedly connected inside the connecting holes 4. The middle part of the elastic diaphragm 401 is concave and extends into the device housing 1. The inner wall of the central axis of the elastic diaphragm 401 is in rotatable contact with the central axis 201. When the elastic diaphragm 401 is subjected to pressure into the device housing 1, the elastic diaphragm 401 deforms and presses against the impeller 202, fixing the sensing impeller 2. The device housing 1 is made of rigid plastic, and the central axis 201 is hollow. The elastic diaphragm 401, the central axis 201, and the impeller 202 are all made of elastic silicone material. When the central axis 201 is subjected to pressure from the elastic diaphragm 401, the central axis 201, and the impeller 202 are all made of elastic silicone material. When the disc 401 is squeezed into contact, the central shaft 201 is flattened. The flattened central shaft 201 pushes the impeller 202 outward, so that the impeller 202 is in close contact with the elastic diaphragm 401 and the inner wall of the device box 1. This achieves the sealing of the internal space of the device box 1 by the sensing impeller 2, effectively hindering the flow of the liquid medicine and stopping the infusion of the liquid medicine in time. The device box 1, made of hard plastic, can effectively resist the clamping force of the sensing clamp 301 and the power clamp 302, effectively preventing the device box 1 from deforming, and providing a relatively stable environment for the elastic diaphragm 401, effectively preventing the sensing clamp 301 and the power clamp 302 from contacting the elastic diaphragm 401.

[0036] During the patient's infusion process, if the flow rate and velocity of the medication are abnormal, or if the medication has reached the preset infusion volume, pressure is applied to the elastic diaphragm 401 inside the device housing 1. This causes the elastic diaphragm 401 to deform and press against the central shaft 201. The central shaft 201 is flattened and deformed, pushing the elastic diaphragm 401 to tightly seal against the impeller 202 and the inner wall of the device housing 1. This achieves a tight fit between the impeller 202 and the inner wall of the device housing 1, thereby causing the sensing impeller 2 to seal the internal space of the device housing 1, effectively hindering the flow of the medication and stopping the infusion in time.

[0037] Please see Figure 9 and Figure 10Both the induction clamp 301 and the power clamp 302 have movable holes 402 at the center of their ends near the device housing 1. A protrusion 403 is inserted into the movable hole 402. A concave sleeve 404 is fixedly connected to the outer wall of the central axis of the elastic diaphragm 401. The protrusion 403 and the concave sleeve 404 are inserted into each other. This connection effectively improves the stability of the connection between the induction clamp 301 and the power clamp 302 and the device housing 1. Electromagnetic modules 405 are fixedly connected inside each of the two protrusions 403. The two electromagnet modules 405 attract each other magnetically when energized. Furthermore, the on / off terminals of the electromagnet module 405 are electrically connected to the main control unit. When the two electromagnet modules 405 are energized, they generate a magnetic force that attracts each other, causing the protrusion 403 to apply pressure to the elastic diaphragm 401 into the device housing 1. An annular groove 406 is provided on the inner wall of the bottom end of the movable hole 402. A reset spring 407 is fixedly connected inside the annular groove 406. One end of the protrusion 403 that extends into the movable hole 402 is fixedly connected to the reset spring 407. The reset spring 407 is made of elastic rubber material. The elasticity of the reset spring 407 is used to realize the automatic return of the protrusion 403 to the inside of the movable hole 402.

[0038] When it is necessary to stop the infusion of the medicine, the main control unit controls the electromagnet module 405 to be energized to generate magnetic force. The two electromagnet modules 405, which are magnetically attracted to each other, cause the protrusion 403 to apply pressure to the elastic diaphragm 401 into the device housing 1. When it is necessary to resume the infusion of the medicine, the main control unit controls the electromagnet module 405 to be de-energized. The magnetic force generated by the electromagnet module 405 disappears, and the elastic force of the reset spring 407 is used to realize the automatic restoration of the position of the protrusion 403, thus ending the pressure applied to the elastic diaphragm 401.

[0039] The above description is merely a preferred embodiment of the present invention; it encompasses all the protection scope of the present invention. Any equivalent substitutions or modifications made by those skilled in the art within the technical scope disclosed in the present invention, based on the technical solutions and improved concepts of the present invention, should be covered within the protection scope of the present invention.

Claims

1. A separable infusion device based on impeller metering, comprising a device housing (1), wherein an inlet connector (101) and an outlet connector (102) are fixedly connected to the top and bottom of the device housing (1), respectively, characterized in that: The device housing (1) is rotatably connected to an induction impeller (2), and the device housing (1) is provided with a metering induction component on its exterior. The metering sensing component includes a combination clamp (3) and two clamping ends of the combination clamp (3) fixedly connected to a sensing clamp (301) and a power clamp (302). The sensing clamp (301) and the power clamp (302) respectively contact the front and rear ends of the device box (1). The inside of the sensing clamp (301) is fixedly connected to a photoelectric reflection sensor (303) and a main control unit. The output end of the photoelectric reflection sensor (303) is electrically connected to the main control unit. One end of the device box (1) is provided with a light-transmitting window (304). The photoelectric reflection sensor (303) and the light-transmitting window (304) are arranged in the same line. The main control unit includes a human-machine interface (305) and an audible and visual alarm. The human-machine interface (305) is disposed on the surface of the sensing clamp (301).

2. The detachable infusion device based on impeller metering according to claim 1, characterized in that: The induction impeller (2) consists of a central shaft (201) and multiple blades (202) fixedly distributed around the central shaft (201). One of the blades (202) is fixedly connected to a reflective patch (203) made of aluminum-plated plastic film.

3. A separable infusion device based on impeller metering according to claim 2, characterized in that: Both ends of the device box (1) are provided with connecting holes (4). An elastic diaphragm (401) is fixedly connected inside the connecting hole (4). The middle part of the elastic diaphragm (401) is concave and extends into the device box (1). The inner wall of the central axis of the elastic diaphragm (401) is in rotational contact with the central axis body (201). When the elastic diaphragm (401) deforms into the device box (1), it squeezes and contacts the wheel blade (201).

4. A separable infusion device based on impeller metering according to claim 3, characterized in that: The device housing (1) is made of rigid plastic, the central shaft (201) is hollow, and the elastic diaphragm (401), the central shaft (201) and the impeller (201) are all made of elastic silicone material.

5. A separable infusion device based on impeller metering according to claim 3, characterized in that: The sensing clamp (301) and the power clamp (302) are both provided with a movable hole (402) at the middle of one end of the device box (1). A protruding post (403) is inserted into the movable hole (402). A concave sleeve (404) is fixedly connected to the outer wall of the central axis of the elastic diaphragm (401). The protruding post (403) is inserted into the concave sleeve (404).

6. A separable infusion device based on impeller metering according to claim 5, characterized in that: An electromagnet module (405) is fixedly connected inside each of the two protrusions (403). The two electromagnet modules (405) are attracted to each other by magnetic force after being energized, and the on and off terminals of the electromagnet modules (405) are electrically connected to the main control unit.

7. A separable infusion device based on impeller metering according to claim 5, characterized in that: An annular groove (406) is provided on the inner wall of the bottom end of the movable hole (402). A reset spring (407) is fixedly connected inside the annular groove (406). One end of the protrusion (403) extending into the movable hole (402) is fixedly connected to the reset spring (407). The reset spring (407) is made of elastic rubber material.

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