WO2023045592A1 - 微剂量输出结构、微剂量分泌泵及胰岛素泵 - Google Patents

微剂量输出结构、微剂量分泌泵及胰岛素泵 Download PDF

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WO2023045592A1
WO2023045592A1 PCT/CN2022/110490 CN2022110490W WO2023045592A1 WO 2023045592 A1 WO2023045592 A1 WO 2023045592A1 CN 2022110490 W CN2022110490 W CN 2022110490W WO 2023045592 A1 WO2023045592 A1 WO 2023045592A1
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micro
dose
drive shaft
secretion
movable ring
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PCT/CN2022/110490
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English (en)
French (fr)
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卓力
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时新(上海)产品设计有限公司
上海旭润医学科技有限责任公司
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Publication of WO2023045592A1 publication Critical patent/WO2023045592A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
    • A61M5/14526—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons the piston being actuated by fluid pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16804—Flow controllers

Definitions

  • the invention relates to the field of injection equipment, in particular to a micro-dosage output structure, a micro-dosage secretion pump and an insulin pump.
  • An insulin pump consists of a pump, a small syringe, and an infusion tube connected to it.
  • the small syringe can hold up to 3ml of insulin.
  • the guide needle at the front end of the connected infusion tube is inserted into the patient's subcutaneous (normally the abdominal wall) with a needle injector, and the screw motor of the insulin pump is driven by a battery. Push the plunger of the small syringe to infuse insulin into the body.
  • the basic purpose of the insulin pump is to simulate the secretion of the human pancreas for infusion, and continuously inject insulin into the subcutaneous of the user according to the dose required by the human body, so as to keep the blood sugar stable throughout the day, so as to achieve the purpose of controlling diabetes.
  • Patent document CN110721364A discloses a quantitative and timing insulin pump, which can be fixed on the patient's body and can inject a fixed amount of insulin at a fixed time to automatically inject insulin. It can be seen that the medium similar to insulin needs to be infused strictly according to the timing and quantitative requirements, otherwise it will easily endanger the life and health of the user.
  • This patent document uses MCU to control the opening and closing time of the air pump, so as to achieve the purpose of timing and quantification.
  • Insulin injection usually needs to be injected continuously for several days. If MCU control is used, it requires a large power consumption. Therefore, it is necessary to equip the insulin pump with a battery with sufficient power, which increases the overall volume and weight of the device and brings a burden to wearing. . Therefore, there is an urgent need for a low-power and reliable insulin pump.
  • the overall cost of the equipment is high due to the use of MCU control. Therefore, the method of replacing the injection parts for repeated use is adopted.
  • the internal liquid residue is easy to breed bacteria, and there are hygiene problems.
  • the object of the present invention is to provide a micro-dosage output structure, a micro-dosage secretion pump and an insulin pump.
  • a micro-dose output structure provided according to the present invention includes: a micro-dose secretion component 100, a micro-dose control component 200;
  • the micro-dose secretion assembly 100 drives the screw structure screwed in the nut structure to advance axially by rotating the nut structure, thereby pushing out the required output medium;
  • the micro dose control assembly 200 is connected with the nut structure to dynamically limit the rotation angle of the nut structure.
  • the micro-dosage secretion assembly 100 includes: a power element 101, a drive shaft 102, a turbine 103, a worm 104, a nut column 109, a screw piston 110, a locking structure and a cylinder 112;
  • the power element 101 is connected to the drive shaft 102 to drive the drive shaft 102 to rotate axially;
  • the worm wheel 103 is circumferentially arranged on the outer surface of the drive shaft 102 and meshes with the worm 104, the worm 104 is provided with a gear 105, and the gear 105 meshes with the micro-dose control assembly 200;
  • the movable ring 108 is slidably sleeved on the outside of the drive shaft 102, and the elastic element 107 is connected between the movable ring 108 and the turbine 103;
  • the drive shaft 102 is a hollow structure, the nut column 109 is slidably connected in the drive shaft 102, the screw piston 110 includes a rod part and a piston part, and the rod part is threaded in the nut column 109, The piston part is located in the cylinder body 112;
  • the locking structure is disposed on the driving shaft 102 and can fix or unlock the driving shaft 102 and the nut column 109 to each other.
  • the locking structure includes: an annular lock pin 106, an elastic element 107 and a movable ring 108;
  • the annular lock pin 106 is sleeved on the movable ring 108, the movable ring 108 is sleeved on the drive shaft 102, and the elastic element 107 is connected between the movable ring 108 and the turbine 103 , the drive shaft 102 is provided with a through hole;
  • the movable ring 108 In the initial state, the movable ring 108 is limited in the first position by the limiting structure on the drive shaft 102, the elastic element 107 is in a compressed state, and the rotation of the drive shaft 102 during the output process makes the The movable ring 108 breaks away from the limiting structure, and the elastic element 107 pushes the movable ring 108 forward.
  • the end of the circular locking pin 106 is inserted through the through hole under its own elastic force The nut column 109 .
  • the microdose secretion assembly 100 includes: a sliding bar 113;
  • the slide rod 113 is connected to the nut column 109, and moves synchronously with the nut column 109.
  • a partition is arranged on the movement stroke of the slide rod 113, and the partition is inserted in the micro-dose output structure. in the power supply circuit.
  • a groove is formed on the side wall of the piston part in the circumferential direction, and a sealing element is arranged in the groove, and the sealing element is in contact with the inner wall of the cylinder body 112 .
  • the power element 101 includes a motor or a spring.
  • the micro dose control assembly 200 includes: a motor 201 and a gearbox 202;
  • the output end of the motor 201 is in transmission connection with the nut structure of the micro-dosage secretion assembly 100 through the gear box 202 .
  • the gearbox 202 includes a reduction gearbox.
  • a micro-dosage secretion pump provided according to the present invention includes the micro-dosage output structure.
  • An insulin pump provided according to the present invention includes the micro-dosage output structure.
  • the present invention has the following beneficial effects:
  • the product can achieve low power consumption, which is suitable for situations where the product needs to work continuously and for a long time, such as insulin injection.
  • the scheme has simple structure, low cost and is suitable for one-time use.
  • Fig. 1 is the overall structure schematic diagram of the present invention
  • Figure 2 is a perspective view of the microdose secretion assembly of the present invention
  • Figure 3 is a cross-sectional view of the microdose secretion assembly of the present invention in its initial state
  • Fig. 4 is a cross-sectional view of the microdose secretion assembly of the present invention during liquid injection
  • Fig. 5 is a cross-sectional view of the microdose secretion assembly of the present invention after liquid injection is completed;
  • Fig. 6 is a cross-sectional view of the inventive microdose secretion assembly during output.
  • the present invention provides a micro-dose output structure, including: a micro-dose secretion component 100 and a micro-dose control component 200 .
  • the micro-dosage secretion assembly 100 drives the screw structure screwed in the nut structure to advance axially by rotating the nut structure, so as to push out the required output medium.
  • the advantage of this output method is that the amount of the output medium is accurately and controllable, and will not There is a large deviation.
  • the micro-dose control component 200 is connected to the nut structure to dynamically limit the nut. The rotation angle of the structure.
  • the microdose secretion assembly 100 includes: a power element 101 , a drive shaft 102 , a turbine 103 , a worm 104 , a gear 105 , a nut column 109 , a screw piston 110 , a sealing element 111 , a locking structure and a cylinder 112 .
  • the power element 101 is connected to the drive shaft 102 to drive the drive shaft 102 to rotate axially.
  • the worm wheel 103 is circumferentially arranged on the outer surface of the drive shaft 102 and meshes with the worm 104 .
  • the worm 104 is provided with a gear 105 , and the gear 105 meshes with the micro dose control assembly 200 .
  • the movable ring 108 is slidably sleeved on the outside of the drive shaft 102 , and the elastic element 107 is connected between the movable ring 108 and the turbine 103 .
  • the drive shaft 102 is a hollow structure
  • the nut column 109 is slidably connected in the drive shaft 102
  • the screw piston 110 includes a rod and a piston
  • the rod is threaded in the nut column 109
  • the piston is located in the cylinder 112 .
  • the locking structure is disposed on the driving shaft 102 and can fix or unlock the driving shaft 102 and the nut column 109 to each other.
  • a groove is formed on the side wall of the piston part in the circumferential direction, and a sealing element is arranged in the groove, and the sealing element is in contact with the inner wall of the cylinder 112 . Thereby achieving sealing.
  • the locking structure includes: an annular locking pin 106 , an elastic element 107 and a movable ring 108 .
  • the annular lock pin 106 is sleeved on the movable ring 108, and the movable ring 108 is sleeved on the driving shaft 102, the elastic element 107 is connected between the movable ring 108 and the turbine 103, and the driving shaft 102 is provided with a through hole.
  • the movable ring 108 in an initial state, the movable ring 108 is limited at the first position by the limiting structure on the drive shaft 102 , and the elastic element 107 is in a compressed state.
  • the movable ring 108 is separated from the limit structure by the rotation of the drive shaft 102, and the elastic element 107 pushes the movable ring 108 forward. Insert the nut column 109 through the through hole under the action of its own elastic force. At this time, continuing to rotate the drive shaft 102 will cause the nut column 109 to rotate synchronously, thereby pushing the screw piston 110 out.
  • a slide bar 113 is also designed.
  • the slide bar 113 is connected to the nut column 109. During the liquid injection process, it moves synchronously with the nut column 109.
  • a partition is arranged on the movement stroke of the slide bar 113. It is arranged in the power supply circuit of the micro-dosage output structure.
  • the microdosage control assembly 200 includes: a motor 201 and a gear box 202 .
  • the output end of the motor 201 is drivingly connected with the nut structure of the micro-dose secretion assembly 100 through the gear box 202 .
  • the gear box 202 adopts a gear box with a high reduction ratio.
  • the power element 101 includes a motor or a spring, and in order to reduce energy consumption, this embodiment uses a spring as an example for illustration.
  • the elastic element 107 is in a pre-tightened state, the nut column 109 is screwed to the position close to the piston part of the screw piston 110, the piston part of the screw piston 110 is located at the liquid inlet and outlet of the cylinder body 112, and the cylinder body 112 is emptied gas inside.
  • the power element 101 can be used to drive the drive shaft 102 to rotate.
  • the turbine 103 cannot drive the worm 104
  • the drive shaft 102 cannot rotate at this time, and the power of the mainspring is retained.
  • the motor 201 drives the gearbox 202 to rotate, thereby rotating the worm 104.
  • the turbine 103 has a corresponding rotation space, and now the drive shaft 102 can be rotated by a corresponding angle under the power of the power element 101 . So when the worm 104 turns, it unlocks the worm gear 103, causing the drive shaft 102 to rotate.
  • the micro-dose output structure provided by the present invention can realize the reliable output of micro-dose, and can be applied to various micro-dose secretion pumps, such as insulin pumps.

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  • Health & Medical Sciences (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Vascular Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Veterinary Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Public Health (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
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  • Infusion, Injection, And Reservoir Apparatuses (AREA)

Abstract

一种微剂量输出结构、微剂量分泌泵及胰岛素泵，包括：微剂量分泌组件（100）、微剂量控制组件（200）；微剂量分泌组件（100）通过旋转螺母结构的方式驱动螺接在螺母结构内的螺杆结构轴向推进，从而推出所需输出的介质；微剂量控制组件（200）与螺母结构连接，动态限制螺母结构的旋转角度。通过采用马达（201）和齿轮箱（202）再配合驱动元件的结构，从而可以使产品实现低功耗，适用于产品需要持续工作且时间较长的情况。

Description

微剂量输出结构、微剂量分泌泵及胰岛素泵 技术领域
本发明涉及注射设备领域，具体地，涉及一种微剂量输出结构、微剂量分泌泵及胰岛素泵。
背景技术
胰岛素泵由泵、小注射器和与之相连的输液管组成。小注射器最多可以容纳3毫升的胰岛素，注射器装入泵中后，将相连的输液管前端的引导针用注针器扎入患者的皮下(常规为腹壁)，再由电池驱动胰岛素泵的螺旋马达推动小注射器的活塞，将胰岛素输注到体内。胰岛素泵的基本用途是模拟人体胰腺的分泌进行输注，按照人体需要的剂量将胰岛素持续地推注到使用者的皮下，保持全天血糖稳定，以达到控制糖尿病的目的。
专利文献CN110721364A公开了一种定量定时给药胰岛素泵，能固定在患者身体上，能在固定时间注射固定量的胰岛素自动注射胰岛素。可见类似胰岛素的介质需要严格的按照定时、定量的要求进行输注，否则容易危害使用者的生命和健康。该专利文献采用MCU来控制气泵的启闭时间，从而来实现定时、定量的目的。
然而，上述专利所公开的技术方案存在较多的缺陷：
1、注射胰岛素通常需要持续多天注射，若采用MCU控制则需要较大的功耗，因此需要在胰岛素泵上配备足够电量的电池，增加了设备整体的体积和重量，给穿戴带来了负担。因此亟需一种低功耗且可靠的胰岛素泵。
2、采用MCU控制导致设备整体成本高傲，因此采用了更换注射件来反复使用的方式，内部液体残留容易滋生细菌，存在卫生问题。
发明内容
针对现有技术中的缺陷，本发明的目的是提供一种微剂量输出结构、微剂量分泌泵及胰岛素泵。
根据本发明提供的一种微剂量输出结构，包括：微剂量分泌组件100、微剂量控制组件200；
所述微剂量分泌组件100通过旋转螺母结构的方式驱动螺接在所述螺母结构内的螺杆结构轴向推进，从而推出所需输出的介质；
所述微剂量控制组件200与所述螺母结构连接，动态限制所述螺母结构的旋转角度。
优选地，所述微剂量分泌组件100包括：动力元件101、驱动轴102、涡轮103、蜗杆104、螺母柱109、螺杆活塞110、锁止结构和缸体112；
所述动力元件101连接所述驱动轴102，驱动所述驱动轴102轴向旋转；
所述涡轮103周向设置于所述驱动轴102的外表面，并与所述蜗杆104啮合，所述蜗杆104上设置有齿轮105，所述齿轮105与所述微剂量控制组件200啮合；
所述活动环108滑动套设在所述驱动轴102的外侧，所述弹性元件107连接在所述活动环108与所述涡轮103之间；
所述驱动轴102为中空结构，所述螺母柱109滑动连接在所述驱动轴102内，所述螺杆活塞110包括杆部和活塞部，所述杆部螺纹连接在所述螺母柱109内，所述活塞部位于所述缸体112内；
所述锁止结构设置于所述驱动轴102上，能够将所述驱动轴102和所述螺母柱109相互固定或解锁。
优选地，所述锁止结构包括：环形锁针106、弹性元件107和活动环108；
所述环形锁针106套设在所述活动环108上，所述活动环108套设在所述驱动轴102上，所述弹性元件107连接在所述活动环108和所述涡轮103之间，所述驱动轴102开设有通孔；
在初始状态下，所述活动环108被所述驱动轴102上的限位结构限位在第一位置，所述弹性元件107呈压缩状态，输出过程中通过所述驱动轴102的旋转，使所述活动环108脱离所述限位结构，所述弹性元件107推动所述活动环108前进，在前进过程中，所述环形锁针106的端部在自身弹力作用下通过所述通孔插入所述螺母柱109。
优选地，所述微剂量分泌组件100包括：滑杆113；
所述滑杆113连接所述螺母柱109，随所述螺母柱109同步运动，在所述滑杆113的运动行程上设置有隔板，所述隔板插设在所述微剂量输出结构的供电回路中。
优选地，所述活塞部的侧壁周向开设有凹槽，所述凹槽内设置有密封元件，所述密封元件与所述缸体112的内壁接触。
优选地，所述动力元件101包括马达或发条。
优选地，所述微剂量控制组件200包括：马达201和齿轮箱202；
所述马达201的输出端通过所述齿轮箱202与所述微剂量分泌组件100的螺母结构传动连接。
优选地，所述齿轮箱202包括减速齿轮箱。
根据本发明提供的一种微剂量分泌泵，包括所述的微剂量输出结构。
根据本发明提供的一种胰岛素泵，包括所述的微剂量输出结构。
与现有技术相比，本发明具有如下的有益效果：
通过采用马达和齿轮箱再配合驱动元件的结构，从而可以使产品实现低功耗，适用于产品需要持续工作且时间较长的情况，比如注射胰岛素。同时本方案结构简单，成本低廉，适合一次性使用。
通过采用锁止结构解决了用户可以加注任意容量的液体而不影响产品正常使用的问题，避免缸体内必须加入指定大小的体积之后才能工作的缺陷。
通过在加液过程中，滑杆触发电源电路的方式，解决了产品长时间存放过程中耗电的问题。
附图说明
通过阅读参照以下附图对非限制性实施例所作的详细描述，本发明的其它特征、目的和优点将会变得更明显：
图1为本发明的整体结构示意图；
图2为本发明微剂量分泌组件的立体图；
图3为本发明微剂量分泌组件在初始状态的剖视图；
图4为本发明微剂量分泌组件在注液过程中的剖视图；
图5为本发明微剂量分泌组件在注液完成后的剖视图；
图6为发明微剂量分泌组件在输出过程中的剖视图。
具体实施方式
下面结合具体实施例对本发明进行详细说明。以下实施例将有助于本领域的技术人员进一步理解本发明，但不以任何形式限制本发明。应当指出的是，对本领域的普通技术人员来说，在不脱离本发明构思的前提下，还可以做出若干变化和改进。这些都属于本发明的保护范围。
如图1所示，本发明提供一种微剂量输出结构，包括：微剂量分泌组件100、微剂量控制组件200。微剂量分泌组件100通过旋转螺母结构的方式驱动螺接在螺母结构内的螺杆结构轴向推进，从而推出所需输出的介质，这样的输出方式的优势在于输出介质的量精确可控，不会出现较大的偏差。在此基础上，由于胰岛素泵等应用场景需要微剂量分泌组件100连续缓慢工作，不能出现螺杆结构快速旋转导致介质注入过快的问题，因此通过微剂量控制组件200与螺母结构连接，动态限制螺母结构的旋转角度。
结合图2所示，微剂量分泌组件100包括：动力元件101、驱动轴102、涡轮103、蜗杆104、齿轮105、螺母柱109、螺杆活塞110、密封元件111、锁止结构和缸体112。动力元件101连接驱动轴102，驱动驱动轴102轴向旋转。涡轮103周向设置于驱动轴102的外表面，并与蜗杆104啮合，蜗杆104上设置有齿轮105，齿轮105与微剂量控制组件200啮合。活动环108滑动套设在驱动轴102的外侧，弹性元件107连接在活动环108与涡轮103之间。驱动轴102为中空结构，螺母柱109滑动连接在驱动轴102内，螺杆活塞110包括杆部和活塞部，杆部螺纹连接在螺母柱109内，活塞部位于缸体112内。锁止结构设置于驱动轴102上，能够将驱动轴102和螺母柱109相互固定或解锁。
活塞部的侧壁周向开设有凹槽，凹槽内设置有密封元件，密封元件与缸体112的内壁接触。从而实现密封。
在本实施例中，锁止结构包括：环形锁针106、弹性元件107和活动环108。环形锁针106套设在活动环108上，活动环108套设在驱动轴102上，弹性元件107连接在活动环108和涡轮103之间，驱动轴102开设有通孔。如图3所示，在初始状态下，活动环108被驱动轴102上的限位结构限位在第一位置，弹性元件107呈压缩状态。如图5和图6所示，输出过程中，通过驱动轴102的旋转，使活动环108脱离限位结构，弹性元件107推动活动环108前进，在前进过程中，环形锁针106的端部在自身弹力作用下通过通孔插入螺母柱109。此时继续旋转驱动轴102就会使螺母柱109同步旋转，从而将螺杆活塞110推出。
在本实施例中，还设计有滑杆113，滑杆113连接螺母柱109，在注液过程中，随螺母柱109同步运动，在滑杆113的运动行程上设置有隔板，隔板插设在微剂量输出结构的供电回路中。
如图1所示，微剂量控制组件200包括：马达201和齿轮箱202。马达201的输出端通过齿轮箱202与微剂量分泌组件100的螺母结构传动连接。齿轮箱202采用高减速比齿轮箱。
在本发明中，动力元件101包括马达或发条，为了降低能耗，本实施例以发条为例进行说明。
初始状态：
如图3所示，弹性元件107处于预紧状态，螺母柱109旋拧至螺杆活塞110的贴近活塞部位置，螺杆活塞110的活塞部位于缸体112的液体进出口处，排空缸体112内的气体。
注液状态：
如图4，当液体从液体进出口处注入到缸体112内部时，其注入的液体在压力的作用下推动螺杆活塞110连同螺母柱109向后推移。在加注液体的容量达到缸体容量一时，螺杆活塞110上的滑杆113移除隔板，此时产品电源连通并开机(此处结构未图示)，此设计的目的在于无需强制用户必 须注入定量的液体才能使用产品，因为此产品可实现一次性，避免用户因注入的液体过少从而不能充分的利用产品。另一方面可以避免长时间待机导致电量流失。如图5所示，当加注液体的容量达到缸体容量值最大时，此时螺杆活塞110上的滑杆113与控制板上的簧片接触，产品会发出报警提示，同时停止注药。
输出状态(注射)：
注液完成后，即可利用动力元件101驱动驱动轴102旋转，然而由于涡轮103无法驱动蜗杆104，此时驱动轴102也无法旋转，发条的动力得以保留。然后，马达201驱动齿轮箱202转动，从而转动蜗杆104，转动蜗杆104后，涡轮103便有了相应的转动空间，此时即可在动力元件101的动力作用下转动驱动轴102旋转相应的角度。所以当蜗杆104转动时，会解锁涡轮103，从而促使驱动轴102旋转。当驱动轴102旋转一定角度时，活动环108脱离壳体的限制，在弹性元件107的作用下，向前推移，同时活动环108上的环形锁针106在推移的过程中刺入螺母柱109中，从而限制螺母柱109轴向移动。如图6所示，在螺母柱109轴向位移被限制后，继续转动驱动轴102时,螺母柱109将随驱动轴102原地转动，从而促使螺杆活塞110直线推进，从而推出缸体112内部液体。
本发明提供的微剂量输出结构可以实现微剂量的可靠输出，可以适用于各种微剂量分泌泵中，例如胰岛素泵。
在本申请的描述中，需要理解的是，术语“上”、“下”、“前”、“后”、“左”、“右”、“竖直”、“水平”、“顶”、“底”、“内”、“外”等指示的方位或位置关系为基于附图所示的方位或位置关系，仅是为了便于描述本申请和简化描述，而不是指示或暗示所指的装置或元件必须具有特定的方位、以特定的方位构造和操作，因此不能理解为对本申请的限制。
以上对本发明的具体实施例进行了描述。需要理解的是，本发明并不局限于上述特定实施方式，本领域技术人员可以在权利要求的范围内做出各种变化或修改，这并不影响本发明的实质内容。在不冲突的情况下，本申请的实施例和实施例中的特征可以任意相互组合。

Claims (10)

  1. 一种微剂量输出结构，其特征在于，包括：微剂量分泌组件(100)、微剂量控制组件(200)；
    所述微剂量分泌组件(100)通过旋转螺母结构的方式驱动螺接在所述螺母结构内的螺杆结构轴向推进，从而推出所需输出的介质；
    所述微剂量控制组件(200)与所述螺母结构连接，动态限制所述螺母结构的旋转角度；
    所述微剂量分泌组件(100)包括：动力元件(101)、驱动轴(102)、涡轮(103)和蜗杆(104)；
    所述动力元件(101)连接所述驱动轴(102)，驱动所述驱动轴(102)轴向旋转；
    所述涡轮(103)周向设置于所述驱动轴(102)的外表面，并与所述蜗杆(104)啮合，所述蜗杆(104)与所述微剂量控制组件(200)啮合。
  2. 根据权利要求1所述的微剂量输出结构，其特征在于，所述微剂量分泌组件(100)还包括：弹性元件(107)、活动环(108)、螺母柱(109)、螺杆活塞(110)、锁止结构和缸体(112)；
    所述蜗杆(104)上设置有齿轮(105)，所述齿轮(105)与所述微剂量控制组件(200)啮合；
    所述活动环(108)滑动套设在所述驱动轴(102)的外侧，所述弹性元件(107)连接在所述活动环(108)与所述涡轮(103)之间；
    所述驱动轴(102)为中空结构，所述螺母柱(109)滑动连接在所述驱动轴(102)内，所述螺杆活塞(110)包括杆部和活塞部，所述杆部螺纹连接在所述螺母柱(109)内，所述活塞部位于所述缸体(112)内；
    所述锁止结构设置于所述驱动轴(102)上，能够将所述驱动轴(102)和所述螺母柱(109)相互固定或解锁。
  3. 根据权利要求2所述的微剂量输出结构，其特征在于，所述锁止结构包括：环形锁针(106)、弹性元件(107)和活动环(108)；
    所述环形锁针(106)套设在所述活动环(108)上，所述活动环(108) 套设在所述驱动轴(102)上，所述弹性元件(107)连接在所述活动环(108)和所述涡轮(103)之间，所述驱动轴(102)开设有通孔；
    在初始状态下，所述活动环(108)被所述驱动轴(102)上的限位结构限位在第一位置，所述弹性元件(107)呈压缩状态，输出过程中通过所述驱动轴(102)的旋转，使所述活动环(108)脱离所述限位结构，所述弹性元件(107)推动所述活动环(108)前进，在前进过程中，所述环形锁针(106)的端部在自身弹力作用下通过所述通孔插入所述螺母柱(109)。
  4. 根据权利要求2所述的微剂量输出结构，其特征在于，所述微剂量分泌组件(100)包括：滑杆(113)；
    所述滑杆(113)连接所述螺母柱(109)，随所述螺母柱(109)同步运动，在所述滑杆(113)的运动行程上设置有隔板，所述隔板插设在所述微剂量输出结构的供电回路中。
  5. 根据权利要求2所述的微剂量输出结构，其特征在于，所述活塞部的侧壁周向开设有凹槽，所述凹槽内设置有密封元件，所述密封元件与所述缸体(112)的内壁接触。
  6. 根据权利要求2所述的微剂量输出结构，其特征在于，所述动力元件(101)包括马达或发条。
  7. 根据权利要求1所述的微剂量输出结构，其特征在于，所述微剂量控制组件(200)包括：马达(201)和齿轮箱(202)；
    所述马达(201)的输出端通过所述齿轮箱(202)与所述微剂量分泌组件(100)的螺母结构传动连接。
  8. 根据权利要求7所述的微剂量输出结构，其特征在于，所述齿轮箱(202)包括减速齿轮箱。
  9. 一种微剂量分泌泵，其特征在于，包括权利要求1至8任一项所述的微剂量输出结构。
  10. 一种胰岛素泵，其特征在于，包括权利要求1至8任一项所述的微剂量 输出结构。
PCT/CN2022/110490 2021-09-27 2022-08-05 微剂量输出结构、微剂量分泌泵及胰岛素泵 WO2023045592A1 (zh)

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