WO2022105466A1 - 多段式气体致动供药装置及方法 - Google Patents

多段式气体致动供药装置及方法 Download PDF

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Publication number
WO2022105466A1
WO2022105466A1 PCT/CN2021/122571 CN2021122571W WO2022105466A1 WO 2022105466 A1 WO2022105466 A1 WO 2022105466A1 CN 2021122571 W CN2021122571 W CN 2021122571W WO 2022105466 A1 WO2022105466 A1 WO 2022105466A1
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WO
WIPO (PCT)
Prior art keywords
gas
push rod
hollow tube
hollow tubes
actuated
Prior art date
Application number
PCT/CN2021/122571
Other languages
English (en)
French (fr)
Inventor
李柏颖
郑光翔
Original Assignee
洁霺生医科技股份有限公司
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Filing date
Publication date
Application filed by 洁霺生医科技股份有限公司 filed Critical 洁霺生医科技股份有限公司
Priority to KR1020237016723A priority Critical patent/KR20230092968A/ko
Priority to JP2023528538A priority patent/JP2023553262A/ja
Priority to EP21893616.9A priority patent/EP4249014A4/en
Priority to AU2021383119A priority patent/AU2021383119A1/en
Publication of WO2022105466A1 publication Critical patent/WO2022105466A1/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
    • 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
    • A61M5/178—Syringes
    • A61M5/20—Automatic syringes, e.g. with automatically actuated piston rod, with automatic needle injection, filling automatically
    • A61M5/2046—Media being expelled from injector by gas generation, e.g. explosive charge
    • 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
    • A61M5/178—Syringes
    • A61M5/31—Details
    • A61M5/315—Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
    • A61M5/31565—Administration mechanisms, i.e. constructional features, modes of administering a dose
    • A61M5/3159—Dose expelling manners
    • A61M5/31593—Multi-dose, i.e. individually set dose repeatedly administered from the same medicament reservoir
    • A61M5/31595—Pre-defined multi-dose administration by repeated overcoming of means blocking the free advancing movement of piston rod, e.g. by tearing or de-blocking
    • 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
    • A61M5/178—Syringes
    • A61M5/31—Details
    • A61M5/315—Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
    • A61M5/31565—Administration mechanisms, i.e. constructional features, modes of administering a dose
    • 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
    • A61M2005/14204—Pressure infusion, e.g. using pumps with gas-producing electrochemical cell
    • 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
    • A61M5/178—Syringes
    • A61M5/31—Details
    • A61M5/315—Pistons; Piston-rods; Guiding, blocking or restricting the movement of the rod or piston; Appliances on the rod for facilitating dosing ; Dosing mechanisms
    • A61M5/31511—Piston or piston-rod constructions, e.g. connection of piston with piston-rod
    • A61M2005/31518—Piston or piston-rod constructions, e.g. connection of piston with piston-rod designed to reduce the overall size of an injection device, e.g. using flexible or pivotally connected chain-like rod members

Definitions

  • the present invention relates to a multi-stage gas-actuated drug supply device, in particular to an actuated drug supply device and method that requires small volume and prevents gas leakage.
  • the treatment of many chronic diseases requires the subcutaneous administration of drugs or therapeutic agents in precisely controlled doses, either continuously or at specific time intervals.
  • Subcutaneous injection a common method of delivering drugs into the body, allows the drug to be slowly absorbed in the body over a longer period of time (compared to direct injection into a blood vessel).
  • pen or patch injectors have been developed using primary containers (prefilled syringes or prefilled cartridges) such as pen injectors, auto injectors and wearable injectors, enabling users to self-inject drugs into their own in the body.
  • these traditional pen injectors utilize springs or micromotors to generate a driving force to deliver the drug, which may cause unexpected pain during injection due to the unstable driving force caused by the spring or motor.
  • some treatments require injection volumes greater than 1 mL beyond the limits of the injection volume of a limited hypodermic device, and the injection velocity is either too fast (seconds) or too slow (hours); for example, intravenous injection of traditional protein drugs
  • the injection volume usually exceeds 30mL or even reaches 250mL, and the injection time is 30 minutes to several hours. Therefore, if the protein drug concentration can be increased to reduce the injection volume (1-20mL), a portable or wearable hypodermic injection device can be provided. To carry out home drug delivery, it will save patients waiting for injection time and improve the convenience of patient treatment.
  • protein drugs cannot be concentrated indefinitely. Increasing the protein concentration beyond the solubility limit of the protein will form crystals and precipitate.
  • the volume of many subcutaneously injected protein drugs at the necessary therapeutic dose often exceeds 1 ml.
  • Protein injections of more than 1 mL when injected at high flow rates can cause injection site swelling and patient pain, resulting in the largest injection volume of 1 mL of pen injector or autoinjector currently available on the market.
  • Many wearable drug pump devices are driven by stepper motors (or similar components used to rotate gears), however, their motion is discrete (one division at a time) rather than continuous. Therefore, the basal delivery flow provided by the stepper motor is also discrete (one drop at a time).
  • a basal rate in the range of 5 to 5000nl/min (a typical dosing regimen for insulin) with discrete 5nl deliveries at rates ranging from one delivery per hour to a thousand deliveries per hour, with 1 ml injections being the fastest Usually more than 3-6 hours, the injection rate is too slow for the patient's needs (5-10 minutes).
  • the present invention provides a multi-stage gas-actuated medicine supply device and method, which can be used with different medicine supply equipment.
  • a multi-stage gas-actuated medicine supply device of the present invention includes: a gas supply unit for supplying the gas of the device; a push rod unit, which is composed of several hollow tubes, one end of which is connected to the gas supply unit; a push rod The top is connected to the other end of the push rod unit; an air chamber passes through the push rod unit and is connected to the air supply unit; a limiting part is located at the connecting end of the connected hollow pipes, used to limit the telescopic lengths of several hollow pipes; and an air The sealing piece is located at the connecting end of the connected hollow pipe, which has the effect of sealing the air chamber.
  • the gas supply unit of the present invention includes an electrochemical pump.
  • the electrochemical pump can release gas at a linear or non-linear speed, and can also release gas slowly to push the push rod unit; it is worth noting that the present invention can cooperate with the injection site or/and The speed of delivery of different drugs requires administration, so that the injected person will not feel uncomfortable.
  • a multi-stage gas-actuated drug supply method of the present invention comprises: a gas supplying a gas with a linear or non-linear speed increase continuously within a period of time from a gas supply unit; the gas is charged to a gas covered by a push rod unit As the gas pressure received by the air chamber increases, several hollow tubes of the push rod unit are simultaneously stretched with linear or non-linear speed; the push rod unit is stretched to push a push block structure; if the gas supply unit continues When air is supplied, a limit portion on several hollow tubes can limit a stretched length of the push rod unit; and the push block structure can push a medicine.
  • the airtight member of the present invention is located at the connecting end of the connected hollow pipes, and the airtight member prevents the gas from leaking from the gas chamber, which can effectively prevent the gas from contaminating the supplied medicament.
  • FIG. 1 is a schematic diagram of a multi-stage gas-actuated drug supply device
  • Fig. 2 is a schematic flow diagram of a multi-stage gas actuated drug supply method
  • Figure 3 is a schematic diagram of a buffer gas chamber and a gas supply separation
  • Figure 4 is a schematic diagram of the push rod unit of the hollow tube from small to large;
  • FIG. 5 is a schematic diagram of a push rod unit of different forms of hollow tubes
  • FIG. 6 is a schematic diagram of a push rod unit of a hollow tube in a multi-segment form
  • Figure 7 is a schematic diagram of different airtight parts and concave design forms
  • Figure 8 is a schematic diagram of the change in the force area of the push rod unit
  • FIG. 9 is a schematic diagram of a cylinder assembly and a capillary hollow tube
  • Figure 10 is a schematic diagram of large and small spiral patterns
  • Figure 11 is a schematic structural diagram of the top joint part of the push rod and the buffer sheet
  • Figure 12 is a schematic diagram of a push rod unit with changes
  • Figure 13 is a schematic diagram of the injection needle of the drug supply actuating device
  • Fig. 14 is a schematic diagram of the injection needle of the drug supply actuating device and the general injection needle;
  • Figure 15 is a schematic diagram of different drug supply speed curves
  • a multi-stage gas-actuated drug supply device 100 of the present invention can be connected to a drug injection container 10 for use, and the device 100 includes:
  • a gas supply unit 1 providing a gas
  • a push rod unit 2 is composed of several hollow tubes, one end of which is connected to the air supply unit 1, and the hollow tubes can be stretched by gas;
  • a push rod top 3 connected to the other end of the push rod unit 2, pushes a movable blocking member 15 according to the extension of several hollow tubes, and further pushes a medicine 13;
  • An air chamber 4 which penetrates through the push rod unit 2 and is connected to the air supply unit 1, is used for accommodating gas and extending several hollow tubes as the gas increases, further expanding the air chamber 4;
  • the push rod unit 2 when the air supply unit 1 is not in action, the push rod unit 2 is in the shortest unextended state; after the air supply unit 1 provides gas, the extension length of the push rod unit 2 is less than the total length of several hollow tubes.
  • the gas supply unit 1 of the present invention includes an electrochemical pump.
  • the electrochemical pump can release gas at a linear or non-linear speed, and can also release gas slowly to push the push rod unit 2; / And the speed of supply of different drugs requires the drug to be given without making the injectee feel uncomfortable.
  • a multi-stage gas-actuated drug supply method includes:
  • a gas with a linear or non-linear velocity increase is continuously supplied by a gas supply unit 1 within a period of time;
  • the gas is charged to a gas chamber 4 covered by a push rod unit 2;
  • the movable blocking member 15 includes a rubber plug and a piston.
  • a multi-stage gas-actuated drug supply device 100 as shown in FIG. 3 , a plurality of hollow tubes of the push rod unit 2 have an airtight member 9 at the connecting end of the connected hollow tubes. And a limit part 5, the airtight part 9 prevents the gas from leaking from the gas chamber 4, which can effectively prevent the gas from contaminating the supplied medicine; the limit part 5 limits the extension length of several hollow tubes.
  • a multi-stage gas-actuated medicine supply device 100 as shown in FIG. 3, the gas supply unit 1 is further connected to a buffer air chamber 7 and then connected to the push rod unit 2; the buffer air chamber 7 To prevent the gas generated by the air supply unit from directly impacting the push rod unit 2, so as to achieve the smooth extension of the push rod unit 2; the shape of the buffer air chamber 7 shown in the figure is only an embodiment, and the present invention is not limited in this shape.
  • a multi-stage gas-actuated medicine supply device 100 is shown in FIG. 3 , the gas supply unit 1 may be of a separate design, and the push rod unit 2 is connected by a connecting pipe.
  • the push rod unit 2 is composed of large to small hollow tubes according to the tube diameter, and the inner diameter of the Nth hollow tube is slightly larger than the outer diameter of an N+1th hollow tube, so that the N+1th hollow tube is The hollow tube can slide in the Nth hollow tube; N is the number of 20 sections of the hollow tube, which is an integer greater than 0.
  • the push rod unit 2 is composed of three sections of hollow tubes.
  • One end of the first hollow tube 21 is connected to the air supply unit 1 , and the other end is connected to a second hollow tube 22 , the outer diameter of the second hollow tube 22 is slightly smaller than the inner diameter of the first hollow tube 21, so that the second hollow tube 22 can slide in the first hollow tube 21;
  • the third hollow tube 23 is connected to the second hollow tube 22 , the outer diameter of the third hollow tube 23 is slightly smaller than the inner diameter of the second hollow tube 22, so that the third hollow tube 23 can slide in the second hollow tube 22, and the other end of the third hollow tube 23 is connected to the top of a push rod 3.
  • the push rod unit 2 is composed of hollow tubes with diameters from small to large.
  • the outer diameter of the Nth hollow tube is slightly smaller than the inner diameter of the Nth hollow tube, so that the Nth hollow tube is slightly smaller than the inner diameter of the Nth hollow tube. It can slide in the N+1th hollow tube; N is the number of 20 sections of the hollow tube, which is an integer greater than 0.
  • the push rod unit 2 is composed of three sections of hollow tubes.
  • One end of the first hollow tube 21 is connected to the air supply unit 1 , and the other end is connected to the second hollow tube 22 .
  • the outer diameter of the first hollow tube 21 is slightly smaller than the inner diameter of the second hollow tube 22, so that the first hollow tube 21 can slide in the second hollow tube 22;
  • the third hollow tube 23 is connected to the second hollow tube 22,
  • the outer diameter of the second hollow tube 22 is slightly smaller than the inner diameter of the third hollow tube 23, so that the second hollow tube 22 can slide in the third hollow tube 23, and the other end of the third hollow tube 23 is connected to a push rod top 3 .
  • the push rod units of different forms of hollow tubes are shown in the right figure of FIG. 5
  • the push rod unit 2 is composed of three sections of hollow tubes, and one end of the first hollow tube 21 is connected to the air supply unit 1.
  • the other end is connected to the second hollow tube 22.
  • the outer diameter of the first hollow tube 21 is slightly smaller than the inner diameter of the second hollow tube 22, so that the first hollow tube 21 can slide in the second hollow tube 22;
  • the third The hollow tube 23 is connected to the second hollow tube 22.
  • the inner diameter of the second hollow tube 22 is slightly larger than the outer diameter of the third hollow tube 23, so that the third hollow tube 23 can slide in the second hollow tube 22, and the third hollow tube 23 can slide in the second hollow tube 22.
  • the other end of the hollow tube 23 is connected to a push rod top 3 .
  • the push rod units of different forms of hollow tubes are shown in the left figure of FIG. 5
  • the push rod unit 2 is composed of three sections of hollow tubes, and one end of the first hollow tube 21 is connected to the air supply unit 1.
  • the other end is connected to the second hollow tube 22.
  • the inner diameter of the first hollow tube 21 is slightly larger than the outer diameter of the second hollow tube 22, so that the second hollow tube 22 can slide in the first hollow tube 21;
  • the hollow tube 23 is connected to the second hollow tube 22.
  • the outer diameter of the second hollow tube 22 is slightly smaller than the inner diameter of the third hollow tube 23, so that the second hollow tube 22 can slide in the third hollow tube 23.
  • the other end of the hollow tube 23 is connected to a push rod top 3 .
  • the push rod unit of a multi-section hollow tube is shown in FIG. 6
  • the push rod unit 2 may be composed of several hollow tubes, including two sections of hollow tubes (as shown in the left figure of FIG. 6 ) shown), four-section hollow pipe (as shown in the right picture of Figure 6); the length of the two-section hollow pipe is half of the total length when the two-section hollow pipe is not stretched; the length of the four-section hollow pipe is four One part, the present invention can effectively reduce the size of the device and save space.
  • the length can be reduced to 1 mm.
  • the contact area of the hollow tube changes accordingly, which further affects the stretching speed of the hollow tube;
  • the extension speed of the tube is inversely proportional.
  • a multi-stage gas-actuated drug supply device 100 is shown in FIG. 7 , and the airtight member 9 includes a circle, a quadrangle, an ellipse, a polygon, an X shape, etc.; each form is hollow
  • the tube stretching speed is not the same.
  • the airtight parts 9 can be used in combination.
  • various forms can be used in combination; the stretching speed of the hollow tubes for each combination form is determined according to the form of the airtight parts 9; it is worth noting Yes, according to the properties of different drugs or/and the characteristics of different subcutaneous tissues, this kind of matching design can design the time-speed curve of drug supply that makes the recipient feel the least discomfort.
  • the airtight member 9 can be used with one or more backing rings 91 , which can improve the deformation of the airtight member 9 when the hollow tube expands and contracts under high pressure.
  • the limiting portion 5 is of a concave design, and the height of the side of the concave is lower than the height of the airtight member 9 , so as to strengthen the positioning of the airtight member 9 and ensure airtightness.
  • FIG. 8 several hollow pipes of the push rod unit can be directly designed with different pipe diameters or/and with different pipe wall thicknesses, so as to indirectly change the amount of air released by the air supply unit 1
  • the relationship between the force area (A) of the gas pressure (P) and the normal force (F); the formula is as follows:
  • the force-bearing area (A) is proportional to the positive force (F) of the stretching speed, and the larger the force-bearing area (A), the faster the stretching speed;
  • the variable and controllable drug supply rate curve is realized by changing the ratio of the inner diameter of the several hollow tubes to the thickness of the tube wall, and changing and controlling the stretching sequence and speed of the several hollow tubes.
  • a four-stage gas-actuated drug supply device is composed of a push rod unit 2 and a drug injection container 10, which can realize different drug supply speed curves;
  • Figure 15 shows the relationship between
  • the inner surface roughness of several hollow tubes of the push rod unit can be designed according to the actual stretching sequence and stretching speed;
  • the stretching speed is inversely proportional (the greater the roughness, the slower the stretching speed), by changing the ratio of the roughness of the inner surface of the hollow tubes, changing and controlling the stretching sequence and speed of the hollow tubes to achieve variable and controllable supply. drug rate curve.
  • a multi-stage gas-actuated drug supply device 100 is shown in the left figure of FIG. 9 .
  • the end section of the push rod unit 2 is a cylinder assembly 8 . Push one end of the cylinder assembly 8 directly, and the other end is the top 3 of the push rod.
  • a multi-stage gas-actuated drug supply device 100 is shown in the right figure of FIG. 9 , and the first hollow tube 21 can be a capillary hollow tube 14 structure.
  • a multi-stage gas-actuated drug supply device 100 is shown in the cross-sectional view of a hollow tube in FIG.
  • the hollow tube of the push rod unit 2 extends in a spiral manner; the spiral pattern includes a small spiral pattern 11 and a large spiral pattern 12 .
  • the top 3 of the push rod is connected to a joint 31 for installing various push block structures 6 to lock the movable blocking member 15 to assist in pushing the medicine, and the push block structure 6 includes movable blocking Piece Lock, Push Rod Top Lock, Active Barrier Push Rod Top Lock.
  • a buffer piece 92 is installed at one end of the hollow tube, and the buffer piece 92 can pass through one or more holes.
  • the buffer sheet 92 can change the stretching sequence and speed of each section of the hollow tube; the holes can be micro-nano-scale to micro-scale holes to provide different gas passage speed control.
  • the buffer sheet 92 can be matched with different forms of airtight parts 9 and hollow tubes 20 of different lengths to achieve a changing drug supply curve.
  • the push rod unit according to an embodiment of the present invention 2.
  • the composition structure is that the length of the second hollow tube 22 is greater than the length of the third hollow tube 23, the first hollow tube 21 and the second hollow tube 22 use a circular airtight member 9, and the second hollow tube 22 and the third hollow tube 22 use a circular airtight member 9.
  • the hollow tube 23 uses a rectangular airtight member 9, and a buffer sheet 92 is installed at one end of the second hollow tube 22; because of the action of the buffer sheet 92, the gas generated by the air supply unit 1 fills the second hollow tube 22 of the gas chamber 4 first.
  • the second hollow tube 22 is first stretched to the first hollow tube 23. The length of the hollow tube 21; the gas further fills the third hollow tube 23 of the gas chamber 4.
  • the stretching speed will be slower than the stretching speed of the second hollow tube 22; A relatively large amount of the medicine 13 is pushed at a relatively fast speed, and a relatively small amount of the medicine 13 is pushed at a relatively slow speed.
  • the multi-stage gas actuated drug supply device 100 can be used with a drug injection container 10 containing a movable barrier to form a drug supply actuated device injection needle 200 , and then cooperate with the gas supply unit 1 As an electrochemical pump, the device can be installed on automatic injection equipment.
  • the electrochemical pump generates gas slowly and pushes the medicament in the injection needle 200 gently, so that patients who need a long time and continuous small amount of subcutaneous injection will not feel discomfort due to the injection process; the current long time continuous small amount In the subcutaneous injection of the invention, the injection volume and the injection time are controlled by the nurse, and this problem can be solved by the present invention.
  • FIG. 14 An embodiment of the present invention is shown in FIG. 14 .
  • a multi-stage gas actuated drug supply device 100 of the present invention is combined with the drug injection container 10 to form a drug supply actuating device injection needle 200 , and the present invention is effective. Shorten the needle length.

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  • Health & Medical Sciences (AREA)
  • Vascular Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Physics & Mathematics (AREA)
  • Fluid Mechanics (AREA)
  • Infusion, Injection, And Reservoir Apparatuses (AREA)
  • Physical Or Chemical Processes And Apparatus (AREA)
  • Catching Or Destruction (AREA)
  • Medicines Containing Antibodies Or Antigens For Use As Internal Diagnostic Agents (AREA)

Abstract

一种多段式气体致动供药装置(100)及方法。多段式气体致动供药装置(100)连接药物注射容器(10)，包括：用于提供气体的供气单元(1)；推杆单元(2)，由数个中空管(21,22,23)组成，一端连接供气单元(1)，可由气体伸展中空管(21,22,23)；推杆顶部(3)，连接推杆单元(2)另一端，依着中空管(21,22,23)伸展而推送药剂(13)；气室(4)，贯通推杆单元(2)并连接供气单元(1)，用于容纳气体并随着气体增加而伸展中空管(21,22,23)，进一步扩展气室(4)；限位部(5)，位于相连接的中空管连接端，限制中空管(21,22,23)伸缩长度；以及气密件(9)，位于相连接的中空管连接端，使气室(4)达到密封效果。

Description

多段式气体致动供药装置及方法 技术领域
本发明涉及一种多段式气体致动供药装置，尤其涉及需要小体积并且防气体泄漏的致动供药装置及方法。
背景技术
许多慢性疾病的治疗，需要以精准受控的药剂量，在连续或特定时间间隔下进行皮下施用药物或治疗剂。皮下注射，是将药物递送到体内的常用方法，让药物在身体内用更长的时间被缓慢地吸收(与直接注射到血管中相比)。目前，已经开发出使用笔式注射器、自动注射器和可穿戴注射器等主要容器(预充式注射器或预充式药筒)的笔式或贴片式注射器，使用户能够自行将药物注射到自己的身体中。然而，这些传统的笔式注射器利用弹簧或微型马达来产生推动力来输送药物，由于弹簧或马达引起的不稳定驱动力，可能会在注射过程中引起意想不到的疼痛。
此外，某些治疗需要大于1毫升的注射量超过限有皮下注射装置之注射体积之极限，且注射速动不是过快(数秒钟)就是过慢(数小时)；例如，传统蛋白质药物之静脉注射其注射量通常超过30mL甚至到达250mL，其注射时间为30分钟到数小时，因此，若能提高蛋白药物浓度来缩小其注射体积(1-20mL)以提供可携式或穿戴式皮下注射装置来进行居家药物传递，将能节省病人注射时间的等待且提高病人治疗的方便性。但蛋白质药物无法无限制的浓缩，提高蛋白质浓度以至于超过蛋白质之溶解度极限将形成结晶并沉淀，因此很多皮下注射的蛋白质药物在必要之治疗剂量下的体积时常远超过1毫升。以高流速注射时超过1毫升的蛋白质注射量就会导致注射部位肿胀和患者疼痛，造成市场上现有的笔型或自动皮下注射装置(pen injector or autoinjector)最大的注射体积为1毫升。许多穿戴式药物泵装置是由步进电机(或用于旋转齿轮的类似部件)驱动，然而，它们的运动是离散的(每次转一格)，而不是连续的。因此，步进电机提供的基础输送流量也是离散的(每次一小滴)。例如，在5到5000nl/min范围内的基础速率(胰岛素的典型剂量方案)具有离散的每次5nl递送，速率介于每小时一次递送至每小时一千次递送之间，注射1毫升最快通常要超过3-6小时，此种注射速度又过慢无法满足病人需求(5-10分钟)。
现有的电化学泵通常是将产生的气体施加到药物分离构件(例如隔膜或活动阻隔件)上直接作用/施力，以将药物从其药物容器中排出，从而形成完整的药物输送动作。在该给药过程中，存在电化学产生的高压气体通过分离构件的泄漏部位(例如隔膜、容器壁或活动阻隔件上的缺陷)泄漏而导致药物污染的风险。
所以，开发一种藉由温和的气体产生速度来推动供药，同时又不能让气体有污染药剂的风险存在，并兼具小体积的致动供药装置刻不容缓。
发明内容
有鉴于此，本发明为解决背景技术问题，提供一种多段式气体致动供药装置及方法，可搭配不同供药设备使用。
本发明的一种多段式气体致动供药装置包含:一供气单元，用于供应本装置的气体；一推杆单元，由数个中空管组成，一端连接供气单元；一推杆顶部，连接推杆单元另一端；一气室，贯通推杆单元并连接供气单元；一限位部，位于相连接的中空管连接端，用于限制数个中空管伸缩长度；以及一气密件，位于相连接的中空管连接端，起到使气室密封的效果。
本发明的供气单元包含一电化学泵，电化学泵可依一线性或非线性速度释放气体，亦可缓慢释放气体推动推杆单元；值得注意的是，本发明可配合注射部位或/和不同药物的供药速度需求给药，使被注射者不会感觉到不舒服。
本发明的一种多段式气体致动供药方法包含:由一供气单元在一时间段内连续提供一线性或非线性速度增加的一气体；气体充至一推杆单元所包覆的一气室；随着气室接收的气体压力增加，推杆单元的数个中空管同时随着线性或非线性速度伸展；藉由推杆单元伸展，进而推动一推块结构；若供气单元持续供气，则数个中空管上的一限位部可限制推杆单元的一段伸展长度；以及推块结构可推挤一药剂。
此外，本发明的气密件位于相连接的中空管连接端，气密件防止该气体从气室泄漏，能有效防止气体污染所供的药剂。
附图说明
图1是多段式气体致动供药装置示意图；
图2是多段式气体致动供药方法流程示意图；
图3是具缓冲气室及供气分离式示意图；
图4是由小到大的中空管之推杆单元示意图；
图5是不同形式的中空管的推杆单元示意图；
图6是多段形式的中空管的推杆单元示意图；
图7是搭配不同气密件及凹型设计形式示意图；
图8是推杆单元受力面积变化示意图；
图9是柱体组件及毛细中空管示意图；
图10是大、小螺旋纹示意图；
图11是推杆顶部结合部及缓冲片结构示意图；
图12是具变化的推杆单元示意图；
图13是供药致动装置注射针示意图；
图14是供药致动装置注射针与一般注射针示意图；
图15是不同的供药速度曲线示意图；
附图标记说明：1-供气单元；2-推杆单元；3-推杆顶部；4-气室；5-限位部；6-推块结构；7-缓冲气室；8-柱体组件；9-气密件；10-药物注射容器；11-小螺旋纹；12-大螺旋纹；13-药剂；14-毛细中空管；15-活动阻隔件；20-中空管；21-第一中空管；22-第二中空管；23-第三中空管；24-第四中空管；31-结合部；91-背托环；92-缓冲片；100-多段式气体致动供药装置；200-供药致动装置注射针；300-一般注射针；A1～A4-多段式气体致动供药方法流程。
具体实施方式
以下结合附图对本发明的实施方式进行更详细的说明。应当了解的是，本发明具体实施方式中的组件大小、比例、间隙仅为举例说明，而不是对本发明的限制。
本发明的一种多段式气体致动供药装置100如图1、图13所示，可连接一药物注射容器10使用，装置100包含:
一供气单元1，提供一气体；
一推杆单元2，由数个中空管所组成，一端连接供气单元1，可藉由气体伸展该些中空管；
一推杆顶部3，连接推杆单元2另一端，依着数个中空管伸展而推动一活动阻隔件15，进一步推送一药剂13；
一气室4，贯通推杆单元2并连接供气单元1，用于容纳气体并随着气体增加而伸展数个中空管，进一步扩展气室4；
其中，供气单元1未动作时，推杆单元2处于未伸展的最短状态；供气单元1提供气体后，推杆单元2伸展长度小于数个中空管总长。
本发明的供气单元1包含一电化学泵，电化学泵可依一线性或非线性速度释放气体，亦可缓慢释放气体推动推杆单元2；值得注意的是，本发明可配合注射部位或/和不同药物的供药速度需求给药物，不会使被注射者感觉到不舒服。
在本发明一实施例中，一种多段式气体致动供药方法如图2所示，包含:
A1.由一供气单元1在一时间段内连续提供一线性或非线性速度增加的一气体；
A2.气体充至一推杆单元2所包覆的一气室4；
A3.随着该气室4接收的气体压力增加，推杆单元2的数个中空管同时随着线性或非线性速度伸展；以及
A4.藉由推杆单元2伸展，进而推动一药物注射容器的活动阻隔件15来推送一药剂13。
较佳的，活动阻隔件15包含橡胶塞及活塞。
在本发明一实施例中，一种如图3所示的多段式气体致动供药装置100，推杆单元2的数个中空管在位于相连接的中空管连接端具有一气密件9及一限位部5，气密件9防止气体从气室4泄漏，能有效防止气体污染所供的药剂；限位部5限制数个中空管伸展长度。
在本发明一实施例中，一种多段式气体致动供药装置100，如图3所示，供气单元1进一步连接一缓冲气室7后再与推杆单元2连接；缓冲气室7起到让供气单元产生的的气体不会直接冲击推杆单元2，从而达到推杆单元2平稳伸展；图中所示的缓冲气室7形状仅为一实施例，本发明并不受限于此形状。
在本发明一实施例总，一种多段式气体致动供药装置100如图3所示，供气单元1可为分离式设计，藉由连接管连接推杆单元2。
在本发明一实施例中，推杆单元2依管径由大到小的中空管所组成，第N中空管内径略大于一第N+1中空管外径，使第N+1中空管可在第N中空管内滑动；N为该中空管20节数，为大于0的整数。
在本发明一实施例中，如图1所示，推杆单元2由三段中空管所组成，第一中空管21一端连接供气单元1，另一端连接一第二中空管22，第二中空管22外径略小于第一中空管21内径，使第二中空管22可在第一中空管21内滑动；第三中空管23连接第二中空管22，第三中空管23外径略小于第二中空管22内径，使第三中空管23可在第二中空管22内滑动，第三中空管23另一端连接一推杆顶部3。
在本发明一实施例中，推杆单元2由管径从小到大的中空管所组成，第N中空管外径略小于一第N+1中空管内径，使第N中空管可在第N+1中空管内滑动；N为该中空管20节数，为大于0的整数。
在本发明一实施例中，如图4所示，推杆单元2由三段中空管所组成，第一中空管21一端连接供气单元1，另一端连接第二中空管22，第一中空管21外径略小于第二中空管22内径，使第一中空管21可在第二中空管22内滑动；第三中空管23连接第二中空管22，第二中空管22外径略小于第三中空管23内径，使第二中空管22可在第三中空管23内滑动，第三中空管23另一端连接一推杆顶部3。
在本发明一实施例中，不同形式的中空管的推杆单元如图5右图所示，推杆单元2由三段中空管所组成，第一中空管21一端连接供气单元1，另一端连接第二中空管22，第一中空管21外径略小于第二中空管22内径，使第一中空管21可在第二中空管22内滑动；第三中空管23连接第二中空管22，第二中空管22内径略大于第三中空管23外径，使第三中空管23可在第二中空管22内滑动，第三中空管23另一端连接一推杆顶部3。
在本发明一实施例中，不同形式的中空管之推杆单元如图5左图所示，推杆单元2由三段中空管所组成，第一中空管21一端连接供气单元1，另一端连接第二中空管22，第一中空管21内径略大于第二中空管22外径，使第二中空管22可在第一中空管21内滑动；第三中空管23连接第二中空管22，第二中空管22外径略小于第三中空管23内 径，使第二中空管22可在第三中空管23内滑动，第三中空管23另一端连接一推杆顶部3。
在本发明一实施例中，多段形式的中空管的推杆单元如图6所示，推杆单元2可由数个中空管所组成，包含两段中空管(如图6左图所示)、四段中空管(如图6右图所示)；两段中空管未伸展时长度为总长度的二分之一；四段中空管未伸展时长度为总长度的四分之一，本发明可有效缩小装置尺寸节省空间。
较佳的，多段式气体致动供药装置100的推杆单元2未伸展时，长度可缩小至1mm。
较佳的，依气密件9形状与材质不同，中空管的接触面积随之改变，进一步影响中空管伸展速度；气密件9贴紧中空管形成一接触面积，该接触面积与中空管的伸展速度成反比。
在本发明一实施例中，一种多段式气体致动供药装置100如图7所示，气密件9包含圆形、四边形、椭圆形、多边形、X型等…；每种形式使中空管伸展速度都不相同。
上述实施例中，气密件9可交互搭配使用，例如图7所示，多种态样可搭配使用；每种搭配形式的数个中空管伸展速度，依气密件9形式决定；值得注意的是，此种搭配设计可依不同药剂性质或/及供给不同皮下部位组织特性，设计出使受药剂者最不会感觉不舒服的药剂供给的时间速度曲线。
较佳的，如图7所示，气密件9可搭配一个或一个以上背托环91使用，可改善在高压下该气密件9在中空管伸缩时的变形量。
较佳的，如图7所示，限位部5为凹型设计，凹型侧边高度低于气密件9高度，以加强气密件9定位，确保气密性。
在本发明一实施例中，如图8所示，推杆单元的数个中空管可直接设计成不同管径大小或/和设计成不同的管壁厚度，间接改变供气单元1释出气体压力(P)的受力面积(A)与正向力(F)关系；公式如下：
压力(P)＝正向力(F)/受力面积(A)，P＝F/A
在供气单元1提供的固定压力(P)下，受力面积(A)与伸展速度正向力(F)成正比，受力面积(A)面积越大伸展速度越快；进一步，可藉由改变数个中空管的内径与管壁厚度的比率，改变并控制数个中空管的伸展顺序与速度来实现具变化并可控制的供药速率曲线。
在本发明一实施例中，一种四段式气体致动供药装置，如图8所示，由推杆单元2搭配药物注射容器10组成，可实现不同的供药速度曲线；第一中空管21固定连接供气单元1，由供气单元1提供固定压力(P)；在第一阶段，推杆单元未伸展时受力面积(A 1)最大正向力(F 1)最高(A 1＝推杆顶部3面积+该第二、三中空管22、23壁厚*2)，流量最高2st；在第二阶段，第二中空管22已伸展时受力面积(A 2＝推杆顶部3面积+第三中空管23壁厚*2)，流量次之3nd；在第三阶段，第三中空管22已伸展时受力面积(A 3＝该推杆顶部3面积)，流量最小4rd；图15显示了时间与该药剂流量的关系。
在本发明一实施例中，推杆单元的数个中空管的内表面粗糙度，可依实际伸展顺序 与伸展速度来设计；由于数个中空管内表面的粗糙度与数个中空管的伸展速度成反比(粗糙度越大伸展速度越慢)，可藉由改变该些中空管内表面的粗糙度之比率，改变并控制中空管的伸展顺序与速度来实现具变化并可控制的供药速率曲线。
在本发明一实施例中，一种多段式气体致动供药装置100如图9左图所示，推杆单元2末段为一柱体组件8，柱体组件8没有气室4，气体直接推挤柱体组件8一端，另一端为推杆顶部3。
在本发明一实施例中，一种多段式气体致动供药装置100如图9右图所示，第一中空管21可为一毛细中空管14结构。
在本发明一实施例中，一种多段式气体致动供药装置100如图10中空管剖面图所示，推杆单元2的一中空管20的内壁具有多个螺旋纹，可让推杆单元2的中空管以螺旋方式伸展；螺旋纹包含小螺旋纹11、大螺旋纹12。
在本发明一实施例中，如图11所示，推杆顶部3连接一结合部31，用于安装多种推块结构6来锁定活动阻隔件15辅助推送药剂，推块结构6包含活动阻隔件锁定、推杆顶部锁定、活动阻隔件推杆顶部锁定。
在本发明一实施例中，如图11所示，中空管一端安装一缓冲片92，缓冲片92上可贯通一个或一个以上的孔洞，藉由每段该中空管安装不同数量孔洞的缓冲片92，可改变每段中空管的伸展顺序与速度；孔洞可微纳米级至微米级孔洞以提供不同的气体通过速度控制。
如本发明图12所示的一实施例所示，缓冲片92搭配不同形式的气密件9及不同长短的中空管20可实现具变化的供药曲线，本发明一实施例的推杆单元2组成结构为第二中空管22长度大于第三中空管23长度，第一中空管21与第二中空管22使用圆形的气密件9，第二中空管22与第三中空管23使用长方形的气密件9，第二中空管22一端安装有缓冲片92；因为缓冲片92作用使得供气单元1所产生的气体先行充满气室4的第二中空管22区间，又因圆形的气密件9与第一中空管21的接触面积小于长方形的气密件9与第三中空管23的接触面积，使得第二中空管22先被伸展至第一中空管21长度；气体再进一步充满气室4的第三中空管23区间，因为长方形的气密件9，故伸展速度会比第二中空管22伸展速度慢；本发明达到先以一相对快的速度推送该药剂13量的相对多的量，再以一相对慢的速度推送药剂13量相对少的量。
承上所述，利用改变中空管长度、管径、粗糙度并搭配该气密件9形状，加上缓冲片92的不同组合，可实现不同的供药速度曲线。
本发明一实施例如图13所示，多段式气体致动供药装置100可搭配含有活动阻隔件的一药物注射容器10组成一供药致动装置注射针200使用，再配合该供气单元1为电化学泵，本装置可安装于自动注射设备上。
在上述实施例中，电化学泵缓慢产生气体，平缓推挤注射针200内的药剂，可使需要长时间且持续少量的皮下注射患者，不会因为注射过程感觉到不适；现行长时间持续少量的皮下注射，都是由护士来控制注射量及注射时间，利用本发明即可解决此一问题。
本发明一实施例如图14所示，本发明一种多段式气体致动供药装置100搭配该药物注射容器10组成的供药致动装置注射针200与一般注射针300比较，本发明可有效缩短注射针长度。
以上所述仅为本发明的实施例，并非用以限定本发明的保护范围，凡举依据本发明权利要求书所述内容、特征以及其精神而为之的其他变化的等效实施，皆应包含于本发明的保护范围内。

Claims (27)

  1. 一种多段式气体致动供药装置，连接一药物注射容器，包括:
    一供气单元，所述供气单元包含一电化学泵，可提供一气体；
    一推杆单元，其一端连接供气单元，并由不同管径的数个中空管组成，数个中空管的管径由小到大排列，第一中空管外径略小于第二中空管内径，使第一中空管可在第二中空管内滑动；
    一气室，贯通推杆单元并连接供气单元，用于容纳气体并随着气体增加而伸展所述数个中空管，进一步扩展气室；以及
    一推杆顶部，连接推杆单元另一端，依着所述数个中空管伸展而推动一活动阻隔件，进一步推送一药剂。
  2. 如权利要求1所述的多段式气体致动供药装置，推杆单元的第二中空管连接第三中空管，第三中空管外径略小于第二中空管内径，使第三中空管可在第二中空管内滑动。
  3. 如权利要求1所述的多段式气体致动供药装置，所述供气单元进一步连接缓冲气室后再与推杆单元连接。
  4. 如权利要求1所述的多段式气体致动供药装置，推杆单元的数个中空管一端安装一缓冲片，缓冲片上可贯通一个或一个以上的孔洞。
  5. 如权利要求1所述的多段式气体致动供药装置，推杆单元的数个中空管内一表面粗糙度与数个中空管的伸展速度成反比，粗糙度越大伸展速度越慢。
  6. 如权利要求1所述的多段式气体致动供药装置，所述中空管在位于相连接的数个中空管连接端具有一气密件、一限位部，限位部为凹型，凹型侧边高度低于气密件高度，以确保气密性。
  7. 如权利要求1所述的多段式气体致动供药装置，所述数个中空管具有数个螺旋纹，可使推杆单元的数个中空管顺着螺旋方向伸展。
  8. 如权利要求1所述的多段式气体致动供药装置，推杆顶部推动活动阻隔件的供药致动装置注射针，可安装于自动注射设备。
  9. 一种多段式气体致动供药装置，连接一药物注射容器，包括：
    一供气单元，所述供气单元包含一电化学泵，可提供一气体；
    一推杆单元，一端连接供气单元，所述推杆单元由不同管径的数个中空管所组成，所述数个中空管的管径由大到小排列，第一中空管内径略大于第二中空管外径，使第二中空管可在第一中空管内滑动；
    一气室，贯通推杆单元并连接供气单元，用于容纳气体并随着气体增加而伸展数个中空管，进一步扩展气室；以及
    一推杆顶部，连接推杆单元另一端，依着数个中空管伸展而推动一活动阻隔件，进一步推送一药剂。
  10. 如权利要求9所述的多段式气体致动供药装置，推杆单元的第二中空管连接一第三中空管，第三中空管内径略大于第二中空管外径，使第二中空管可在第三中空管内滑动。
  11. 如权利要求9所述的多段式气体致动供药装置，供气单元进一步连接一缓冲气室后再与推杆单元连接。
  12. 如权利要求9所述的多段式气体致动供药装置，推杆单元的数个中空管一端安装一缓冲片，所述缓冲片上可贯通一个或一个以上的孔洞。
  13. 如权利要求9所述的多段式气体致动供药装置，推杆单元的数个中空管的管径大小及一管壁厚度形成受力面积，受力面积与伸展速度成正比，受力面积越大伸展速度越快。
  14. 如权利要求9所述的多段式气体致动供药装置，推杆单元的数个中空管内的表面粗糙度与数个中空管的伸展速度成反比，粗糙度越大伸展速度越慢。
  15. 如权利要求9所述的多段式气体致动供药装置，数个中空管在位于相连接的数个中空管连接端具有一气密件、一限位部，限位部为凹型，凹型侧边高度低于气密件高度，以确保气密性。
  16. 如权利要求9所述的多段式气体致动供药装置，数个中空管具有数个螺旋纹，可使推杆单元的数个中空管顺着螺旋方向伸展。
  17. 如权利要求9所述的多段式气体致动供药装置，推杆单元末段为一柱体组件，气体直接推挤所述柱体组件。
  18. 如权利要求9所述的多段式气体致动供药装置，推杆顶部推动活动阻隔件的供药致动装置注射针，可安装于自动注射设备。
  19. 一种多段式气体致动供药方法，所述方法包括：
    A1.由一供气单元在一时间段内连续提供一线性或非线性速度增加的一气体；
    A2.气体充至一推杆单元所包覆的一气室；
    A3.随着气室接收的气体压力增加，推杆单元的数个中空管同时随着线性或非线性速度伸展；以及
    A4.藉由推杆单元伸展，进而推动一药物注射容器的活动阻隔件来推送一药剂。
  20. 如权利要求19所述的多段式气体致动供药方法，供气单元连接一缓冲气室后再与推杆单元连接，可避免该气体直接冲击气室。
  21. 如权利要求19所述的多段式气体致动供药方法，数个中空管一端安装一缓冲片，缓冲片上可贯通一个或一个以上的孔洞，藉由每段中空管安装不同数量孔洞的缓冲片可改变每段中空管的伸展顺序与速度。
  22. 如权利要求19所述的多段式气体致动供药方法，推杆单元的数个中空管的管径大小及管壁厚度形成一受力面积，受力面积与伸展速度成正比，受力面积越大伸展速度越快。
  23. 如权利要求19所述的多段式气体致动供药方法，推杆单元的数个中空管藉由改变内表面的粗糙度可调整数个中空管的伸展速度，中空管内表面粗糙度与中空管的伸展速度成反比，粗糙度越大伸展速度越慢。
  24. 如权利要求19所述的多段式气体致动供药方法，数个中空管在位于相连接的数个中空管连接端具有一气密件，气密件贴合数个中空管的接触面积与中空管的伸展速度成反比。
  25. 如权利要求19所述的多段式气体致动供药方法，数个中空管具有数个螺旋纹，可使推杆单元的数个中空管顺着螺旋方向伸展。
  26. 如权利要求19所述的多段式气体致动供药方法，推杆顶部连接一结合部，可安装多种推块结构来辅助推送。
  27. 如权利要求19所述的多段式气体致动供药方法，推杆顶部推动活动阻隔件的供药致动装置注射针，可安装于自动注射设备。
PCT/CN2021/122571 2020-11-18 2021-10-08 多段式气体致动供药装置及方法 WO2022105466A1 (zh)

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