Source: https://patents.google.com/patent/DE60111967T2/en
Timestamp: 2019-12-11 17:51:45
Document Index: 657990472

Matched Legal Cases: ['art 18', 'art 18', 'art 18', 'art 18', 'art 18', 'art 38', 'art 38', 'art 38', 'art 38', 'art 38']

DE60111967T2 - Needleless hypodermic injection system - Google Patents
Needleless hypodermic injection system
DE60111967T2
DE60111967T2 DE2001611967 DE60111967T DE60111967T2 DE 60111967 T2 DE60111967 T2 DE 60111967T2 DE 2001611967 DE2001611967 DE 2001611967 DE 60111967 T DE60111967 T DE 60111967T DE 60111967 T2 DE60111967 T2 DE 60111967T2
DE2001611967
DE60111967D1 (en
2000-02-16 Priority to US18295400P priority Critical
2000-02-16 Priority to US182954P priority
2001-01-16 Application filed by Roche Diagnostics GmbH filed Critical Roche Diagnostics GmbH
2005-08-25 Publication of DE60111967D1 publication Critical patent/DE60111967D1/en
2006-04-20 Publication of DE60111967T2 publication Critical patent/DE60111967T2/en
The The invention relates to a needleless injection system for the subcutaneous Injection of liquid medication.
In International Patent Application Publication No. WO-A-98/31409 will be a needleless injection system for the subcutaneous injection of liquid Medicines described that use a disposable drug cartridge and a reusable delivery device. The reusable delivery device has a locking Pressure chamber, which contains and supports the cartridge, and other required Including subsystems an electric ignition and security locks. The disposable cartridge contains one prefilled sterile single-dose medication container and a small pyrotechnic Gas generant that acts on the medicament container to administer the injection Pressure generated from 200 to 300 bar. The single-dose medication container has a first area covered by a thin-walled drug reservoir is bounded by flexible plastic, and a second area with a jet nozzle. Of the Gas pressure generated by the gas generator acts on the thin-walled Reservoir that collapses under pressure so that the fluid is expelled through the jet nozzle.
at the system known from WO-A-98/31409 forms the thin wall the drug chamber creates a barrier between the liquid drug and the high pressure gas. This thin wall is mainly hydrostatic Exposed to pressure and therefore loaded only with low tensile and shear forces. However, in the case of a punctual failure of the thin flexible Wall of the drug chamber to reduce the probability that gas with the liquid Drug comes into contact, it is advisable to have a second wall, for example a rubber wall inserting the thin wall of the drug chamber shields.
One Disadvantage of the structure of the known from WO-A-98/31409 system is that with it the use of cheaper Energy sources, for example mechanical devices or low-pressure gas sources, for generating the required pressure on the deformable wall of the medicine container not possible is.
This Disadvantage leads Therefore, to the problem of how the structure of the injection system change that way lets that through the changed one Building the use cheaper Energy sources possible and so reduces the manufacturing cost of the entire system can be.
task Therefore, the present invention is a needleless injection system for the subcutaneous injection of liquid Medicines available to ask for that is designed, cost-effective To use energy sources, so that the Manufacturing costs of the injection system can be reduced.
According to the invention, this object is achieved by a needleless injection system having the following features:
(a) A medicament container configured and sized to store a quantity of fluid to be injected, wherein the medicament container has a first portion and a second portion in fluid communication with each other, wherein the first portion is deformable and the second portion has at least one opening .
(b) a hydrostatic chamber containing a transfer medium for transferring hydrostatic pressure, wherein the hydrostatic chamber is configured and dimensioned such that the medicament container is at least partially disposed in the hydrostatic chamber and that a pressure applied to the transfer medium would cause the first portion of the medicament container deforms to reduce the volume available in the medicament container for the liquid medicament, and
(c) a first piston having a first end and a second end opposite the first end, the first end having a surface adapted to apply pressure to the transfer medium contained within the hydrostatic chamber.
A preferred embodiment of a needleless injection system for subcutaneous injection according to the present invention additionally comprises
(d) an activatable force generator for generating a force and applying that force to the second end of the first piston to cause a corresponding pressure to be exerted on the transfer medium from the surface of the first end of the first piston, and
(e) an activating means for activating the force generator.
The main advantage of a invention Injection system is that it can achieve the above goal with him. A preferred embodiment of such a system additionally has the advantage that it can be manufactured entirely as a disposable injection system, which can be made available to the user ready for use in a sterility-ensuring packaging. In the context of the present invention, ready to use means that it is already filled with a predetermined amount of a drug and that the user no longer needs to assemble it before use.
Of the The invention will now be described with reference to preferred embodiments described. These embodiments serve the understanding of the invention, however, are not intended to be limiting.
1 shows a schematic cross section of a basic structure of a needleless injection system according to a preferred embodiment of the invention.
2 shows a schematic cross section of an embodiment of a needleless injection system according to the invention before activating the force generating means.
3 shows a schematic cross section of the in 2 shown embodiment after activation of the force generating means.
4 shows a schematic cross section of another embodiment of a needleless injection system according to the invention before activating the force generating means.
5 shows a schematic cross section of the in 4 shown embodiment after activation of the force generating means.
6 shows a schematic cross section of a modification of the in 2 shown first embodiment.
7 shows a schematic cross section of a modification of the in 4 shown first embodiment.
basic Structure of a needleless invention injection system
How to get by 1 In particular, a hypodermic injection system according to the invention for subcutaneous injection comprises the following components: a medicament container 11 , a hydrostatic chamber 16 and a piston 18 , Not shown in 1 an activatable force generator and activating means for activating the force generator, but these are also part of the illustrated system.
The medicine container 11 is for storing a quantity of liquid to be injected 12 trained and measured. The medicine container 11 has a first area with a medicine container that has a thin, flexible wall 13 has, and a second area, the one use 14 with a jet nozzle 15 contains. This nozzle 15 stands with the medicine container of the first area of the medicine container 11 in fluid communication. The wall 13 is deformable and can collapse. The jet nozzle 15 has an outlet opening 20 through which the liquid to be injected 12 is ejected. The medicine container 11 is made of suitable materials, such as polyethylene or polypropylene, which are suitable for storing medicines, including sensitive proteinaceous medicines.
The hydrostatic chamber 16 contains a transfer medium 17 for transmitting hydrostatic pressure and is designed and dimensioned so that the medicament container 11 at least partially in the hydrostatic chamber 16 is arranged and that one on the transfer medium 17 applied pressure would cause the wall 13 the first section of the medicine container 11 deformed so that in the first area for the liquid drug 12 available volume is reduced. In a preferred embodiment, the wall collapses 13 of the first area under pressure generated by the transfer medium 17 is applied to it, so that the entire volume of the liquid drug 12 through the jet nozzle 15 is ejected.
In general, it is the transfer medium 17 for transmitting hydrostatic pressure around a biocompatible material which flows well when exposed to a pressure of about 200 bar to 300 bar and which is substantially incompressible. The transfer medium 17 hydrostatically transfers the pressure from the piston to the disposable drug reservoir. The transfer medium 17 is inert to the drug and other materials used in the device. From the transfer medium 17 It is not expected to leak or evaporate during the shelf life of the injection system.
In the transfer medium 17 it is preferably a gel, for example an elastomeric silicone gel. Such a gel is an excellently biocompatible material, for example, in Long-term implants are used for humans. In the unlikely event that particles of the gel 17 come in contact with the liquid drug and thus penetrate into the body of a patient, one can assume that this is harmless. In the transfer medium 17 it may also be, for example, soft rubber or a sterile saline solution.
The piston 18 has a first end 19 and a second end 21 that's the first end 19 opposite. The first end 19 has a surface that closes the hydrostatic chamber 16 forms, and is designed to be in the hydrostatic chamber 16 contained gel 17 Exercise pressure.
The injection system of 1 further includes a metal housing 23 , which at one end by a closure insert 25 hermetically sealed. Through a crimping 30 or other equally secure fastener is the closure insert 25 in the case 23 held against internal pressure forces in this position. The closure insert has a bore 27 partially with gel 17 is filled. The piston 18 partially protrudes into the hole 27 into it. A suitable piston sealing element 28 ensures a sliding seal of the bore 27 through the piston 18 , The medicine container 11 is located in the housing 23 and is in, how 1 shows, arranged so that it the other end of the housing 23 closes. The with gel 17 filled hydrostatic chamber 16 extends between the inner end of the closure insert 25 and the medicine container 11 , At one end of the hydrostatic chamber 16 is through a closure insert seal 26 ensures a hermetic seal. The opposite end of the hydrostatic chamber 16 is through a rubber element 24 Hermetically sealed, with the drug container 11 in the case 23 is held in his position.
Being a force, like the one in 1 through the arrow 29 shown force, on one end of the piston 18 exercised, a corresponding pressure acts over the surface 19 at the opposite end of the piston 18 on the gel 17 in the hydrostatic chamber 16 , Through the gel 17 The pressure is hydrostatic on the deformable wall 13 forwarded to the first area of the drug container. This pressure causes the liquid contained in the container to pass through the nozzle 15 is ejected. That of a given force by acting on the piston 18 generated pressure is determined by the size of the surface 19 certainly. Through the stroke of the piston 18 in the hole 27 the displaced fluid volume, ie the volume of fluid injected, is determined. Therefore, by suitable choice of these parameters (size of the surface 19 , Stroke of the piston 18 ) achieve a desired injection behavior.
As will be described below by means of examples of specific embodiments, a preferred embodiment of a needleless injection system according to the invention additionally comprises the following means, which are described in US Pat 1 not shown:
- An activatable force generator, which creates a force and this force on the second end 21 of the piston 18 to cause that from the surface of the first end 19 of the piston 18 a corresponding pressure on the gel 17 is exercised, and
An activation means for activating the force generator.
A system with the in 1 For example, the structure shown has a jet nozzle 15 with a diameter of 0.2 mm. If on the flexible part of the medicine container through the gel 17 a pressure of, for example, 300 bar is exerted, one achieves a maximum flow of 7 microliters per millisecond with the injection system in one injection.
The exact structure of an injection system according to the invention is determined by the following experimental findings:
- The diameter of the opening 20 the jet nozzle 15 affects the penetration depth of the injected fluid. At a given pressure, a larger opening diameter results in a greater penetration depth. Diameters of openings for subcutaneous injection jets are typically in the range of 0.10 mm to 0.25 mm. The diameter of the opening 20 the jet nozzle 15 is 0.2 mm in the following examples.
The rate at which the pressure applied to the deformable medicament container increases with time is critical to achieving good injection performance. In order to achieve the necessary penetration depth, a rapid increase to the maximum pressure of the injection is required at the beginning. After the initial penetration, a lesser pressure is needed to administer the drug without unduly entering the soft subcutaneous tissue. An initial pressure rise to about 300 bar in less than a millisecond followed by a sustained pressure of 200 bar is typical for subcutaneous injections of 200 microliters through an orifice of the jet nozzle 15 with a diameter of 0.2 mm.
Generally speaking, the activatable force generator is designed and sized to be designed to apply the force applied to the piston 18 should be exercised with such a mechani make available that the corresponding to the transfer medium 17 applied pressure in a period of time, which is about 2 milliseconds or less, rises to a peak value and decreases after this period to a value which is smaller than the peak value.
As a power generator different energy storage including compressed springs or compressed gas can be used. In particular, each of the following energy stores can be used in the context of the present invention, for example to generate a force pulse of 50 milliseconds duration with a peak value of more than 200 watts:
- Pyrotechnic energy sources are ideal for delivering a short pulse of great power in a small space. They also have the advantage that the injection pressure can be generated directly, without an increase in pressure by means of a differential piston is required.
- Liquefied gases, such as CO2, are a safe and effective source of energy. Since the vapor pressure of CO2 at room temperature is less than 60 bar, this pressure must be intensified by means of a differential surface piston in order for the pressure required to effectively administer an injection to reach from 200 bar to 300 bar becomes. In principle, any low pressure source of pressurized gas or vapor may be used, for example acid bicarbonate reactions, low pressure nitrogen, fuel air combustion or low pressure pyrotechnics.
- Compressed gas at 300 bar and more is an effective energy source, with the directly required pressure can be achieved, provided suitable storage containers and devices for release are available.
- Rubber or plastic springs, especially certain rubber or plastic springs, store per unit mass compared to steel springs large amount of energy. The cost and behavior of such rubber or Kunststoffedern are favorable, provided long-term stability of their properties is ensured and with time only small voltage losses occur. Both manufacturer-biased and user-tensioned rubber or plastic springs may be used.
- Metal springs, especially certain steel springs, store a large amount of energy per unit mass. Both manufacturer-biased and user-tensioned metal springs may be used.
Electrochemical gas generation by dissociation of liquids, such as water, can be used to recover compressed gas. The advantage of such a process is that, with a small battery power over time, a pressure can be produced which is capable of producing by rapid release the pressure required to administer an injection.
Electromechanical energy sources, such as a DC motor powered, for example, with a nickel-cadmium battery, may be used to generate the force pulse required for beam injection.
The Choice of a suitable energy source for an injection system according to the invention depends on the given application. An electromechanical power source can in a hospital environment where size does not matter, appropriate and very inexpensive be while a spring or liquefied gas as energy sources for a disposable injection system more suitable for single use could be.
in the In general, an injection system according to the invention may vary depending on the intended use or requirements / needs the user with or without an energy source packed and to the Users are delivered.
At the in 1 illustrated embodiment is an injection system without energy source. Such a system is intended for use with a separate drive module, which may be, for example, a hand-operated spring device or an automatic device operated by gas or electricity.
in the The following will be specific examples of particular embodiments a needleless invention Injection system described which include an energy source. Such systems are primarily disposable disposable devices Use. Their integrated energy source can, for example, a Be a spring or a gas supply.
The 2 and 3 illustrate the structure and operation of a first embodiment of a device according to the invention. This first embodiment is essentially a one-way disposable device, one with LPG 34 working force generator includes.
As in 2 is shown in this embodiment in a reservoir 34a contained LPG 34 used to generate the force acting on a differential piston 18a should be exercised. The means for generating this force further include a gas outlet valve 33 and one trigger 32 for actuating, ie for opening the valve 33 , These components and a spring 47 are assembled and with the other components of the system through a housing 45 operably connected, which is designed to have a housing 23 of the basis of 1 to be pushed. The feather 47 serves to specify the value of the mechanical pressure that must be exercised with the system on the skin of a Patien th, so that the force generator by means of the shutter 32 can be activated. At the gas outlet valve 33 it is, for example, a breakable closure of an outlet opening of the gas reservoir 34 , In this case, the shutter is designed to operate when the shutter button is pressed 32 to break.
Before use, the various components of the injection system have the in 2 positions shown. The outlet of the jet nozzle 15 is with a tear-off closure flap 22 locked. The trigger 32 is with a guide slot in its position in the sliding housing 45 blocked. This lock will cause unintentional actuation of the trigger 32 prevented.
The preparation of the injection system for administering an injection includes the following steps:
- Remove the locking tab 22 to the opening 20 to open,
- Pressing the nose of the device to the skin of a patient, so that the housing 45 over a section of the housing 23 pushes and the housing in their in 3 get shown positions. Through this movement of the housing 45 relative to the housing 23 becomes the spring 47 compressed and the trigger 32 placed in a position in which he opens the valve 33 can be depressed so that gas 34 escape and pressure can build up on an end face 21 of the differential piston 18 acts.
Following the preparatory steps described above, you can press the shutter release button 32 be given an injection.
Will the valve 33 by pressing the shutter button 32 opened, that will be in the reservoir 34 contained gas through the valve 33 released. This gas evaporates, leaving itself on an end face 21a of the differential piston 18a Build up pressure. The movement of the piston 18a is caused by a shearing stop 31 prevents it until the pressure is high enough and exceeds a predetermined threshold. As soon as this happens, the shearable stop shears 31 from, so that the differential piston 18a suddenly released to the hydrostatic chamber 16 can move to a stamp 18c to apply and in this way to the in the hydrostatic chamber 16 contained gel 17 Exercise pressure. Remaining gas escapes through a vent 35 ,
By means of the differential piston 18a settles on the surface at its end 21a exerted gas pressure by a factor multiplied by the quotient of the surface of the end 21a and the surface of the end 19a of the piston 18a matches. This factor is greater than 1, since the surface of the end 21 larger than the surface of the end 19 is. In the in the 2 and 3 illustrated embodiment, the pressure through the differential piston 18 increased by a factor of about 6 to 1. Because the surface of the end 19a of the differential piston 18a on an equally large surface of the stamp 18c is the one on the hydrostatic gel 17 applied pressure equal to the product of the gas pressure and said factor.
In the in the 2 and 3 The embodiment shown is the initial increase of the gel 17 on the deformable wall 13 pressure exerted due to the impact pressure of the impact of the piston 18 on the stamp 18c is produced, especially high. This impact pressure arises because of the existence of a given gap 18b that is between the initial position of the end 19a of the piston 18a and the stamp 18c represents a free route.
In this way, a high hydrostatic pressure is generated which abruptly impacts the gel 17 acts. Under pressure, the gel exercises 17 in turn pressure on the deformable wall 13 of the medicine container 11 out. Thus, the sudden release of gas causes a rapid increase in the pressure exerted by the hydrostatic gel on the deformable wall 13 is exercised. This leads to the ejection of the liquid medicament contained therein 12 through the jet nozzle 15 of the insert 14 of the second area of the medicament container 11 ,
The 3 shows the configuration of in 2 illustrated embodiment after completion of the injection.
The 6 shows a schematic cross section of a modification of the in 2 shown embodiment. At this in 6 the modification shown comprises the piston 18m two parts: a first part 18d from a first material and a second part 18e of a second material, wherein the second material has a higher density than the first material. In the first part 18d For example, it is a metallic core part and the second part 18e for example, a peripheral part made of a plastic material. The purpose of the piston 18m with a heavier core part 18d out Consist, is the total mass of the piston 18m increase the force with which the piston 18m on the stamp 18c increases, thereby shortening the rise time of the pressure pulse applied to the gel 17 and thus on the squeezable wall 13 of the medicine container 11 is exercised.
The 4 and 5 illustrate the structure and operation of a second embodiment of a device according to the invention. This second embodiment is essentially a one-way disposable device that includes a force generator driven by a rubber spring system.
As 4 shows, in this embodiment, a rubber spring 37 used in the form of a sling to generate the force acting on a pestle 38 should be exercised. When the pestle 38 is displaced by a force caused by abruptly relaxing the spring 37 is generated beats a first end 40 of the plunger 38 on a piston 41 which then puts a corresponding pressure on that in the hydrostatic chamber 16 contained gel 17 exercises. The pestle 38 and the piston 41 practice a similar function as the piston in this way 18 at the top based on the 2 and 3 described embodiment.
The feather 37 is stretched during manufacture and in the in 4 Locked position shown locked. In this position, the spring practices 37 to the second end 42 of the plunger 38 a power out. In a modified embodiment, the spring 37 not tensioned in the factory and must therefore be brought by the user in the cocked position in 4 is shown.
That for the production of the rubber spring 37 The selected rubber material must have the following properties: high strength, high ductility and low loss over time. In a preferred embodiment, the tensioned spring 37 subjected in a production step, a thermal aging process, so that the shelf life of the device consistent characteristics are ensured.
By means of a trigger 36 The user may experience an abrupt release of the previously cocked spring 37 cause. For this purpose, the trigger includes 36 a ball lock 39 that is designed for the plunger 38 depending on the position of the trigger 36 withhold or release. The ball lock 39 prevents the plunger 38 moves as long as the trigger 36 is in a first position, the in 4 is shown. The ball lock 39 is designed and dimensioned so that it becomes unstable as soon as it is actuated by the trigger 36 in the in 5 shown position was brought. This property of the ball lock 39 make them suitable for the pestle 38 abruptly release and in this way an abrupt shift of the plunger 38 to be made possible by a force caused by relaxing the rubber spring 37 is produced. In this way there will be a rapid increase in the rate of the plunger 38 over the piston 41 on the gel 17 applied pressure and a correspondingly rapid increase of the gel 17 on the deformable wall 13 of the medicine container 11 applied pressure causes.
As 4 shows, the embodiment illustrated therein additionally comprises an inner housing 49 that mechanically with the housing 23 the pressure chamber is connected, an outer housing 46 , which is designed so that it over the inner housing 49 can be pushed, and a spring 48 between the inner casing 49 and the outer housing 46 is arranged. The feather 48 The purpose of this is to provide the value of the mechanical pressure that must be exerted on the skin of a patient by the system so that the force generator can be activated by means of the trigger 36 can be activated.
Before use, the various components of the injection system have the in 4 shown positions. The outlet opening of the jet nozzle 15 is by a tear-off closure flap 22 closed and by a removable cap 44 protected by the removal of the locking tab 22 is relieved. The removable cap 44 also serves to the outer housing 46 relative to the inner housing 49 to lock and prevents in this way accidental actuation of the shutter 36 ,
- Remove the cap 44 and the closure flap 22 to the opening 20 to open,
- Pressing the nose of the device to the skin of a patient, so that the outer housing 46 over a section of the inner housing 49 is pushed and the housings in their in 5 get shown positions. Through this movement of the housing 46 relative to the housing 49 becomes the spring 48 compressed and the trigger 36 placed in a position where he can be depressed to the ball lock 39 to release and in this way the plunger 38 to release abruptly.
Following the preparatory steps described above, you can press the shutter release button 36 be given an injection.
Will be the trigger 36 pressed after the just described preparation steps, gives the ball lock 39 the pestle 38 abruptly free, so that the rubber spring 37 can relax abruptly. This relaxation process causes the plunger 38 on the piston 41 bounces, then a hydrostatic gel pressure on the deformable wall 13 exercises so that the liquid drug contained therein 12 through the jet nozzle 15 of the insert 14 of the second area of the medicament container 11 is ejected.
In the in the 4 and 5 The embodiment shown is the initial increase of the gel 17 on the deformable wall 13 pressure applied due to the impact pressure of the impact of the plunger 38 on the piston 41 is produced, especially large. This impact pressure arises because of the existence of a given gap 40b that is between the initial position of the end 40 of the plunger 38 and the piston 41 represents a free route.
The 5 shows the configuration of in 4 shown embodiment after completion of an injection.
The 7 shows a schematic cross section of a modification of the first embodiment, which in 4 is shown.
At the in 7 illustrated modification includes the plunger 38m two parts: a first part 38a from a first material and a second part 38b of a second material, wherein the second material has a higher density than the first material. In the first part 38a For example, it is a metallic core part and the second part 38b for example, a peripheral part made of a plastic material. The purpose, the pestle 38 with a heavier core part 38 To equip, is the total mass of the plunger 38 increase the force with which the plunger 38 on the piston 41 hits, increasing and thus shortening the rise time of the pressure pulse applied to the gel 17 and thus on the squeezable wall 13 of the medicine container 11 is exercised.
deformable Wall of the first section of the medicine container
commitment the second area of the medicine container
Hydrostatic chamber
first piston
second Piston (differential piston)
Core part of the first piston 18m
Peripheral part of the first piston 18m
First end of the first piston 18
First end of the second piston 18a
Second end of the first piston 18
Second end of the second piston 18a
Tear-off closure flap
Housing of pressure chamber
Gummidichtug
poetry the closure insert
Montagekrimpung
shearable attack
LPG reservoir
Rubber spring loop
Core part of the plunger 38m
Peripheral part of the plunger 38m
first End of the pestle
Second end of the pestle 38
Even though a preferred embodiment of The invention has been described using specific terms this description is only illustrative Purposes and is understood to be changes and variations made can be without departing from the definitions of the following claims.
Needleless injection system for the subcutaneous injection of liquid drugs, comprising: (a) a medicament container ( 11 ) for storing a quantity of liquid to be injected ( 12 ) is formed and dimensioned, wherein the medicament container ( 11 ) a first area ( 13 ) and a second area ( 14 ), which are in fluid communication with each other, the first region ( 13 ) is deformable and the second area ( 14 ) at least one opening ( 15 . 20 ), characterized by (b) a hydrostatic chamber ( 16 ), which is a transfer medium ( 17 ) for transmitting hydrostatic pressure, the hydrostatic chamber ( 16 ) is designed and dimensioned such that the medicament container ( 11 ) at least partially in the hydrostatic chamber ( 16 ) and that one on the transfer medium ( 17 ) would cause the first area ( 13 ) of the medicament container ( 11 ) so deformed that in the medicament container ( 11 ) for the liquid drug ( 12 ) available volume, and (c) a first piston ( 18 ) with a first end ( 19 ) and a second end ( 21 ), which is the first end ( 19 ), the first end ( 19 ) a surface ( 19 ) designed to be placed in the hydrostatic chamber ( 16 ) transfer medium ( 17 ) To apply pressure.
An injection system for subcutaneous injection according to claim 1, additionally comprising (d) an activatable force generator with which a force ( 29 ) and generate this force ( 29 ) to the second end ( 21 ) of the first piston ( 18 ) in order to cause the surface ( 19 ) of the first end ( 19 ) of the first piston ( 18 ) a corresponding pressure on the transfer medium ( 17 ) and (e) activating means for activating the force generator.
An injection system for subcutaneous injection according to claim 2, wherein the activatable force generator is designed and dimensioned to be capable of controlling the force ( 29 ) with such a mechanical performance that the transfer to the transfer medium ( 17 ) pressure rises to a peak value over a period of time that is about 2 milliseconds or less and drops to a value less than the peak value after that period.
An injection system for subcutaneous injection according to claim 2, wherein the activatable force generator comprises a container ( 34a ) with LPG ( 34 ).
An injection system for subcutaneous injection according to claim 2, wherein the activatable force generator is a spring ( 47 . 48 ) as a force-generating element.
An injection system for subcutaneous injection according to claim 4, additionally comprising a second piston ( 18a ) designed to fit on the first piston ( 18 ) exert a force, and a shear-off component ( 31 ), which prevents the force generated by the force generator, a displacement of the second piston ( 18a ) as long as the force does not exceed a predetermined threshold, the 31 ) is designed and dimensioned so that it breaks off when the force reaches the predetermined threshold, which is an abrupt shift of the second piston ( 18a ) caused by the force generated by the force generator.
An injection system for subcutaneous injection according to claim 6, wherein the second piston ( 18a ) a first part ( 18d ) of a first material and a second part ( 18e ) of a second material, the second material having a higher density than the first material.
Injection system for subcutaneous injection according to claim 5, additionally comprising a plunger ( 38 ), which is designed to fit on the first piston ( 18 ) exert a force, and in which the activation means for activating the force generator, a ball lock ( 39 ), which prevents the plunger ( 38 ), as long as the force generator is not activated by the activation means, the ball lock ( 39 ) is designed and dimensioned so that it is unstable after being triggered, and in this way is designed to move the plunger ( 38 ) release abruptly and thus an abrupt shift of the tappet ( 38 ) caused by the force generated by the force generator.
An injection system for subcutaneous injection according to claim 8, wherein the plunger ( 38 ) has a first part of a first material and a second part of a second material, wherein the second material has a higher density than the first material.
Injection system for subcutaneous injection according to claim 1, in which the transfer medium ( 17 ) is a biocompatible material for transferring hydrostatic pressure, which flows well when exposed to a pressure of about 300 bar and which is substantially incompressible.
Injection system for subcutaneous injection according to claim 1, in which the transfer medium ( 17 ) is a gel for transmitting hydrostatic pressure.
Injection system for subcutaneous injection after Claim 11, wherein the gel is an elastomeric silicone gel.
Injection system for subcutaneous injection according to claim 1, in which the transfer medium ( 17 ) is a soft rubber for transmitting hydrostatic pressure.
Injection system for subcutaneous injection according to claim 1, in which the transfer medium ( 17 ) is a sterile saline solution for transmitting hydrostatic pressure.
DE2001611967 2000-02-16 2001-01-16 Needleless hypodermic injection system Expired - Fee Related DE60111967T2 (en)
US18295400P true 2000-02-16 2000-02-16
US182954P 2000-02-16
DE60111967D1 DE60111967D1 (en) 2005-08-25
DE60111967T2 true DE60111967T2 (en) 2006-04-20
ID=22670772
DE2001611967 Expired - Fee Related DE60111967T2 (en) 2000-02-16 2001-01-16 Needleless hypodermic injection system
US (1) US6440099B2 (en)
EP (1) EP1125593B1 (en)
JP (1) JP3420215B2 (en)
KR (1) KR100389189B1 (en)
CN (1) CN1308970A (en)
AR (1) AR027942A1 (en)
AT (1) AT299725T (en)
AU (1) AU743816B2 (en)
BR (1) BR0100561A (en)
CA (1) CA2331030A1 (en)
DE (1) DE60111967T2 (en)
ES (1) ES2245676T3 (en)
MX (1) MXPA01000560A (en)
ZA (1) ZA200100810B (en)
EP1596907A1 (en) * 2003-02-25 2005-11-23 F. Hoffmann-La Roche Ag Needleless hypodermic injection device with non-electric primer ignition means
WO2005058392A2 (en) 2003-12-18 2005-06-30 Novo Nordisk A/S Cartridge for delivery device
US20090005737A1 (en) * 2007-06-29 2009-01-01 Thomas Chun Auto-Injector
DK2442852T3 (en) * 2009-06-19 2013-07-29 Sanofi Aventis Deutschland Injection device for a liquid pharmaceutical
CA2923492A1 (en) 2013-09-09 2015-03-12 Lts Lohmann Therapie-Systeme Ag Needle-free subcutaneous administration of proteins
US10413671B2 (en) 2017-09-12 2019-09-17 Portal Instruments, Inc. Rotary motor based transdermal injection device
US993309A (en) * 1910-12-31 1911-05-23 Fred C Ellasser Joint for longitudinal members.
2001-01-10 CA CA 2331030 patent/CA2331030A1/en not_active Abandoned
2001-01-16 DE DE2001611967 patent/DE60111967T2/en not_active Expired - Fee Related
2001-01-16 EP EP20010810039 patent/EP1125593B1/en not_active Not-in-force
2001-01-16 ES ES01810039T patent/ES2245676T3/en active Active
2001-01-16 MX MXPA01000560 patent/MXPA01000560A/en not_active Application Discontinuation
2001-01-16 AT AT01810039T patent/AT299725T/en not_active IP Right Cessation
2001-01-18 KR KR20010002842A patent/KR100389189B1/en not_active IP Right Cessation
2001-01-29 ZA ZA200100810A patent/ZA200100810B/en unknown
2001-02-12 US US09/781,377 patent/US6440099B2/en not_active Expired - Fee Related
2001-02-13 AU AU19734/01A patent/AU743816B2/en not_active Ceased
2001-02-14 AR ARP010100658A patent/AR027942A1/en not_active Application Discontinuation
2001-02-15 CN CN 01104535 patent/CN1308970A/en not_active IP Right Cessation
2001-02-15 JP JP2001038226A patent/JP3420215B2/en not_active Expired - Fee Related
2001-02-15 BR BR0100561A patent/BR0100561A/en not_active IP Right Cessation
EP1125593A1 (en) 2001-08-22
ES2245676T3 (en) 2006-01-16
MXPA01000560A (en) 2002-06-04
KR100389189B1 (en) 2003-06-27
US20010031945A1 (en) 2001-10-18
CN1308970A (en) 2001-08-22
BR0100561A (en) 2001-10-09
AR027942A1 (en) 2003-04-16
AU743816B2 (en) 2002-02-07
DE60111967D1 (en) 2005-08-25
AT299725T (en) 2005-08-15
AU1973401A (en) 2001-09-06
JP3420215B2 (en) 2003-06-23
JP2001224684A (en) 2001-08-21
CA2331030A1 (en) 2001-08-16
US6440099B2 (en) 2002-08-27
KR20010082005A (en) 2001-08-29
ZA200100810B (en) 2001-08-16
EP1125593B1 (en) 2005-07-20
JP4004544B2 (en) 2007-11-07 Unit dose dosing device
EP1326662B1 (en) 2012-06-13 Wet/dry automatic injector assembly
JP3872429B2 (en) 2007-01-24 Compact structure needleless safety syringe