EP1365997A1 - Dispositif et procede pour la fabrication d'une seringue a usage medical - Google Patents

Dispositif et procede pour la fabrication d'une seringue a usage medical

Info

Publication number
EP1365997A1
EP1365997A1 EP02710041A EP02710041A EP1365997A1 EP 1365997 A1 EP1365997 A1 EP 1365997A1 EP 02710041 A EP02710041 A EP 02710041A EP 02710041 A EP02710041 A EP 02710041A EP 1365997 A1 EP1365997 A1 EP 1365997A1
Authority
EP
European Patent Office
Prior art keywords
syringe
laser beam
syringe body
joining zone
temperature
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP02710041A
Other languages
German (de)
English (en)
Inventor
Udo J. Vetter
Dieter H. Baumann
Jens Bliedtner
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Apotheker Vetter and Company Arzneimittel GmbH Ravensburg
Original Assignee
Apotheker Vetter and Company Arzneimittel GmbH Ravensburg
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Apotheker Vetter and Company Arzneimittel GmbH Ravensburg filed Critical Apotheker Vetter and Company Arzneimittel GmbH Ravensburg
Publication of EP1365997A1 publication Critical patent/EP1365997A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • C—CHEMISTRY; METALLURGY
    • C03—GLASS; MINERAL OR SLAG WOOL
    • C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
    • C03C23/00—Other surface treatment of glass not in the form of fibres or filaments
    • C03C23/0005—Other surface treatment of glass not in the form of fibres or filaments by irradiation
    • C03C23/0025—Other surface treatment of glass not in the form of fibres or filaments by irradiation by a laser beam
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K26/00—Working by laser beam, e.g. welding, cutting or boring
    • B23K26/02—Positioning or observing the workpiece, e.g. with respect to the point of impact; Aligning, aiming or focusing the laser beam
    • B23K26/06—Shaping the laser beam, e.g. by masks or multi-focusing
    • B23K26/073—Shaping the laser spot
    • B23K26/0734—Shaping the laser spot into an annular shape
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K26/00—Working by laser beam, e.g. welding, cutting or boring
    • B23K26/08—Devices involving relative movement between laser beam and workpiece
    • B23K26/082—Scanning systems, i.e. devices involving movement of the laser beam relative to the laser head
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B23—MACHINE TOOLS; METAL-WORKING NOT OTHERWISE PROVIDED FOR
    • B23K—SOLDERING OR UNSOLDERING; WELDING; CLADDING OR PLATING BY SOLDERING OR WELDING; CUTTING BY APPLYING HEAT LOCALLY, e.g. FLAME CUTTING; WORKING BY LASER BEAM
    • B23K26/00—Working by laser beam, e.g. welding, cutting or boring
    • B23K26/352—Working by laser beam, e.g. welding, cutting or boring for surface treatment
    • B23K26/354—Working by laser beam, e.g. welding, cutting or boring for surface treatment by melting
    • C—CHEMISTRY; METALLURGY
    • C03—GLASS; MINERAL OR SLAG WOOL
    • C03B—MANUFACTURE, SHAPING, OR SUPPLEMENTARY PROCESSES
    • C03B23/00—Re-forming shaped glass
    • C03B23/04—Re-forming tubes or rods
    • C03B23/043—Heating devices specially adapted for re-forming tubes or rods in general, e.g. burners
    • C—CHEMISTRY; METALLURGY
    • C03—GLASS; MINERAL OR SLAG WOOL
    • C03B—MANUFACTURE, SHAPING, OR SUPPLEMENTARY PROCESSES
    • C03B23/00—Re-forming shaped glass
    • C03B23/04—Re-forming tubes or rods
    • C03B23/09—Reshaping the ends, e.g. as grooves, threads or mouths
    • C03B23/099—Reshaping the ends, e.g. as grooves, threads or mouths by fusing, e.g. flame sealing
    • C—CHEMISTRY; METALLURGY
    • C03—GLASS; MINERAL OR SLAG WOOL
    • C03B—MANUFACTURE, SHAPING, OR SUPPLEMENTARY PROCESSES
    • C03B23/00—Re-forming shaped glass
    • C03B23/20—Uniting glass pieces by fusing without substantial reshaping
    • C03B23/207—Uniting glass rods, glass tubes, or hollow glassware
    • C—CHEMISTRY; METALLURGY
    • C03—GLASS; MINERAL OR SLAG WOOL
    • C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
    • C03C27/00—Joining pieces of glass to pieces of other inorganic material; Joining glass to glass other than by fusing
    • C03C27/02—Joining pieces of glass to pieces of other inorganic material; Joining glass to glass other than by fusing by fusing glass directly to metal
    • 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
    • A61M2207/00—Methods of manufacture, assembly or production
    • 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
    • A61M5/3129—Syringe barrels
    • 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
    • A61M5/32—Needles; Details of needles pertaining to their connection with syringe or hub; Accessories for bringing the needle into, or holding the needle on, the body; Devices for protection of needles
    • A61M5/34—Constructions for connecting the needle, e.g. to syringe nozzle or needle hub
    • A61M5/343—Connection of needle cannula to needle hub, or directly to syringe nozzle without a needle hub

Definitions

  • syringes serve to firmly connect the cannula to the main body of syringes.
  • Pre-filled syringes produced in this way form the majority of the primary packaging used for the parenteral application of injectables. They have a glass cylinder, referred to here as a syringe body, which is rolled out on one side to form a cone receiving the cannula and on the other side to form a special rolled edge.
  • a cannula which is preferably made of stainless steel, is firmly glued into the opening of the glass cylinder with the cone using a UV-sensitive adhesive.
  • a cannula protective cap which consists of an elastomer, preferably of latex-free natural rubber, is usually placed over the cannula. The cannula protection cap is firmly clamped onto the glass cone when it is put on. The syringe barrel is filled from the end opposite the cannula, which is then closed by a piston stopper that is preferably provided with a thread.
  • a plastic finger rest is attached to the glass cylinder by means of the rear rolled edge of the glass cylinder.
  • Gluing the cannula to the glass cylinder has some significant disadvantages: Occasionally, the gluing is insufficient, as too little adhesive is introduced into the joint gap between the cone and the cannula. This means that the cannula is not sufficiently fixed after the adhesive has hardened and can be pulled out of the cone. It can also happen that too much adhesive is placed in the joint gap. As a result, the excess adhesive runs down in the joint gap and finally flows into the proximal end of the channel lumen. This can lead to a complete closure of the cannula. Often, the cannula is not noticed until an attempt is made to inject the contents of the syringe.
  • Syringes are usually subjected to an autoclaving process, that is, a steam sterilization process, in order to kill any germs.
  • This process takes place in an autoclave for about 20 to 60 minutes at a temperature of 121 ° C and a pressure of 1.10 bar in the autoclave, depending on the product placed in the syringe barrel.
  • the syringe system can only be 100% pyrogen-free if the The pre-filled syringe is subjected to baked-on siliconization.
  • the inner surface of the syringe body is provided with silicone and the syringe is guided through a hot air tunnel, which is operated, for example, at a temperature of approx. 340 ° C.
  • this process step cannot be carried out with conventional UV-curing, pharmaceutically approved adhesives, since these are only heat-resistant up to a maximum temperature of approx. 150 ° C. At a higher temperature, you lose the strength acquired after curing.
  • a device which has the features mentioned in claim 1. It is characterized by a laser radiation source, which is used to generate a laser beam. It also includes a beam shaping and / or steering device. This serves to direct the laser beam onto the joining zone between the syringe body and the cannula and, if necessary, to adapt the beam geometry to a desired melting process. Finally, the device comprises a receiving device for holding and positioning the syringe body. Further configurations result from the remaining subclaims.
  • a method of the type mentioned which comprises the steps mentioned in claim 12 and is characterized in that the joining zone between a syringe body and a cannula is exposed to a laser beam, that the material of the syringe body in this area is at least partially melted and that this material is cooled to solidify the joining zone and to fix the cannula in the syringe body.
  • Figure 1 shows a device for manufacturing a
  • Figure 2 shows a device for manufacturing a syringe for medical purposes with a stationary syringe and a fixed laser beam
  • FIG. 3 shows a device for manufacturing a syringe for medical purposes with a rotating syringe and a fixed laser beam
  • FIG. 4 shows a diagram from which the basic temperature profile during the manufacture of a syringe is shown over time;
  • Figure 5 is a schematic diagram to illustrate the path of movement of the laser beam in the manufacture of a syringe for medical purposes
  • FIG. 6 shows a device for manufacturing a syringe for medical purposes with a stationary syringe and a stationary laser beam
  • FIG. 7 shows a further device for manufacturing a syringe for medical purposes with a stationary syringe and a fixed laser beam
  • FIG. 1 shows a first embodiment of a device for manufacturing a syringe for medical purposes.
  • the device 1 comprises a laser beam generating device 3, the basic structure of which is known in principle and which has a laser resonator with a corresponding supply unit. In the following, the device will be referred to as laser resonator 5.
  • the device 1 also has a beam steering device 7 with mirrors 8a and 8b, which ultimately serves to generate the laser beam 9 generated by the laser resonator 5 to point to a syringe 11, which comprises a syringe body 13 and a cannula 15.
  • the syringe 11 is held by a suitable holding device 17, which comprises a positioning device 19 and a holding mandrel 21 for holding the syringe body 13.
  • the scanner device 23 In the direction of the laser beam 9 emanating from the laser resonator 5, the scanner device 23 is followed by a focusing unit 37, which serves to focus the laser beam 9 on the joining zone between the cannula 15 and the syringe body 13.
  • An arrow 39 indicates that the xy movement of the laser beam 9 is so different from that Scanner device 23 causes the laser beam 9 here to follow a circular path in order to sweep over the joining zone 41.
  • the scanner device 23 is designed such that the laser beam 9 can follow any desired contour.
  • the holding device 17 in such a way that the holding mandrel 21 is set in rotation, so that the syringe 11 also rotates.
  • This rotational movement can be desired in addition to the movement of the laser beam 9 caused by the scanner device 23.
  • the scanner device 23 in such a way that the laser beam 9 is focused in a point or an area of the joining zone 41 and that the syringe 11 is then set in rotation in order to ultimately apply the laser beam 9 to align the entire joining zone 41.
  • the syringe 11 is at a standstill and that the laser beam 9 executes a movement in the region of the joining zone 41 with the aid of the scanner device 23.
  • the beam steering device 7 is designed such that the laser beam 9 is focused on the joining zone 41 and that the shape of the laser focus in the area of the joining zone can also be changed. It is therefore possible to create a round or oval laser spot in the area of the joining zone.
  • the laser beam 9 is not moved in the embodiment of the device 1 shown in FIG. 3.
  • the syringe 11 is rotated at a predetermined, desired rotational speed in order to uniformly apply the laser beam to the joining zone 41.
  • the syringe 11 can be pivoted more or less out of the horizontal position, so that the joining zone 41 is exposed to the laser beam more or less from the front. is struck.
  • the joining zone 41 can also be exposed to the laser beam from above or from the front. It is therefore possible to use the receiving device 17, as shown in FIG. 3, instead of the receiving devices shown in FIGS. 1 and 2. Both a fixed and a moving laser beam can be used.
  • the laser beam generating device 3 is designed such that the energy of the laser beam can be controlled in time.
  • the power of the laser beam generating device 3 is preferably controlled so that the joining zone 41 is heated further for a certain period of time.
  • the temperature during this reheating phase is significantly lower than during the connection process and preferably also lower than during the preheating phase.
  • the devices 1 described here are designed in such a way that the laser power, the geometry of the laser beam and the focus size and position can be set during the method for manufacturing the syringe.
  • the focusing unit 37 can be designed such that the geometry of the laser beam 9, that is to say the beam diameter and / or the shape of the laser point given in the joint zone 41, is also variable here ,
  • the device 1 and the method can be coordinated such that a desired temperature / time profile is set in the area of the joint zone 41. It is also possible to heat the syringe body 13 in adjacent areas in order to reduce material stress.
  • the temperature given in the joining zone 41 can be detected and evaluated with the aid of a temperature detection unit in order to control the laser beam generating device 3 accordingly and to set the desired temperature or the desired temperature profile.
  • Thermal cameras and / or pyrometers but also other temperature detection devices can be used as the temperature detection unit.
  • additional materials in particular glass solder, can also be introduced into the joining zone 41 during the manufacture of the syringe 11, on the one hand to close larger joining gaps and on the other hand to ensure a low-tension connection between the cannula 15 and the syringe body 13, which have very different expansion coefficients.
  • the method described here enables contactless manufacture of the syringe without the need for an adhesive. If only glass and metal are present in the joining zone 41, it is readily possible to subject the finished syringe 11 to baked-on siliconization and to introduce it into a hot-air tunnel which also has temperatures in the region of 340 ° C. The connection between the syringe body 13 and the cannula 15 can take place very quickly with the appropriate energy of the laser beam 9.
  • the simple structure of the devices 1 described in the figures also makes it possible to automate the manufacture of the syringe and to produce it efficiently in short cycle times.
  • the figure shows the temperature T given in the joining zone 41 over the time t. It can be seen that the joining zone 41 is first preheated. A preheating temperature is maintained over a certain period of time. Then, in a second period of time, by appropriately controlling the laser beam generating device 3, a higher temperature is set in the region of the joining zone 41 in order to ensure the actual connection between the syringe body 13 and the cannula 15. The joining zone 41 is then allowed to cool. It is then kept at a temperature below the melting temperature to relieve stress.
  • the preheating phase can be significantly longer than the preheating and connection phase; the post-heating temperature can also be below the preheating temperature.
  • the preheating temperature Tl is below the transformation temperature TG of the glass used in each case. It is preferably 50 to 100 K below TG.
  • the temperature T2 required for melting and for the joining process is above the transformation temperature TG, preferably approximately 50 to 100 K above this temperature.
  • the temperature T1 is maintained, for example, for a time range of approximately two to three seconds, the temperature T2 selected during the actual connection between the syringe body 13 and the cannula 15 is maintained for approximately one to two seconds, and the reheating temperature T3 for approximately three to five seconds , Thereafter, a more or less targeted cooling of the joining zone 41 can take place.
  • the transformation temperature TG is, for example, about 565 ° C.
  • the temperature in the region of the joining zone 41 is controlled, that is to say the level of the temperature and the duration of action of the temperature are adapted to the materials of the syringe and cannula.
  • Figure 5 shows purely schematically a syringe 11 from the front, namely the joining zone 41.
  • the syringe body 13 is shown and the inner ring is the cannula 15, the lumen of which is not shown here.
  • the path of movement of a light point formed by the laser beam 9 in the region of the joining zone 41 is represented by an arrow 49. It can be seen that the light spot generated by the laser beam is guided along a circular path. This can be achieved by means of a fixed light spot with a rotating syringe 11 or with a stationary syringe 11 with the aid of a scanner device 23.
  • FIG. 6 shows yet another embodiment of a device 1, which is used to manufacture a syringe 11 for medical purposes. Parts that have already been described with reference to the preceding figures are provided with the same reference numbers here, so that reference is made to the description above.
  • the laser beam device 7 is also stationary. It has a fixed, concave mirror 8, which focuses the laser beam 9 on the joining zone 41. It has already been stated above that protective gas 11 can be used in the manufacture of the syringe.
  • a chamber 51 is therefore provided, which is also possible in the exemplary embodiments described above, which is closed off by walls 53 arranged all around and by a base 55 and by a cover 57.
  • the cover is provided with an optical window 59 which is transparent to the laser beam 9 and which enables the laser beam 9 to freely access the joining zone 41.
  • the window is made of a special glass that does not have an absorbing effect, for example quartz glasses of various types, in particular those made of ZnESe, can be used.
  • Shielding gas is introduced into the chamber 51 in a suitable manner.
  • Two feed lines 61, 61 ' are provided here by way of example, which break through the walls 53 and via which, as indicated by arrows 63, 63', a protective gas is introduced.
  • a protective gas is introduced.
  • the receiving device 17 with a drive in order to set the syringe 11 in rotation.
  • the construction is particularly simple if the syringe is arranged in a stationary manner, as described.
  • the path of the laser beam is simplified compared to that explained with reference to FIG. 2. Only a single mirror 8 is required here in order to direct the laser beam 9 emerging from the laser beam generating device 3 via the processing head 43 onto the joining zone 41.
  • the receiving device 17, which holds the syringe 11, is also preferably configured here such that the syringe is arranged in a stationary manner while the joining zone 41 is acted upon by the laser beam 9. In principle, however, it is also conceivable to provide a drive unit that rotates the syringe 11.
  • an annular beam profile of the layer is preferably serstrahls 9 used.
  • this can be generated by using a special laser beam generating device, for example by a laser type that works in the TEMoi.
  • beam shaping elements for example diaphragms, can also be used. These are preferably cooled.
  • FIG. 8 shows again part of a device 1 for producing a syringe 11, which is held by a holding device 17.
  • An upside-down cone 67 the syringe of which lies in the region of the joining zone 41, indicates an annular distribution of the laser beam which serves to uniformly heat the joining zone 41 even when the syringe 11 is at a standstill.

Landscapes

  • Engineering & Computer Science (AREA)
  • Chemical & Material Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Optics & Photonics (AREA)
  • Materials Engineering (AREA)
  • Organic Chemistry (AREA)
  • Plasma & Fusion (AREA)
  • Mechanical Engineering (AREA)
  • General Chemical & Material Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Geochemistry & Mineralogy (AREA)
  • Toxicology (AREA)
  • Health & Medical Sciences (AREA)
  • Ceramic Engineering (AREA)
  • Infusion, Injection, And Reservoir Apparatuses (AREA)

Abstract

L'invention concerne un dispositif pour la fabrication d'une seringue à usage médical, comprenant un corps de seringue en verre et une canule. Le dispositif selon l'invention est caractérisé par un dispositif générateur de rayon laser (3) pourvu d'un résonateur laser (5) servant à générer un rayon laser (9), par un dispositif de mise en forme et de guidage de rayon (7), ainsi que par un dispositif de réception (17) servant à fixer et à positionner le corps de seringue (13).
EP02710041A 2001-02-19 2002-01-25 Dispositif et procede pour la fabrication d'une seringue a usage medical Withdrawn EP1365997A1 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
DE10108958 2001-02-19
DE10108958A DE10108958A1 (de) 2001-02-19 2001-02-19 Vorrichtung und Verfahren zur Fertigstellung einer Spritze für medizinische Zwecke
PCT/EP2002/000840 WO2002066387A1 (fr) 2001-02-19 2002-01-25 Dispositif et procede pour la fabrication d'une seringue a usage medical

Publications (1)

Publication Number Publication Date
EP1365997A1 true EP1365997A1 (fr) 2003-12-03

Family

ID=7675369

Family Applications (1)

Application Number Title Priority Date Filing Date
EP02710041A Withdrawn EP1365997A1 (fr) 2001-02-19 2002-01-25 Dispositif et procede pour la fabrication d'une seringue a usage medical

Country Status (6)

Country Link
US (1) US20040065116A1 (fr)
EP (1) EP1365997A1 (fr)
JP (1) JP2004517707A (fr)
CA (1) CA2437975A1 (fr)
DE (1) DE10108958A1 (fr)
WO (1) WO2002066387A1 (fr)

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WO2006039705A2 (fr) 2004-09-30 2006-04-13 Becton, Dickinson And Company Procede permettant de reduire ou d'eliminer des residus dans un contenant en verre et contenant en verre ainsi obtenu
DE102007037565A1 (de) 2007-08-09 2009-02-12 Mglas Ag Spritzenkörper und Verfahren zur Herstellung eines Spritzenkörpers
DE102010045095B4 (de) * 2010-09-13 2015-01-08 Schott Ag Spritzenkörper-Kanülen-Verbund und Verfahren zu dessen Herstellung
DE102010045094B4 (de) * 2010-09-13 2013-03-07 Schott Ag Verfahren und Vorrichtung zur lasergestützten Glasformung
EP3560535A1 (fr) * 2011-04-15 2019-10-30 W. L. Gore & Associates, Inc. Procédé de réduction de la friction entre des composants de seringue
DE102012109967A1 (de) * 2012-10-18 2014-03-06 Schott Ag Verfahren zur Herstellung eines Spritzenkörper-Kanülen-Verbundes, sowie verfahrensgemäß hergestellter Spritzenkörper mit integrierter Kanüle
EP2992917B1 (fr) * 2013-05-02 2018-08-08 Terumo Kabushiki Kaisha Cylindre extérieur à aiguille et son procédé de production
DE102016205930A1 (de) * 2016-04-08 2017-10-12 Siemens Aktiengesellschaft Umschmelzen mit gleichzeitiger Erzeugung einer Druckringzone
DE102016114104A1 (de) 2016-07-29 2018-02-01 Schott Ag Verfahren zur lasergestützen Umformung von Glaskörpern
EP3431123B1 (fr) * 2017-07-18 2020-09-23 Gerresheimer Regensburg GmbH Procédé de fabrication d'une seringue comprenant un moyen de perçage
DE102023000991A1 (de) 2023-03-14 2024-09-19 Daniel Gruber Verfahren zur Herstellung von Glasspritzen mit einer eingeformten Kanüle

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US3383491A (en) * 1964-05-05 1968-05-14 Hrand M. Muncheryan Laser welding machine
DE1796038A1 (de) * 1967-09-01 1972-02-17 Comp Generale Electricite Verfahren zum Verschweissen von Werkstoffen mit Glas oder aehnlichen Stoffen
DE1771405B1 (de) * 1968-05-18 1971-01-14 Battelle Institut E V Herstellung von Quarzglas
JPS5590426A (en) * 1978-12-26 1980-07-09 Canon Inc Forming method for nozzle
GB2105320B (en) * 1981-09-07 1984-08-01 Burgess Limited Edwin Method of and apparatus for sealing pressurised ampoules
US4578558A (en) * 1984-01-23 1986-03-25 Clegg John E Laser means and method
US5607401A (en) * 1991-09-03 1997-03-04 Humphrey; Bruce H. Augmented polymeric hypodermic devices
US5427825A (en) * 1993-02-09 1995-06-27 Rutgers, The State University Localized surface glazing of ceramic articles
US5695465A (en) * 1995-07-24 1997-12-09 Zhu; Jinyou Syringe containing drug to be injected
DE19609199A1 (de) * 1996-03-09 1997-09-11 Vetter & Co Apotheker Verfahren zur Bearbeitung von Werkstücken aus festen Materialien sowie Vorrichtung zur Durchführung des Verfahrens
DE19700518C2 (de) * 1997-01-09 2000-03-16 Fraunhofer Ges Forschung Vorrichtung und Verfahren zum Verformen von thermoplastischen Material zum Verbinden zweier Bauteile

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Also Published As

Publication number Publication date
US20040065116A1 (en) 2004-04-08
DE10108958A1 (de) 2002-09-12
JP2004517707A (ja) 2004-06-17
WO2002066387A1 (fr) 2002-08-29
CA2437975A1 (fr) 2002-08-29

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