GB2094628A - Infusion apparatus - Google Patents
Infusion apparatus Download PDFInfo
- Publication number
- GB2094628A GB2094628A GB8107468A GB8107468A GB2094628A GB 2094628 A GB2094628 A GB 2094628A GB 8107468 A GB8107468 A GB 8107468A GB 8107468 A GB8107468 A GB 8107468A GB 2094628 A GB2094628 A GB 2094628A
- Authority
- GB
- United Kingdom
- Prior art keywords
- ratchet
- wheel
- plunger
- infusion apparatus
- lead screw
- 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- Withdrawn
Links
Classifications
-
- 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
- A61M5/1456—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons with a replaceable reservoir comprising a piston rod to be moved into the reservoir, e.g. the piston rod is part of the removable reservoir
-
- 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
- A61M2005/14506—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons mechanically driven, e.g. spring or clockwork
Abstract
An automatic infuser has a syringe (21) with plunger (12) which is depressed by a device mechanism (17) rotating a lead screw (13) to act on a nut (14) bearing on the plunger. The mechanism (17) has a ratchet wheel (24) co-operating with a pawl (25) actuated by a solenoid (18) so that each energising of the solenoid produces a corresponding indexed rotation of the ratchet. An electric circuit delivers energising pulses to the solenoid at a rate selected to provide a desired rate of delivery of medication from the syringe. <IMAGE>
Description
SPECIFICATION
Infusion apparatus
The present invention is concerned with infusion apparatus for delivering liquid medication by injection at predetermined dose rates. For chronic diseases or ailments, it is often necessary to deliver regular doses of medication by injection.
For example, diabetics require regular doses of insulin to control the disease. With usual handoperated syringes, relatively large doses of medication are injected at intervals of typically several hours. However, this technique causes the level of medication in the patient to vary very considerably between a high level shortly after an injection and a low level just before the next dose is due. It has been known for some time that it would be preferable to deliver medication substantially continuously to the patient at a predetermined dose rate selected to maintain the desired level of medication in the patient's bloodstream. This continuous regime enables more efficient use of the medication and reduction of the total dosage, as well as providing an improved control ofthe disease.
Infusion apparatus are known for continuous delivery of medication by a needle or catheter placed subcutaneously or in a vein of the patient. Hitherto, such infusion apparatus has often been rather bulky and therefore not suitable to be carried continuously by, for example, a diabetic having an otherwise substantially normal day-to-day life.
According to the present invention infusion apparatus for delivering liquid medication by injection at predetermined dose rates, comprises a syringe having a plunger which can be depressed to discharge medication from the syringe for delivery to a patient, an electronic circuit arranged to produce successive voltage pulses at predetermined regular intervals, a drive mechanism operable to depress the plunger and including a ratchet-wheel and pawl assembly whereby rotation of the ratchet-wheel effects depression of the plunger, and a solenoid connected to the pawl and arranged to be energised by the voltage pulses to produce corresponding actuations of the pawl and thus corresponding incremental rotational movements of the ratchet wheel.With this arrangement, each voltage pulse from the electronic circuit produces a corresponding single incremental rotational movement of the ratchet-wheel and thus a corresponding small depression of the plunger of the syringe. The drive mechanism, with the ratchet-wheel and pawl assembly can be arranged so that each voltage pulse produces a very minute dosage delivery of medication to a patient. it can be seen then that the rate of production of voltage pulses by the electronic circuit is directly related to the rate of delivery of medication and it is a relatively simple matter to control the voltage pulse rate and thus the medication dose rate.
The electronic circuit preferably includes control means for adjusting the rate of said voltage pulses.
Preferably also the control means includes two adjustable pulse rate controls for providing two corresponding preset pulse rates, and a selection switch operable to produce a selected one of said preset pulse rates. With this arrangement the apparatus can be preset for two pulse rates and either one of these preset pulse rates selected as required to give a corresponding different dose rate. This is very convenient in any applications where different dose rates of medication are required at different times of day, for example, during the daytime and during the night-time. For diabetics, it is common for the nighttime basal dose rate to be lower than the daytime rate.
Preferably also said control means includes booster dose initiate means and means responsive thereto to produce a predetermined number of voltage pulses at a high rate less than the maximum response rate of the solenoid and the ratchet-wheel and pawl assembly to effect a corresponding predetermined angular rotation of the ratchet-wheel.
With this arrangement a booster dose of medication can be delivered on operation of the initiate means.
This results in the production of a preset number of voltage pulses corresponding to a preset dose or bolus which is delivered substantially immediately by depression of the plunger of the syringe. The rate of production of the voltage pulses to produce the bolus should be much higher than the normal rate for basal delivery but it will be appreciated that it is importantthatthe solenoid and ratchet-wheel and pawl assembly should be capable of responding to the high pulse rate.
It is often necessary for such booster doses to be delivered over and above the normal basal dosage rate. For example, for diabetics, a booster of insulin is usually required just before eating to cope with the usual rise in blood sugars resulting from digestion of food.
Preferably said means responsive to the booster dose initiate means include booster dose control means adjustable to select said predetermined number of voltage pulses and thus the size of the booster dose discharged.
In one arrangement, the drive mechanism comprises a lead screw rotatably mounted to extend substantially parallel with the plunger and driven by the ratchet-wheel, and a nut engaging the lead screw and connected to the plunger whereby on operation of the apparatus the nut is driven along the lead screw and depresses the plunger. The ratchet-wheel may drive the lead screw via a worm gear. Instead the ratchet-wheel may drive the lead screw via a reduction gear train.
Examples of the present invention will be described with reference to the accompanying drawings in which:
FIGURE 1 is a schematic diagram of an infusion apparatus embodying the present invention;
FIGURE 2 is a view along arrow X of FIGURE 1 of a ratchet-wheel and pawl assembly driving a worm gear for depressing the plunger of the syringe of the
apparatus of FIGURE 1;
FIGURE 3 is a view of the ratchet-wheel and pawl
assembly along arrow Y of FIGURE 2;
FIGURE 4 is an enlarged view of an alternative drive mechanism for depressing the plunger, emp
loying a reduction gear train; and
FIGURE 5 is a block schematic diagram of the electronic circuit for generating voltage pulses to energise the solenoid of the apparatus.
In FIGURE 1, a complete insulin infusion pump is illustrated contained in a casing 10. A syringe 11 having a plunger 12 is mounted in the casing 10. The syringe and plunger may be of a type commonly available for delivering injections manually. An elongate lead screw 13 is rotatably mounted and extends substantially parallel to the length of the plunger 12. A nut assembly 14 engages the lead screw 13 and engages the head 15 of the plunger 12 so that when the lead screw 13 is rotated to drive the nut 14 along the screw in the direction of the arrow 16 the nut 14 depresses the plunger 12 into the barrel of the syringe 11. Preferably, the nut 14 is arranged to be readily disengagable from the head 15 of the plunger 12 so that the entire syringe 11 can be easily removed from the casing 10 for disposal or refilling.
The lead screw 13 is rotated by a drive mechanism indicated generally at 17 which is actuated via a ratchet-wheel and pawl assembly by a solenoid 18.
The solenoid 18 is itself energised by voltage pulses from an electronic circuit housed in the casing 10 beneath a control panel 19. A battery 20 also housed in the casing 10 delivers electric energy to power the
electronic circuit.
A lid would normally completely enclose the con
tents of the casing 10 but is removed in FIGURE 1.
The lid may have a transparent window, as indicated
by the rectangle 21 in FIGURE 1, located over the
barrel of the syringe 11 so that the amount of medi
cation left in the syringe can readily be inspected.
Referring to FIGURES 2 and 3, the drive mechan
ism for the lead screw 13 is illustrated in more detail.
The lead screw 13 is driven by a pinion 22 which is
itself driven by a worm gear 23. The worm gear 23 is
itself in turn driven by a ratchet-wheel 24 which is engaged by a pawl 25 actuated by the solenoid 18.
As shown in FIGURE 31, the pawl 25 is rotatably mounted on a bracket 26 and is spring-loaded into a position engaging the teeth of the tarchet-wheel 24.
The bracket 26 is itself mounted to be rotatable about the axis 27 of the ratchet-wheel 24 and is jour nalled at 28 to the movable core 29 of the solenoid 18. A non-return pawl 30 is also mounted on the casing of the drive mechanism to engage the ratchet-wheel 24to prevent reverse movement of the wheel corresponding to withdrawal of the plunger 12. On each occasion, the solenoid 18 is energised by a voltage pulse from the electronic circuit, the core 29 is withdrawn into the windings of the solenoid 18 rotating the bracket 26 about the axis 27 in an anti-clockwise direction in FIGURE 3. The pawl 25 engages a tooth of the ratchet-wheel 24 and produces a corresponding angular movement of the
ratchet-wheel.When the solid 18 is subsequently
de-energised, the core 29 returns to the original
extended position and the pawl 25 is displaced against its spring-loading slide over the teeth of the ratchet-wheel 24 which is prevented from rotating back again by the pawl 30. It can be seen therefore that each voltage pulse energising the solenoid 18 produces a predetermined incremental rotation of the ratchet-wheel which in turn, via the worm gear 23 and pinion wheel 22 produces a very small incremental rotation of the lead screw 13 and thus depression of the plunger 12.
FIGURE 4 illustrates an alternative drive mechanism to that shown in FIGURES 1 to 3. In FIGURE 4, a reduction gear train comprising pinion wheels 31,32 and 33, interconnects a ratchet-wheel 34 and the lead screw 13. A solenoid 35 is connected to a pawl 36 which is biased by a spring 37 to engage the teeth of the ratchet-wheel 34. A non-return pawl 38 is also spring-biased to engage the teeth of the ratchetwheel and prevent the reverse rotation of the wheel.
On energising the solenoid 35, the pawl 36 is moved in the direction of the arrow 39 by an amount corresponding to the throw 40 of the solenoid 35. In the illustrated example, the throw 40 is arranged to correspond to the spacing between an adjacent pair of the teeth 41 on the ratchet-wheel 34, so that each voltage pulse is delivered to energise the solenoid 35 causes the pawl 36 to index the ratchet-wheel 34 by one tooth 41. The incremental rotation of the ratchet-wheel 34 is then reduced and delivered to the lead screw to depress the syringe plunger.
FIGURE 5 illustrates in block schematic form the electronic circuit for producing and delivering voltage pulses to energise the solenoid 18 or 35. The solenoid is indicated in FIGURE 5 by a block 45 and is supplied by voltage pulses from a pulse-shaper 46. A battery 47, which may be a commonly available battery, for example, 9V, for use with transistor radios etc. powers the electronic circuit, including a crystal oscillator 48 which supplies output pulses on a line 49 at a relatively high rate. A switch 50 (see also
FIGURE 1) can be manually operated to supply the oscillator output pulses to one of two dividers 51 and 52. Each of dividers 51 and 52 is programmable by means of a manual control 53, 54 (see also FIGURE 1) to set the divider to produce output pulses on lines 55 and 56 at a desired rate to energise the solenoid 45 to produce desired dosage rates.
The lines 55 and 56 feed the output pulses from the dividers 51 and 52 to the pulse-shaper 46 for delivery to the solenoid 45.
In this way, one of the dividers 57 can be preset by its control 53 to produce pulses on the line 55 and thus to the solenoid 45 at a rate predetermined to provide a desired daytime basal dosage rate. On the other hand, the other divider 52 can be set by its control 54 to produce pulses to provide a night-time basal dosage rate. Then, the user of the infusion pump simply has to operate the switch 50 to change overfrom daytime to night-time basal rates.
The oscillator48 also provides output pulses on a line 57 via a push button switch 58 (see also FIGURE 1) to a third divider 59. Operation of the push button switch 58 triggers the divider 59 to produce on an output line 60 a predetermined number of voltage pulses. These voltage pulses are supplied on the line 60 also to energise the solenoid 45. The rate of pulses from the divider 59 is much higher than the pulse rates from the dividers 51 and 52 but is less than the maximum response rate of the solenoid 45 and the drive mechanism connected thereto. It can be seen therefore that operation of the press button 58 causes a predetermined number of actuations of the solenoid 45 thereby producing a predetermined rotation of the ratchet-wheel and the lead screw, and thus delivery of a predetermined dose of medication from the syringe 11.The entire dose determined by the predetermined number of pulses is delivered in a relativelyshorttime, i.e. in no more than afew minutes, and provides a bolus dose. Such bolus dosage of insulin is usually required prior to mealtimes. The size of the bolus can be selected by a manual control 61 (see also FIGURE 1) which is arranged to determined the number of voltage pulses produced by the divider 59 in response to pressing of the push button 58.
Also illustrated in FIGURE 5, there is an indicator light 62, typically an LED which is arranged to flash on at each voltage pulse delivered to the solenoid 45.
This enables the user to check that the pump is functioning correctly. A low battery indicator 63 may also be provided to illuminate a warning light 64 if the voltage of the battery 47 is declining.
It can be seen thatthe pump described above enables separate daytime and night-time basal rates to be readily set and selected as required, and also a predetermined bolus dose to be provided on demand.
It will be appreciated that the actual electronic design of the circuit illustrated in FIGURE 5 may vary from that shown. This design should present little problem to a person experienced in the field of electronics.
In one example of the invention, the drive mechanism, syringe size and medication concentration is arranged so that one unit of medication is delivered by 900 pulses of the solenoid 45. It can be seen then that a pulse rate from the dividers 51 or 52 of, say 1 pulse per 2 secs. corresponds to a dose rate of 2 units per hourwhereas 1 pulse every twenty seconds corresponds to 0.2 units per hour. The divider 59 may be arranged to generate pulses on the line 60 in 900 pulse lots each lot corresponding to one unit bolus. Then the control 61 may control the number of 900-pulse lots, i.e. the number of units bolus delivered by the pump.
Instead of delivering bolus doses electronically as described in the above example, a milled knob may be provided at one end of the lead screw extending through a hole in the casing 10. The bolus can then be delivered by turning the knob manually a predetermined angular amount. The knob may have an indexing mechanism providing an audible click and notchy feel to enable a known dose to be delivered by turning a predetermined number of clicks. A clutch mechanism is provided between the lead screw and the gear drive from the solenoid to enable the lead screw to be turned by the knob without transmitting the action to the gears.
Electronic check circuitry may also be provided for verifying that an electronic pulse is followed by a corresponding mechanical movement. This would enable the user to be warned of a jamming syringe, a blocked line, a malfunction, the plunger reaching the end of the syringe or a mechanical failure.
Claims (9)
1. Infusion apparatus for delivering liquid medication by injection at predetermined dose rates, comprising a syringe having a plunger which can be depressed to discharge medication from the syringe for delivery to a patient, an electronic circuit arranged to produce successive voltage pulses at predetermined regular intervals, a drive mechanism operable to depress the plunger and including a ratchet-wheel and pawl assembly whereby rotation of the ratchet-wheel effects depression of the plunger, and a solenoid connected to the pawl and arranged to be energised by the voltage pulses to produce corresponding actuations of the pawl and thus corresponding incremental rotational movements of the ratchet-wheel.
2. Infusion apparatus as claimed in claim 1 wherein the electronic circuit includes control means for adjusting the rate of said voltage pulses.
3. Infusion apparatus as claimed in claim 2 wherein said control means includes two adjustable pulse rate controls for providing two corresponding preset pulse rates and a selection switch operable to produce a selected one of said preset pulse rates.
4. Infusion apparatus as claimed in claim 2 or claim 3 wherein said control means includes booster dose initiate means and means responsive thereto to produce a predetermined number of voltage pulses at a high rate less than the maximum response rate of the solenoid and the ratchet-wheel and pawl assembly to effect a corresponding predetermined angular rotation of the ratchet-wheel.
5. Infusion apparatus as claimed in claim 4 wherein said means responsive to the booster dose initiate means includes booster dose control means adjustable to select said predetermined number of voltage pulses and thus the size of the booster dose discharged.
6. Infusion apparatus as claimed in any preceding claim wherein the drive mechanism comprises a lead screw rotatably mounted to extend substantially parallel with the plunger and driven by the ratchet-wheel, and a nut assembly engaging the lead screw and connected to the plunger whereby on operation of the apparatus the nut is driven along the lead screw and depresses the plunger.
7. Infusion apparatus as claimed in claim 6 wherein the ratchet-wheel drives the lead screw via a worm gear.
8. Infusion apparatus as claimed in claim 6 wherein the ratchet-wheel drives the lead screw via a reduction gear train.
9. Infusion apparatus substantially as hereinbefore described with reference to and as illustrated in the accompanying drawings.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| GB8107468A GB2094628A (en) | 1981-03-10 | 1981-03-10 | Infusion apparatus |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| GB8107468A GB2094628A (en) | 1981-03-10 | 1981-03-10 | Infusion apparatus |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| GB2094628A true GB2094628A (en) | 1982-09-22 |
Family
ID=10520275
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| GB8107468A Withdrawn GB2094628A (en) | 1981-03-10 | 1981-03-10 | Infusion apparatus |
Country Status (1)
| Country | Link |
|---|---|
| GB (1) | GB2094628A (en) |
Cited By (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0143895A1 (en) * | 1983-09-07 | 1985-06-12 | Disetronic Ag | Portable infusion apparatus |
| GB2153445A (en) * | 1984-01-25 | 1985-08-21 | Fernandez Tresguerres Hernande | Delivery and dosage device |
| FR2572288A1 (en) * | 1984-10-26 | 1986-05-02 | Infors Gmbh | INFUSION PUMP |
| EP0212225A1 (en) * | 1985-07-24 | 1987-03-04 | Karl Storz GmbH & Co. | Device for the control of an encased probe of an endoscopy apparatus |
| FR2600538A1 (en) * | 1986-06-27 | 1987-12-31 | Cassimatis Jean | Portable injector |
| EP0317808A2 (en) * | 1987-11-22 | 1989-05-31 | Fresenius AG | Pump for infusion seringes |
| EP0390388A2 (en) * | 1989-03-28 | 1990-10-03 | The BOC Group plc | Improvements in infusion pumps |
| EP0767641A1 (en) * | 1995-02-28 | 1997-04-16 | PHOTOGENESIS Incorporated | Medical linear actuator for surgical delivery, manipulation, and extraction |
| WO1997036623A1 (en) * | 1996-03-30 | 1997-10-09 | Peter Jeffrey | Materials delivery device |
| US5997501A (en) * | 1993-11-18 | 1999-12-07 | Elan Corporation, Plc | Intradermal drug delivery device |
| WO2002051473A1 (en) * | 2000-12-22 | 2002-07-04 | Dca Design International Limited | Dosing means for an injection device |
| EP1374932A2 (en) * | 2002-06-20 | 2004-01-02 | B. Braun Melsungen Ag | Syringe pump |
| USD743802S1 (en) * | 2013-07-29 | 2015-11-24 | Welch Foods Inc., A Cooperative | Beverage bottle |
-
1981
- 1981-03-10 GB GB8107468A patent/GB2094628A/en not_active Withdrawn
Cited By (25)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0143895A1 (en) * | 1983-09-07 | 1985-06-12 | Disetronic Ag | Portable infusion apparatus |
| GB2153445A (en) * | 1984-01-25 | 1985-08-21 | Fernandez Tresguerres Hernande | Delivery and dosage device |
| FR2572288A1 (en) * | 1984-10-26 | 1986-05-02 | Infors Gmbh | INFUSION PUMP |
| EP0212225A1 (en) * | 1985-07-24 | 1987-03-04 | Karl Storz GmbH & Co. | Device for the control of an encased probe of an endoscopy apparatus |
| FR2600538A1 (en) * | 1986-06-27 | 1987-12-31 | Cassimatis Jean | Portable injector |
| EP0317808A2 (en) * | 1987-11-22 | 1989-05-31 | Fresenius AG | Pump for infusion seringes |
| EP0317808A3 (en) * | 1987-11-22 | 1989-09-13 | Fresenius Ag | Pump for infusion seringes |
| EP0390388A2 (en) * | 1989-03-28 | 1990-10-03 | The BOC Group plc | Improvements in infusion pumps |
| EP0390388A3 (en) * | 1989-03-28 | 1991-09-11 | The BOC Group plc | Improvements in infusion pumps |
| US5997501A (en) * | 1993-11-18 | 1999-12-07 | Elan Corporation, Plc | Intradermal drug delivery device |
| EP0767641A4 (en) * | 1995-02-28 | 2000-03-01 | Photogenesis Inc | Medical linear actuator for surgical delivery, manipulation, and extraction |
| EP0767641A1 (en) * | 1995-02-28 | 1997-04-16 | PHOTOGENESIS Incorporated | Medical linear actuator for surgical delivery, manipulation, and extraction |
| WO1997036623A1 (en) * | 1996-03-30 | 1997-10-09 | Peter Jeffrey | Materials delivery device |
| CN100400117C (en) * | 2000-12-22 | 2008-07-09 | Dca设计国际有限公司 | Medicament metering device for injecting device |
| US6949082B2 (en) | 2000-12-22 | 2005-09-27 | Lea Design International Limited | Dosing means for an injection device |
| US7052484B2 (en) | 2000-12-22 | 2006-05-30 | Robert Frederick Veasey | Drive mechanism for an injection device |
| WO2002051473A1 (en) * | 2000-12-22 | 2002-07-04 | Dca Design International Limited | Dosing means for an injection device |
| AU2007202032B2 (en) * | 2000-12-22 | 2009-11-05 | Dca Design International Limited. | Dosing means for an injection device. |
| US7699815B2 (en) | 2000-12-22 | 2010-04-20 | Dca Design International Limited | Drive mechanism for an injection device |
| US8926553B2 (en) | 2000-12-22 | 2015-01-06 | Christopher Nigel Langley | Pen-type injector having an electronic control unit |
| EP1374932A2 (en) * | 2002-06-20 | 2004-01-02 | B. Braun Melsungen Ag | Syringe pump |
| EP1374932A3 (en) * | 2002-06-20 | 2004-04-07 | B. Braun Melsungen Ag | Syringe pump |
| CN100379468C (en) * | 2002-06-20 | 2008-04-09 | B·布朗·梅尔松根有限公司 | Injective pump |
| AU2003204472B2 (en) * | 2002-06-20 | 2008-05-29 | B Braun Melsungen Ag | A syringe pump |
| USD743802S1 (en) * | 2013-07-29 | 2015-11-24 | Welch Foods Inc., A Cooperative | Beverage bottle |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| WAP | Application withdrawn, taken to be withdrawn or refused ** after publication under section 16(1) |