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WO1980001459A1 - Systeme d'injection autonome - Google Patents

Systeme d'injection autonome Download PDF

Info

Publication number
WO1980001459A1
WO1980001459A1 PCT/US1979/000013 US7900013W WO8001459A1 WO 1980001459 A1 WO1980001459 A1 WO 1980001459A1 US 7900013 W US7900013 W US 7900013W WO 8001459 A1 WO8001459 A1 WO 8001459A1
Authority
WO
WIPO (PCT)
Prior art keywords
fluid
piston
patient
time
prescribed
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.)
Ceased
Application number
PCT/US1979/000013
Other languages
English (en)
Inventor
D Whitney
J Martin
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.)
Individual
Original Assignee
Individual
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 Individual filed Critical Individual
Priority to JP50139479A priority Critical patent/JPS56500119A/ja
Priority to DE19792953494 priority patent/DE2953494A1/de
Priority to GB8028796A priority patent/GB2050843B/en
Priority to PCT/US1979/000013 priority patent/WO1980001459A1/fr
Publication of WO1980001459A1 publication Critical patent/WO1980001459A1/fr
Priority to EP19790901050 priority patent/EP0022776A4/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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
    • A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body

Definitions

  • This invention relates generally to devices for dis ⁇ pensing or injecting a fluid at a controlled rate and more particularly to a device for use in the medical field to inject fluids into the body of a patient at a slow rate over a prolonged period of time.
  • fluids such as liquid medicaments into the body of the patient, whether human or animal, at a relatively slow rate over a prolonged period of time.
  • Several varieties of medical treatments such as chemotherapy, pre- and post- surgery treatments for the prevention of blood clotting, various nutrient treatments, various antibiotic treatments and treatment of certain other diseases generally require low rates of injection over a long period of time. Such injections are generally made intravenously or subcuta- neously into the patient.
  • Some of these treatments gene- rally require that the fluid be introduced relatively continuously over an extended period of time at varying rates ranging from very slow rates, usually about lcc per 24-hour period, to relatively fast rates of more than about 5 cc per 24-hour period.
  • the fluid In subcutaneous injection, the fluid must be injected within the subcutaneous fat layer between the patient's skin and muscle. Inasmuch as it is desirable to inject the fluid as deep as possible into the subcu ⁇ taneous fat layer to isolate the point of injection of the fluid from any skin surface irritation created by the injection needle puncturing the skin, it has been diffi ⁇ cult for the medical personnel installing the injection needle to assure that the point of injection was always sufficiently deep in the subcutaneous fat layer to be isolated from skin irritation without sometimes penetra- ting the muscle. This is because the thickness of the subcutaneous fat layer varies widely and because no phy ⁇ sical limit is provided on prior art injection needles to limit the depth of penetration.
  • a method of injecting fluid into a patient at an average prescribed injection rate over a prolonged period of time from a chamber carrying the fluid with an outlet connecting the- fluid to the patient and with a piston in the chamber movable toward the outlet to force the fluid into the patient characterized by the steps of connecting the piston to a driving means constructed and arranged to move the piston only a prescribed distance toward the out ⁇ let each time the driving means is operated regardless of the length of time the driving means is operated to force a known volume of the fluid into the patient each time the piston is moved the prescribed distance at an injec- tion rate greater than the desired average prescribed rate where the known volume is much less than the total volume of fluid to be injected over the prolonged period of time; and alternately operating and stopping the opera ⁇ tion of the driving means to cause the fluid to be in- jected at the average prescribed rate over the sum of the times the driving means is operated and not operated so that, in the event of a malfunction which continuously operates the driving means, the piston will be moved only the prescribed distance toward the outlet
  • the method of the invention may be further charac ⁇ terized by operating the driving means for ⁇ a fixed period of time each time the driving means is operated and stop- ping the operation of the driving means for a selectively variable period of time so that the average prescribed injection rate can be changed.
  • the method of the inven ⁇ tion may likewise be further characterized by selectively varying the prescribed distance the iston is moved each time the driving means is operated so as to vary the known
  • the invention also includes the apparatus for car ⁇ rying out the above methods of injecting fluid into the patient.
  • the driving means may include a solenoid, a stepping motor, or a piezoelectric device with an appro ⁇ priate control means.
  • a method of subcutaneously injecting fluids from a fluid supply source into the subcutaneous fat layer of a patient using an injection needle and a locating surface characterized by the steps of positively locating an in- jection needle with a sharpened end thereon with respect to a locating surface so that the sharpened end of the needle projects from the locating surface a prescribed distance slightly less than the minimum distance between the skin surface and the interface between the subcuta- neous fat layer and the muscle tissue in the patient likely to be encountered at the position where subcutaneous in ⁇ jection is to take place, and so that the sharpened end of the needle is oriented generally normal to the loca ⁇ ting surface; inserting the sharpened end of the needle into the patient at that position where subcutaneous in ⁇ jection is to take place until the locating surface is in juxtaposition with the skin surface while maintaining the positive location between the needle and the locating sur ⁇ face to insure that the sharpened end of the needle is located within the subcutaneous fat layer; and attaching the needle
  • the invention also includes apparatus for carrying out the method of subcutaneous injection characterized by an injection needle defining a fluid passage there- through, the injection needle having an inlet end con- nectible to the fluid supply source and a sharpened out ⁇ let end adapted to puncture the patient's skin and subcu ⁇ taneous fat layer; and locator means mounting the needle 5 thereon, the locator means defining a locating surface thereon adapted, to lie against the patient's skin and the sharpened end of the needle projecting from the locating surface generally normal thereto so that the sharpened end is located a prescribed distance from the locating
  • the system pro ⁇ vides a human receptive indication, visible and/or audi ⁇ ble, of whether the device is working which can be
  • the system of the invention is ideally suited for out-patient use not pre ⁇ sently clinically available to prevent unnecessary hos- pitalization and expense.
  • FIG. 1 is a perspective view illustrating the in ⁇ vention
  • Fig. 2 is an exploded perspective view illustrating the injection apparatus of the invention
  • Fig. 3 is an enlarged exploded perspective view illustrating a first embodiment of the apparatus seen in Fig. 2 with portions thereof broken away to show the construction thereof;
  • Fig. 4 is an elevational view partly shown in cross- section of that embodiment of the apparatus seen in Fig.
  • Fig. 5 is an enlarged view of the ratchet mechanism of the apparatus taken along line 5-5 in Fig. 4;
  • Fig. 6 is enlarged view of the transmission in Fig.
  • Fig. 7 is an enlarged view of that portion encircled by line 7 in Fig. 4 and shown partly in cross-section
  • Fig. 8 is an enlarged view of that portion encircled by line 8 in Fig. 4 and shown partly in cross-section;
  • Fig. 9 is an enlarged view taken along line 9-9 in Fig. 2 showing the ampule
  • Fig. 10 is an enlarged cross-sectional view taken along line 10-10 in Fig. 1;
  • Fig. 11 is an enlarged cross-sectional view taken along line 11-11 in Fig. 1;
  • Fig. 12 is an electrical block diagram of the con ⁇ troller circuit of the invention seen in Figs. 1-3;
  • Fig. 13 is a graphic illustration of the control
  • Fig. 14 is a view similar to Fig. 6 illustrating a modification of the invention.
  • Fig. 15 is an enlarged side view taken along line 15-15 in Fig. 14;
  • Fig. 16 is an enlarged exploded perspective view similar to Fig. 3 illustrating a second embodiment of the apparatus of the invention
  • Fig. 17 is an enlarged view taken generally along line 17-17 in Fig. 16;
  • Fig. 18 is an electrical block diagram of the con ⁇ troller circuit of the invention seen in Fig. 16;
  • Fig. 19 is a graphic illustration of the control output of the controller circuit illustrated in Fig. 18;
  • Fig. 20 is an enlarged partial perspective view illustrating a modified second embodiment of the power unit;
  • Fig. 21 is an enlarged view taken generally along line 21-21 in Fig. 20;
  • Fig. 22 is a view illustrating a first alternate embodiment of the invention;
  • Fig. 23 is a view illustrating a second alternate embodiment of the invention.
  • Fig. 24 is a top right perspective view illustrating an embodiment of the subcutaneous injection needle assem ⁇ bly of the invention.
  • Fig. 25 is a bottom right exploded perspective view of the embodiment of the invention seen in Fig. 24;
  • Fig. 26 is an enlarged cross-sectional view taken generally along line 26-26 in Fig. 24 and showing the invention in use;
  • Fig. 27 is a perspective view illustrating a second embodiment of the subcutaneous injection needle assembly of the invention
  • Fig. 28 is a perspective view similar to Fig. 27 showing the cover removed;
  • Fig. 29 is an enlarged cross-sectional view taken generally along line 29-29 in Fig. 28;
  • Fig. 30 is a perspective view similar to Fig. 28 showing the invention unfolded ready for use;
  • Fig. 31 is an enlarged cross-sectional view taken generally along line 31-31 in Fig. 30;
  • Fig. 32 is a perspective view illustrating a third embodiment of the subcutaneous injection needle assembly of the invention.
  • Fig. 33 is an enlarged cross-sectional view taken along line 33-33 in Fig. 32.
  • the fluid injection system 10 includes an injector 11, a carrier 12 for mounting the injector on the patient, and a connector assembly 14 for connecting the output of injector 10 to the patient, usually intravenously or subcutaneously.
  • Fig. 2 illustrates the injector 11 in more detail.
  • the injector 11 has a power unit 20 for selectively forcing a fluid from the ampule or container 21 carrying the fluid.
  • the ampule 21 is positioned on the power unit 20 by an ampule holder 22.
  • the fluid from the ampule 21 is forced into the patient by the power unit 20 via the connector assembly 14.
  • the power unit 20 includes a housing 30 which removably mounts the ampule holder 22 thereon about an expelling axis A E (Fig. 2) as will become more apparent.
  • the housing 30 mounts a drive screw assembly 31 therein about the expelling axis A p to expel fluid from the ampule 21 carried in holder 22 as will become more apparent.
  • the drive screw assembly 31 is driven by a driving solenoid 32 through a transmission 34 (Fig. 3).
  • a battery 35 is pro ⁇ vided to power solenoid 32 through a controller 36.
  • the housing 30 has a base 39 which mounts the various components thereon.
  • a removable cover 38 is adapted to fit over base 39 to enclose the components mounted on the base. Locating pins 37 maintain cover 38 in alignment with base 39 and latch pin 33 keeps cover 38 in place as best seen in Fig. 3.
  • the drive screw assembly 31 includes an externally
  • ⁇ n ° ⁇ * threaded drive screw 40 (Figs. 2-4) which forces the fluid from ampule 21.
  • the drive screw 40 is positioned coaxi- ally along the expelling axis A- by an internally threaded split nut 41 (Figs. 2 and 4) mounted on the base 39 of housing 30 so.that nut 41 is axially fixed along axis A ⁇ .
  • Nut 41 can be "opened as seen by dashed lines in Fig. 2 to release the drive screw 40 so that it can be manually move axially along axis A- and nut 41 re-engaged as will become more apparent.
  • With nut 41 closed to engage drive screw 40 rotation of drive screw 40 shifts drive screw 40 axi ⁇ ally along the expelling axis A- .
  • the outboard end of drive screw 40 projecting outside of housing 30 is provi ⁇ ded with a pointed driving projection 42 (Figs. 2 and 9) which engages the piston in the ampule 21 as will become more apparent.
  • the drive screw 40 is driven through a slip joint 44 (Figs. 3, 4 and 7).
  • the slip joint 44 is provided through a driven member 45 (Fig. 7) affixed to the inboard end of the drive screw 40.
  • the drive screw 40 defines an axially extending passage 46 therein opening onto its inboard end with the passage 46 being closed by driven member 45.
  • the driven member 45 defines a noncircular driven passage 48 therethrough which is shown as being hexagonal in shape.
  • the driven passage 48 is centered on the expelling " axis A p .
  • a drive shaft 49 with a driving section 47 having a cross-sectional shape complementary to the driven passage 48 in driven member 45 slidably extends therethrough so that rotation of drive shaft 49 rotates the drive screw 40.
  • the driving section 47 on drive shaft 49 projecting through the driven member 45 is freely received in the passage 46 in drive screw 40.
  • the passage 46 extends along the length of drive screw 40 terminating just in ⁇ board of the projecting end of the drive screw 40 as seen in Fig. 9 so that clearance for the driving section 47 on drive shaft 49 is provided when drive screw 40 is fully retracted into housing 30.
  • the drive shaft 49 is rotatably journalled in bearings mounted in support plates 50 of the trans ⁇ mission 34 as seen in Fig. 6 so that the central axis of the drive shaft 49 is coaxial with the expelling axis AT J .
  • the journalled connections between the drive shaft 49 and the support plates 50 prevent axial movement of the drive shaft 49 along the expelling axis A p while allowing the drive shaft 49 to be rotated about the ex ⁇ pelling axis Ag.
  • the drive screw 40 will be rotated to axially displace the drive screw 40 along the expelling axis A E and move the pointed driving projection 42 on the projecting end of the drive screw 40 out of the housing 30.
  • the split nut 41 is opened as shown by dashed lines in Fig. 2 and the drive screw 40 manually pushed back into the housing 30 with the driving section 47 on the drive shaft 49 sliding through the driven member 45.
  • the split nut 41 is reclosed to reengage the drive screw 40 so that it can be driven back out of the housing 30 by rotating the drive shaft 49.
  • the transmission 34 (Figs. 3-6) is powered by sole ⁇ noid 32 to rotate the drive shaft 49.
  • the drive shaft 49 serves as the output of the transmission 34 with an output spur gear 51 fixedly mounted on the drive shaft 49 between the support plates 50 so that rotation of the output spur gear 51 rotates the drive shaft 49.
  • the out ⁇ put spur gear 51 is rotatably driven by an input ratchet assembly 52 driven by the driving solenoid 32.
  • the input ratchet assembly 52 (Figs. 3 and 5) in- eludes a spur drive pinion 54 mounted on a pinion shaft 55"
  • the pinion shaft 55 also mounts thereon a ratchet mechanism 56 which includes a driven ratchet member 58 defining ratchet teeth 59 thereon about a positioning boss 60.
  • the driven ratchet member 58 is fixed to the pinion shaft 55 so that rotation of the driven ratchet member 58 also rotates the pinion shaft 55 and thus the spur drive pinion 54.
  • Driving ratchet member 61 is rotatably mounted about the positioning boss 60 for both rotational movement about the boss 60 and axial movement along the boss 60.
  • the driving ratchet member 61 includes ratchet teeth 62 there ⁇ on which are complementary to the ratchet teeth 59 on the driven ratchet member 58.
  • the ratchet teeth 62 face the ratchet teeth 59 so that, when the driven ratchet member 61 is forced toward the ratchet teeth 59 on the driven ratchet member 58, the ratchet teeth 62 on the driving ratchet member 61 engage the ratchet teeth 59 on the dri ⁇ ven ratchet member 58 whereby rotation of driving ratchet member 61 counterclockwise as seen in Fig. 3 rotates the driven ratchet member 58 therewith thus rotating the spur drive pinion 54.
  • a ratchet spring 64 is positioned around the positioning boss 60 on that side of the driving ratchet member 61 opposite the ra chet teeth 59 on driven ratchet member 58 so that the ratchet spring 64 constantly forces the driving ratchet member 61 toward the teeth 59 on the driven ratchet member 58 to maintain the ratchet teeth 59 and 60 in driving engagement with each other, yet the ratchet teeth 62 on the driving ratchet member 61 can ratchet over the rat ⁇ chet teeth 59 on the driven ratchet member 58 when the driving ratchet member 61 is moved clockwise as seen in Fig . 3 .
  • a ratchet clutch assembly 70 (Figs. 3 and 5) is pro ⁇ vided in the input ratchet assembly 52 to prevent the dri ⁇ ven ratchet member 58 from being rotated in a clockwise direction as seen “ in Fig. 3 " .
  • The" ratchet clutch assembly 70 includes a -ratchet wheel 71 affixed to the pinion shaft 55 and provided with peripheral ratchet teeth 72 which are engaged by a resilient stop member 74 best seen in Fig. 3.
  • the ratchet teeth 72 on the ratchet wheel 71 are oriented with respect to the resilient stop member 74 so that the ratchet wheel 71 can rotate with the pinion shaft 55 in a counterclockwise direction as seen in Fig.
  • the resilient stop member 74 engages the rat ⁇ chet teeth 72 when an attempt is made to rotate the pinion shaft 55 in the clockwise direction to prevent the ratchet wheel 71 and thus the pinion shaft 55 from being rotated in a clockwise direction. This serves to prevent the dri ⁇ ven ratchet member 58 and thus the spur drive pinion 54 from being rotated in a clockwise direction as seen in Fig. 3. Because the stop member 74 is resilient, it will be deflected over the ratchet teeth 72 as the pinion shaft 55 and ratchet wheel 71 are rotated in the counterclockwise direction.
  • the ratchet wheel 71 also serves to captivate the ratchet spring 64 between it and the driving ratchet member 61 so that the driving ratchet member 61 is forced toward the ratchet teeth 59 on the driven ratchet member 58.
  • the ratchet wheel 71 is provided with locating flange 75 thereon which extends over the ratchet spring 64 to prevent inadvertent dislodgement of the ratchet spring 64.
  • the transmission 34 is also provided with a manually operated flush mechanism 80 (Figs. 3 * 5 and 6) which drives the output spur gear 51 through the input ratchet assembly 52 to allow the drive screw 40 to be manually rotated for flushing the injector as will become more appa- rent.
  • the manually operated flush mechanism 80 includes a driven spur pinion 81 affixed to the pinion shaft 55 adjacent the ratchet wheel 71 opposite the ratchet mecha ⁇ nism 56.
  • the driven spur pinion 81 meshes with a manu ⁇ ally driven spur gear 82 journalled between one of the support plates 50 on the transmission 34 and a subplate 84 as best seen in Figs. 3 and 6.
  • the shaft 85 carrying the spur gear 82 extends through the support plate 50 and is provided with a drive slot 86 in the projecting end thereof outside of the support plate 50 so that the drive slot 86 can be engaged .through an appropriate opening by a manually operated tool such as a screwdriver SD partly seen in Fig. 3 to rotate the shaft 85 and spur gear 82.
  • a flush mechanism may be provided by extending the projecting end of the drive shaft 49 through that support plate 50 most remote from its driving sec ⁇ tion 47 and making a slot similar to slot 86 in shaft 85 in the projecting end of drive shaft 49 to be engaged similarly to shaft 85 to manually rotate shaft 49 clock ⁇ wise. This would eliminate the flush mechanism 80 while still providing a flushing capability ⁇ .
  • the input rat ⁇ chet assembly 52 and ratchet clutch assembly 70 would permit flushing in the same manner as explained for flush mechanism 80.
  • the driving ratchet member 61 is provided with a driving projectiong 90 (Figs. 3, 5 and 6) which is used
  • the movement of the driving projection 90 rotating the driving rat ⁇ chet member 61 is limited by upper and lower stops 91 extending above and below the driving projection 90 between the support plates 50 as seen in Fig. 3.
  • the driving projectiong 90 is constantly urged in a clock ⁇ wise direction toward the lower stop 91 as seen in Fig. 3 by a leaf spring 92 as will become more apparent.
  • the driving projection 90 is pivoted in counter- clockwise direction as seen in Fig. 3 by a drive arm 95 pivoted on the base 39 of housing 30 at 96.
  • the drive arm 95 has a projecting end 98 which extends through a slot 99 in one of the support plates 50 to engage the driving projection 90 in opposition to the leaf spring 92.
  • the drive arm 95 also has a driving projection 100 thereon which is engaged by a driving solenoid 32 to pivot the drive arm 95 clockwise as seen in Fig. 3 when the driving solenoid 32 is energized. This causes the projecting end 98 on the drive arm 95 to pivot the dri- ving projection 90 counterclockwise as seen in Fig.
  • the driving solenoid 32 is mounted on the base 39 as best seen in Fig. 3 about an axis A ⁇ .
  • the solenoid 32 has an open ended tubular cylindrical case 110 which mounts an actuator coil 111 therein.
  • a circular actuator plate 112 is pivoted to one end of the case 110 by a hinge spring member 114 so that the actuator plate 112 is mag ⁇ netically responsive to the actuator coil 11.
  • the actuator plate 112 is seen in its deactivated or open position in Fig. 3.
  • Activation of the actuator coil 111 pivots the actuator plate 112 toward the open end of the cylindrical case 110 to its activated or closed position. The movement of the actuator plate 112 is stopped by the end of case 110.
  • the actuator plate 112 has an L-shaped driving projection 115 thereon with a driving section 116 coplanar with the actuator plate 112 and a check section 118 which extends along the side of the case 110 gene ⁇ rally parallel to the solenoid axis A ⁇ .
  • the check sec ⁇ tion 118 is provided with a check slot 119 therein which is engaged by a check member 120 adjustably mounted on the case 110 by a locking screw 121.
  • the check member 120 has a check projection 122 which extends through the check slot 119 in the driving projection 115 to limit the amount of movement of the driving projection 115 as the actuator plate 112 moves away from the open end of case 110 to its deactivated position.
  • the actuator plate 112 is constantly urged toward its deactivated position by the resiliency of hinge spring member 114 as well as the leaf spring 92 in the transmission 34. Since the movement of the actuator plate 112 toward the open end of case 110 when coil 111 is energized is ar ⁇ rested by the end of case 110 and since the movement of the actuator plate 112 away from the open end of case 110 when coil 11 is de-energized is arrested by the check projection 122, the amount of movement of the driving section 116 on the driving projection 115 can thus b ⁇ e adjusted with the locking screw 121 holding the check member 120 on the case 110. Thus, the driving section 116 on the driving projec ⁇ tion 115 is moved the adjustable distance dg seen in Fig.
  • the arcuate driving projection 100 on the drive arm 95 extends behind the driving section 116 on the driving projection 115 as seen in Fig. 3 so that the closure of actuator plate 112 when coil 110 . is energized serves to pivot the drive arm 95 clockwise as seen in Fig. 3.
  • the input ratchet assembly and the ratchet clutch assembly may be used to connect the output spur gear 51 to the drive shaft 49 rather than connecting pinion shaft 55 to input drive pinion 54.
  • Figs. 14 and 15. corresponds- generally to Fig. 6 and Fig. 15 * is taken along line 15-15 in Fig. 14 to show the connection be ⁇ tween the output spur gear 51 and drive shaft 49.
  • the input ratchet assembly has been designated 52' and the check clutch assembly has been designated 70' in Figs. 14 and 15.
  • the output spur gear 51 is rotatably journalled about the drive shaft 49 rather than being affixed thereto so that gear 51 is free to ro ⁇ tate about shaft 49.
  • the input ratchet assembly 52' serves to connect gear 51 to drive shaft 49 so that rota ⁇ tion of gear 51 clockwise, when viewed in the same direc- tion as that seen in Fig. 3, will rotate shaft 49 but allows gear 51 to rotate in the opposite direction without rotating drive shaft 49 as will become more apparent.
  • Driving ratchet member 58' is affixed to the spur gear 51 so that it rotates therewith.
  • An internally splined driven ratchet member 61' is mounted on the drive shaft 49 between support plates 50 vfa an externally splined connector 60' affixed to shaft 49.
  • Connector 60' permits driven ratchet member 61' to slide axially along shaft 49 but rotation of driven ratchet member.-61' posi- tively rotates the drive shaft 49.
  • WIP members 58' and 61' facing each other are respectively provided with meshing ratchet teeth 59' and .62'.
  • Teeth 59' and 62' are constructed so that the driving ratchet teeth 59' rotate the driven ratchet member 61' and drive shaft 49 through driven ratchet teeth 62' when spur gear 51 is rotated -clockwise when viewed as in Fig. 3; how ⁇ ever, the driving teeth 59' can slip over teeth 62' when gear 51 is rotated counterclockwise so that drive shaft 49 will not be rotated counterclockwise.
  • Ratchet spring 64' urges teeth 59' and 62' together to maintain them in mesh.
  • the ratchet clutch assembly 70' (Fig. 15) is provided in the input ratchet assembly 52' to prevent the drive rat ⁇ chet member 61' and thus drive shaft 49 from being rotated in a counterclockwise direction when viewed in Fig. 3.
  • the ratchet clutch assembly 70' includes ratchet wheel 71' affixed to the drive shaft 49 and is provided with peri ⁇ pheral ratchet teeth 72* which are engaged by a resilient stop member 74'.
  • the ratchet teeth 72' on the ratchet wheel 71' are oriented with respect to the resilient stop member 74' so that the ratchet wheel 71' can rotate with the drive shaft 49 in a clockwise direction when viewed as in Fig.
  • the resilient stop member -74' engages the ratchet teeth 72' when an attempt is made to rotate the drive shaft 49 in the counterclockwise direc ⁇ tion to prevent the ratchet wheel 71' and thus the drive shaft 49 from being rotated in a counterclockwise direc ⁇ tion. Because the stop member 74' is resilient, it will be deflected over the ratchet teeth 72' as the drive shaft 49 and ratchet wheel 71' are rotated in the clock- wise direction.
  • the ratchet wheel 71' also serves to captivate the ratchet spring 64 between it and the driven ratchet member 61' so that the driven ratchet member 61' is forced toward the ratchet teeth 59' on the driving ratchet member 58'.
  • the ratchet wheel 71' may be
  • flush mecha ⁇ nism 80' best seen in Fig. 15.
  • the drive shaft 49 pro- jects through . the support plate 50 opposite the driving section 47 on shaft 49 and is provided with a driving slot 86'.
  • Engaging slot 86' with a tool such as the screwdriver mentioned -for use with slot 86 in flush mecha ⁇ nism 80 permits the drive shaft 49 to be directly rota- ted clockwise as viewed in Fig. 3.
  • the driven ratchet member 61' can ratchet over ratchet member 59' so that gear 51 need not be rotated.
  • the ratchet clutch mecha ⁇ nism 70' prevents rotation of shaft 49 counterclockwise.
  • the ampule holder 22 serves to locate the fluid ampule 21 coaxially about the expelling axis A- best seen in Figs. 2, 4 and 8 with the ampule 21 operatively associated with the pointed driving projection 42 on the drive screw 40 as will become more apparent.
  • the ampule holder -22 has a tubular side wall 130 defining an ampule receiving chamber 131 therein closed at its outboard end by end wall 132 and open at its inboard end.
  • the chamber 131 is sized so that the ampule 21 will just slidably fit in chamber 131 as will become more apparent.
  • the holder 22 is removably attached to housing 30 by a bayonet type connector 135.
  • Blades 136 of connector 135 are mounted on the side wall 130 of holder 22 adjacent its inboard end which cooperate with spaced apart locking pins 138 on the base 39 of housing 30 on diametrically opposite sides of the split nut 41 to lock the holder 22 on housing 30 with the holder coaxial with the expelling
  • the holder 22 also serves to maintain the split nut 41 closed about drive screw 40 as seen in Fig. 4 to in ⁇ sure positive threaded engagement between screw 40 and nut 41.
  • the inside diameter of the side wall 130 is substan ⁇ tially equal to the outside diameter of nut 41 in its closed position so that, when the inboard end of side wall 130 is placed around nut 41, it is positively held closed and maintained in its closed position until the ampule holder 22 is removed.
  • the ampule 21 is illustrated in Figs. 2, 4, 8 and 9 and serves to carry the liquid medicament which is to be injected into the patient.
  • Ampule 21 has a tubular side wall 140 with central passage 142 closed at its outboard end by a penetrable rubber plug 141 and open at its inboard end.
  • the side wall 140 is of constant outside and inside diameter with an outside diameter such that it is just slidably received in chamber 131 in holder 22.
  • the length L. of ampule 21 is such that ampule 21 just fits in chamber 131 between the annular arresting shoulder 139 (Fig. 8) in holder 22 adjacent its outboard end the split nut 41 when holder 22 is locked in position as seen in Fig. 4-.
  • the side wall 140 of ampule 21 has an inwardly di ⁇ rected lip 144 at its outboard end seen in Fig. 9 that engages an annular groove 145 around plug 141 to hold it in place.
  • a resilient expelling piston 146 is sli ⁇ dably received in the central passage 142 through its open inboard end and in sealing engagement with side wall 140 to form a liquid chamber 148 between piston 146 and plug 141.
  • the liquid medicament usually in concen- trated form, fills the liquid chamber 148.
  • the liquid medicament in the fluid chamber 148 can be expelled by moving the piston 146 toward the plug 141.
  • the piston 146 will also be positioned for movement coaxially along the axis A £ . This aligns the piston 146 with the drive screw 40 as will become more apparent.
  • the expelling piston 146 defines a driving cavity 150 therein facing the driving projection 42 on the projecting end of the drive screw 40.
  • the piston 146 has annular sealing rings 151 there- around to form a sliding seal with the ampule side wall 140.
  • the driving cavity 150 opens onto the inboard end of piston 146 with its outboard end closed by a conical, forwardly tapering driven surface 152 whose apex is cen ⁇ tered on the expelling axis A p .
  • the surface 152 tapers uniformly about the axis A p so that the driving projec ⁇ tion 42 on the drive screw 40 is aligned with the apex of surface 152.
  • a conical driving plate 154 is carried in the dri ⁇ ving cavity 150 to transfer the motion of screw 40 to piston 146.
  • the conical driving plate 154 has a conical, forwardly tapering .driving surface 155 complementary to the driven surface 152 in cavity 150 on its outboard side so that the plate 154 bears against the driven surface 152.
  • the conical driving plate 154 also has a like conical, forwardly tapering transfer surface 156 on its inboard side facing the driving projection 42.
  • the transfer sur- face 156 is aligned with the driving surface 155 so that the apex 158 of the transfer surface 156 is in alignment with the pointed driving projection 42 on drive screw 40.
  • the pointed projection on drive screw 40 bears against the apex 158 of transfer surface 156 to drive piston 146.
  • the driving surface 155 on driving plate 154 insures that the piston 146 will be smoothly moved along ampule 21 without canting to expel the liquid in the cham ⁇ ber 148.
  • the driving plate 154 is maintained in cavity 150 in piston 146 by an inwardly directed annular resilient lip 159 as best seen in Fig. 9. Because the lip 159 and piston 146 are resilient, the driving plate 154 can be forced into cavity 150 past -the lip. After the driving plate 154 is forced into cavity 150, the lip 159 reassumes the shape shown in Fig. 9 to keep plate 154 in place.
  • the volume of liquid medicament carried by ampule 21 is, of course, determined by the internal diameter of the side wall 140 as well as the length L. of the ampule. The size is usually selected so that some convenient volume of liquid medicament is carried in the liquid chamber 48.
  • the side wall 140 of the ampule 21 is usually graduated to indicate the volume therein and is illustrated as con ⁇ taining about 5cc of liquid medicament.
  • the am ⁇ pule 21 is designed to carry that volume of liquid which is to be dispensed over a 24-hour period. Because
  • the exposed surface of the penetrable rubber plug 141 enclosing the end of the ampule may be covered by a tear-off cover member 160 as seen in Fig. 9 to insure the sterility of this surface. Because the liquid cham- ber 148 is completely enclosed by the rubber plug 141, the ampule side wall 140 and the piston 146, the steri ⁇ lity of the liquid medicament carried in the ampule is maintained prior to its being used.
  • the outlet through the penetrable rubber plug 141 in the end of the ampule 21 is provided by a piercing cap assembly 165 best seen in Figs. 2 and 8 mounted in the outboard end of the ampule holder 22.
  • the piercing cap assembly 165 is attached to a boss. 166 on the out ⁇ board side of the end wall 132 on holder 22 so that the piercing cap assembly 165 is oriented coaxially with respect to the expelling axis A- .
  • the piercing cap assembly 165 includes an externally threaded mount 168 that can be screwed into the internal threads provided in the hole through the boss 166.
  • the externally threaded mount 168 has a piercing needle 169 extending therethrough with a pointed end 170 projecting from the mount 168 into the outboard end of the ampule receiving chamber 131 along the expelling axis A p .
  • the pointed end 170 of needle 169 extends sufficiently far into the ampule receiving chamber 131 to insure that the pointed end 170 pierces the penetrable rubber plug 141 in the outboard end of the ampule 21 when the ampule 21 is pushed into place.
  • a penetrable needle cover 171 may be provi ⁇ ded over the pointed end 170 of needle 169 so that, when the penetrable rubber plug 141 in the outboard end of the
  • An appropriate connector 172 connects the delivery tubing 174 in connector assembly 14 to the passage 175 through the piercing needle 169.
  • Passage 175 serves as the outlet from the liquid chamber 148 of the ampule 21.
  • the delivery tubing 174 may be connected directly to the patient or may be connected to the patient via con ⁇ nector assembly as seen in Fig. 1.
  • the connector assem ⁇ bly 14 as seen in Fig. 1 includes a manifold block 180 illustrated in more detail in Figs. 10 and 11.
  • the mani ⁇ fold block 180 may be permanently or removably attached to the carrier 12.
  • Block 180 has a common delivery tube 181 therefrom to which is connected a common intravenous injection needle assembly 182 or subcutaneous injection needle assembly 610 for connection to the patient. Both types of needles 182 and 610 are illustrated in Fig. 1.
  • the common delivery tube 181 is in communication with a common delivery chamber 184 in block 180 through a quick disconnect 185 seen in Figs. 10 and 1 * 1.
  • the male coupling 186 on the delivery tubing 174 from the injector 11 is connected to a continuous injection transfer chamber 188 through a check valve 189.
  • Chamber 188 is connected to the common delivery chamber 184 so that the fluid flows through
  • a second transfer chamber 190 may be provided in manifold block 180 to afford an additional connection point. Chamber 190 also communicates with the common delivery chamber 184 like chamber 188. The inlet to the second transfer chamber 190 is also equipped with a check valve 191 to permit liquid to only enter chamber 190 for discharge out the delivery chamber 184.
  • Chara- ber 190 allows a second injector of the type shown herein or of other types to be used simultaneously with injector 11.
  • a porous plug type metering assembly PPM from an alternate injector system is shown in Fig. 10 by way of illustration. It is also frequently desirable to provide short injections of medication to the patient with needle de ⁇ vices such as the hypodermic syringe HS partly ' seen in Fig. 11.
  • the manifold block 180 is provided with cross chambers 194 best seen in Fig. 11.
  • the cross chambers 194 intersect one of the transfer chambers 188 or 190 and each are provided with a penetrable plug 195 such as rubber so that the needle HN on the syringe HS can be inserted through plug ,195 into one of the cross chambers 194.
  • the syringe HS can then be used to inject unmetered fluid into the patient via the common delivery tube 181. Because the block 180 is made of a strong material, the needle HN will not pene ⁇ trate same to prevent injection from the hypodermic syringe and also isolates the needle HS from the delivery tube 181.
  • the carrier 12 is designed for convenient attachment to the patient's body. It is illustrated in Fig. 1 for attachment to the patient's arm.
  • the carrier 12 includes a wide elastic band 196 which comfortably fits over the patient's arm without significantly affecting the patient's
  • a support pouch 198 is mounted there ⁇ on which defines a continuous injector pocket therein to receive the injector 11 therein.
  • the continuous pocket is closed by a flap 199 with an appropriate mechanism to hold the flap closed.
  • a cutout 200 is provided in pouch 198 to allow the holder 22 on injector 11 to pass therethrough.
  • the manifold block 180 is illustrated as attached to band 196.
  • the controller 36 serves to alternatively connect and disconnect the battery 35 to solenoid 32 at a rate such that the desired average fluid injection rate is maintained.
  • the controller 36 is schematically illustra- ted in Fig. 12.
  • the controller 36 includes a timing pulse " generator 210 whose pulse output operates a switching network 211 to cause the switching network 211 to alternatively connect the solenoid 32 to and dis ⁇ connect solenoid 32 from battery 35.
  • the pulse output rate from the timing pulse generator 210 can be manually adjusted through the pulse time control 212.
  • the pulse timer control 212 is illustrated in Figs. 2 and 3 as three manually adjustable potentiometers although . diffe ⁇ rent timer control arrangements may be used.
  • the pulse generator output is schematically illus ⁇ trated in Fig. 13. While the output is illustrated as a square wave, it is not intended to be limiting since a variety of wave shapes may be used that functionally operate the switching network 211 in the manner described.
  • the output from generator 210 has a duty cy ⁇ cle where the output goes to state A with time interval t- j and then to state B with time interval t- during each duty cycle.
  • State A causes the switching network 211 to connect the battery 35 to solenoid 32 to activate it and state B causes the switching network 211 to disconnect battery 35 from solenoid 32 to deactivate it.
  • the phy ⁇ sical characteristics of solenoid 32 are such that it takes a prescribed maximum time interval t as seen in Fig.
  • the time interval t that the output from generator 210 remains in state A is selected to be slightly longer than the maximum solenoid actuation time interval to insure full operation of actuator plate 112,
  • the time interval t is selected to be as short as possible to conserve the energy of battery 35 and thus extend battery life. Since the solenoid 32 injects a fixed amount of liquid medicament each time it is activated and since the pulse generator output goes to state A once each duty cycle, varying the time period t--. (Fig. 13) of each duty cycle changes the injection rate. Because of the fixed actuation time ts of solenoid
  • the time interval t can be maintained constant re ⁇ gardless of the pulse rate of the output generator 210.
  • the overall injection rate can be controlled by varying the time interval t ⁇ . This is done by adjusting the pulse timer control 212.
  • Fig. 13 graphically illustrates two pulse rates, a faster rate shown by solid lines and a slower rate shown by dashed lines.
  • the time interval t is the same for both rates while time interval t « is varied. This, of course, varies the duty cycle time period --. c .
  • An indicator mechanism 213 such as lamp L seen in Figs. 1 and 2 or an audible sound generator may be used to provide an indication that the injector is operating.
  • the indicator mechanism may be activated when the output from generator 210 is in state A or state B. Since state A is usually shorter than state B, however, it would usually be activated in response to state A to extend battery life.
  • the setting of the pulse time control 212 can be made to correspond to the injection rate delivered.
  • the setting could correspond to the injection rate to two decimal places.
  • the setting illus ⁇ trated in Fig. 3 would correspond to an injection rate of 1.95 cc per 24-hour period. This facilitates adjust ⁇ ment of injection rate.
  • the overall gear ratio of transmission 34 and the drive screw assembly 31 will be determined by the size of the ampule 21, the stroke of the projecting end 98 of the drive arm 95 when sole ⁇ noid 32 is energized, and the desired incremental volume of liquid medicament to be injected each time the sole ⁇ noid 32 is energized.
  • one set of parameters used was one energized time each minute for solenoid 32 when an injection rate of about 1 cc per 24-hour period was selected. Under these requirements and with the construction illustrated in Figs. 1-9, an overall gear ratio of about 229:1 was satisfactory where the drive screw 40 has 32 threads per inch.
  • each time solenoid 32 is energized about 0.0007 cc of liquid medicament is dispensed.
  • Any conventional battery 35 may be used provided it has a sufficient voltage output to power controller 36 and solenoid 32.
  • the particular battery 35 illustrated is a 9 volt transistor type alkaline battery.
  • the battery 35 may be connected to the switching network 211 through a disabling monitor network 214 shown by phantom lines in Fig. 12.
  • the disabling monitor network 214 is provided with a feedback circuit from the timing pulse generator 210 and the output of the pulse generator 210 so that malfunction of the timing pulse generator 210 causes the feedback circuit to activate the disabling monitor network 214 to cause the disabling monitor network
  • a motion sensor may be operatively associated with the mechani ⁇ cal output of the solenoid 32 to provide another input to the disabling monitor network 214 so that, if the timing pulse generator 210 generates a signal in its output which should cause the switching network 211 to activate the solenoid 32 and no motion is sensed in the mechanical output of the solenoid 32, the disabling moni- tor network 214 disconnects the battery 35 from the switching network 211 to disable the solenoid 32.
  • the disabling monitor network 214 serves to disable the solenoid 32 upon malfunction of the timing pulse gene ⁇ rator or the failure to obtain a mechanical output from the solenoid 32 when such output should be present.
  • FIG. 16 A second embodiment of the power unit which has been designated by the numeral 220 is seen in Figs. 16 and 17.
  • the power unit 220 is used in the same manner as power unit 20 for mounting the ampule 21 in the am ⁇ pule holder 22- to inject fluid from the ampule into the patient via the connector assembly 14. Attention is invited to the disclosure of these components herein- above and will not be redescribed. Those components of. the power unit 220 which are common with the power unit 20 have the same reference numerals applied thereto. From Fig. 16, it will be seen that the power unit 220 includes housing 230 which removably mounts the ampule holder 22 thereon about the expelling axis A E as with the first embodiment of the power unit.
  • the housing 230 mounts drive screw assembly 31 therein about the expel ⁇ ling axis A- to expel fluid from the ampule 21 carried in holder 22.
  • the drive screw assembly 31 is driven by a drive motor 232 through transmission 234 and battery 35 is provided to power motor 232 through a controller 236.
  • the housing 230 has base 39 common with power unit 20 which mounts the various components thereon.
  • a re ⁇ moval cover 238 is adapted to fit over base 39 to enclose components mounted on the base and has a construction the same as the cover 38 for the power unit 20 except that the cutout for the controller 236 is slightly larger in the cover 238.
  • locating pins 37 maintain cover 238 in alignment with base 39, and latch pin 33 keeps cover 238 in place.
  • the drive screw assembly 31 includes the externally threaded drive screw 40 the same as with power unit 20 which is maintained coaxially along the expelling axis A E by the internally threaded split nut 41 (not seen in Fig. 14), the same as with the power unit 20.
  • the drive screw 40 is axially moved along the expelling axis A- simply by rotating the drive screw 40 with respect to the split nut 41.
  • the drive screw assembly 231 also is driven through slip joint 44 with drive shaft 249 having a driving sec ⁇ tion 47 thereon the same as with the drive shaft 49 in the power unit 20.
  • the drive shaft 249 is rotatably jour ⁇ nalled in bearings mounted in the support plates 250 of transmission 234 as best seen in Fig. 16 so that the drive shaft 249 is maintained coaxial with the expelling axis
  • journal connections between the drive shaft 249 and sup ⁇ port plates 250 prevent axial movement of the drive shaft 249 on the expelling axis Ap while allowing the drive shaft 249 to be rotated about that axis.
  • the drive screw 40 is retracted in the same manner as the drive screw 40 in the power unit 20.
  • the transmission 234 is powered by the motor 232 to rotate the drive shaft 249 as will become apparent.
  • the drive shaft 249 serves as the output of the transmission 234 with the output spur gear 51 fixedly mounted on the drive shaft 249 between the support plates 250 so that ro ⁇ tation of the output spur gear 51 rotates drive shaft..2-49 similarly to that described with the first embodiment of the power unit.
  • the output spur gear 51 is rotatably driven by an input pinion 254 mounted on an input shaft 255 journalled between the support plates 250 of the trans ⁇ mission 234.
  • the input shaft 255 is driven by the motor 232 as will become more apparent so that rotation of the input shaft 255 by motor 232 rotates the output spur gear 51 and thus the drive screw 40 to extend it.
  • the transmission 234 is provided with a manually ope ⁇ rated flush mechanism 280 as seen in Figs. 16 and 17 which allows the drive shaft 249 to be manually rotated for flushing the injector as will become more apparent.
  • the drive shaft 249 " rotatably ex ⁇ tends through the support plate 250 opposite the drive screw 40 and is provided with a drive slot 286 in the projected end thereof outside the outboard support plate 5 250 so that the drive slot 286 can be engaged through an appropriate opening in the cover 238 by a manually ope ⁇ rated tool such as a screw driver illustrated in Fig. 3 so that the drive shaft 249 can be manually rotated.
  • a manually ope ⁇ rated tool such as a screw driver illustrated in Fig. 3 so that the drive shaft 249 can be manually rotated.
  • the flush mechanism 280 can be substituted for the flush mechanism 80 in power unit 20.
  • the ratchet clutch assembly 270 seen in Fig. 17 is provided on the drive shaft 249 between the support plates 250.
  • the ratchet clutch assembly 270 includes a ratchet wheel 271 affixed to the c drive shaft 249 and is provided with peripheral ratchet 0 teeth 272 which are engaged by a resilient stop member 274.
  • the ratchet teeth 272 on the ratchet wheel 271 are oriented with respect to the resilient stop member 274 so that the ratchet wheel 271 can rotate with the drive shaft in a clockwise direction as seen in Fig.
  • the resilient stop member 274 engages the rat ⁇ chet teeth 272 when an attempt is made to rotate the drive shaft 249 in the counterclockwise direction to pre ⁇ vent the ratchet wheel 271 and thus the drive shaft 249 from being rotated in a counterclockwise direction.
  • Be- 0 cause the stop member 274 is resilient, it can be deflec ⁇ ted over the ratchet teeth 272 as the drive shaft 249 and ratchet wheel 271 are rotated in a clockwise direc ⁇ tion.
  • the drive shaft 249 can only be rotated in the clockwise direction both by the drive motor 232 and 5 when it is being manually rotated through the slot 286 when flushing.
  • the drive motor 232 is mounted on the base 39 as best seen in Fig. 16 coaxially about the axis A of the input shaft 255 to transmission 234.
  • the output shaft 260 of the motor 232 is connected directly to the input shaft 255 of transmission 234 so that rotation of output shaft 260 counterclockwise as seen in Fig. 16 rotates the output spur gear 51 clockwise thus rotating the drive screw 40 in the desired clockwise direction as seen in Fig. 16.
  • the motor 232 is a stepping motor which rotates its output shaft 260 through a prescribed angular displacement A M as seen in Fig. 16 each time the motor 232 is activated.
  • the amount of extension of drive screw 40 each time the drive motor 232 is stepped can be se ⁇ lected.
  • the stepping motor 232 will only step through the angle A nM each time it is activated regardless of the length of time it remains activated. Therefore, if the controller 236 fails while keeping motor 232 activated, it will only step one increment to prevent overinjection.
  • the controller 236 serves to alternatively connect and disconnect the battery 35 to drive motor 232 so that the liquid medicament from ampule 21 -is injected into the patient at the desired rate.
  • the controller 236 is sche- atically illustrated in Fig. 18.
  • the controller 236 is selectively programmable to deliver the desired injection rate via manually operated input switch network 300.
  • the switch network 300 includes a rate increase control switch 301 operated by rate increase input button 302, a rate decrease control switch 304 operated by rate decrease in ⁇ put button 305, and a mode selector switch 306 operated by actuator 308.
  • Switches 301 and 302 respectively con ⁇ trol outputs O ⁇ and 0 D to an encoding network 310 while switch 306 allowiT'the controller 236 to be programmed while in a program mode and operate the motor 232 while in an operating mode as will become more apparent.
  • Buttons 302 and 305 as well as actuator 308 can also be seen in Fig. 16.
  • the encoding network 310 generates an encoding out- put Op selectively adjustable through outputs O ⁇ j and 0 D from switches -301 and 304 which is representative of the volume of liquid medicament to be dispensed over a se ⁇ lected time period as will become more apparent.
  • the output O p is connected to one of the inputs of mode se- lector switch 306 and also to the input of a dosage rate logic network 311.
  • the dosage rate logic network 311 calculates the pulse rate required to dispense the selected volume of liquid medicament represented by output O p in equal incre- ments over the manually selected time period through manual adjustment of selector actuator 312 on time period selector 314. Actuator 312 is seen in Fig. 16 also. After calculating the required pulse rate, the regulating output 0 R from logic network 311 adjusts the timing pulse output 0 T p of the timing pulse generator 315. Output 0 T p controls switching network 316 to connect and disconnect the motor 232 to battery 35. Because controller 236 is equally applicable to the other embodiments of the power unit, the motor is illustrated as an electro-mechanical driving device. The operation of the timing pulse gene ⁇ rator 315 and switching network 316 may correspond to that already described for generator 210 and switching network 211.
  • the mode selector switch 306 has a first position which allows the controller 236 to be programmed and a second position which allows the injection rate to be monitored. In the first position, the switch 306 connects the output O p from the encoding network 310 to a liquid crystal display 318 so that the amount of liquid medica- ent to be dispensed is visually indicated by the liquid crystal readout 319. In the first position, selector switch 306 also -enables the rate increase and decrease control switches 301 and 304 while disabling the timing pulse generator 315 to prevent injection during program- ing. The personnel programming the injection rate ope ⁇ rates switches- 301 and 304 to establish the desired amount of liquid medicament to be injected.
  • Depressing input button 302 on rate increase switch 301 operates encoding network 310 to increase the displayed output O p in the liquid crystal readout 319
  • depressing input button 305 on the rate decrease switch 304 operates en ⁇ coding network 310 to decrease the displayed output Op in the liquid crystal readout 319.
  • the encoding network 310 is constructed so that, the longer the button 302 or 305 is depressed, the faster the displayed output O p is increased or de ⁇ creased as the case may be. This allows the personnel to rapidly run encoding network 310 until the displayed output O p reaches the vicinity of the desired amount to be injected, release the button 302 or 305, and then press the appropriate button 302 or 305 to finally adjust the displayed output O p .
  • the mode selector switch 306 is transferred to the operation mode via actuator 308.
  • the particular mode of switch 306 may be indicated by indi ⁇ cator lights 313 seen in Fig. 16.
  • the actuator 312 on . time period selector 314 has usually already been set at the desired time period over which the amount of liquid medicament is to be injected.
  • the time periods available may be appropriately changed. However, since the injec- ' tion rates are usually based on increments of a twenty-four hour period, it will probably be convenient to have a twenty-four hour period and several other shorter periods.
  • the control switches 301 and 304 are disabled to prevent changing output O p from encoding network 310 to the dosage rate logic network 311.
  • a monitor network 320 is connected to the output 0 Tp from the pulse generator 315 and generates a monitored output 0 to the liquid crystal display 318 via mode selector switch 306 when it is in the operation mode.
  • the monitor network 320 may also be connected to the time period selector 314 so that the monitored rate is adjusted for different time periods.
  • the battery 35 is connected to the switching network 316 through a disabling monitor network 321.
  • the disabling monitor network 321 is provided with a feedback circuit from the timing pulse generator 315 and the out ⁇ put Orp of generator 315 so that, malfunction of the ti ⁇ ming pulse generator 315 causes the feedback circuit to activate the disabling monitor network 321 to cause the disabling monitor network 321 to disconnect the battery 35 from the switching network 316 and thus disable the motor 232.
  • a motion sensor 322 is operatively associated with the mechanical output of the electro-mechanical dri ⁇ ving device to provide another input to the disabling monitor network 321 so that, if the timing pulse gene- rator 315 generates a signal in its output 0 ⁇ -
  • the disabling monitor net-work 321 disconnects-the battery 35 from the switching network 316 to disable the electro-mechanical driving device.
  • the disabling monitor network 321 serves to disable the electro-mechanical driving device upon malfunction of the timing pulse generator or the failure to obtain a mechanical output from the electro ⁇ mechanical driving device when such output should be present.
  • An alarm device 324 may be provided to the dis ⁇ abling monitor network 321 to provide an alarm that the system is malfunctioning to warn the patient and/or the personnel who is monitoring the injection of the liquid medicament into the patient.
  • the output 0 Tp from the timing pulse generator 315 and the operation of the switching circuit 316 may be the same as that described for the first embodiment of the invention. That is, the electro ⁇ mechanical driving device may be activated for a fixed period of time and deactivated for a variable period of time to change the injection rate.
  • one duty cy ⁇ cle of the timing pulse generator consists of the fixed "on" time plus the variable "off” time.
  • the duty cycle of the timing pulse generator may be changed so that it has a multiple pulse duty cycle.
  • This type of output is illustrated in Fig. 19 and has been identified as output 0 T p' .
  • Curve (a) in Fig. 19 illustrates one injection rate for the electro-mechanical driving device while Curve (b) illustrates a greater injection rate.
  • Output 0 T p' has an "on” pulse burst PB followed by an "off” time OT.
  • the pulse burst PB has one or more "on” pulse P N with short “off” pulses p therebetween so that the electro-mechanical driving device can cycle.
  • Curve (a) illustrates output 0 ⁇ p ' with two "on” pulses P vinegar and one "off” pulse P p in pulse burst PB.
  • the injection rate is determined by the duty cycle time t of the output 0 Tp ' which is the pulse burst time period t plus" the "off" period time t p .
  • Curve (b) illustrates output 0 Tp ' with three "on” pulses P vinegar and two "off” pulses Pp in pulse burst PB.
  • the stepping motor 232 would step only two times between each "off" time OT in the output 0 ⁇ p ' shown in Curve (a) while the stepping motor 232 would step three times between each "off" time OT in the output 0 T p' shown in Curve (b) in Fig. 19.
  • liquid crystal readout 319 on the liquid crystal display 318 may be changed as is appropriate, the liquid crystal readout 319 is arranged to indicate the volume of liquid medicament to be injected over the se ⁇ lected time period to two decimal places with the deci ⁇ mal point 325 being shown in Figs. 16 and 18 on the li- quid crystal readout 319.
  • ⁇ RUll 319 as shown in Figs. 16 and 18 has four integers so that up to 99.99 cc of medicament can be programmed for -dis ⁇ pensing into the patient.
  • a conventional electric motor 232' may be substituted for the stepping motor 232 shown in Figs. 16 and 17.
  • the input shaft 255 connected to the driving motor 232' may be provided with a mechanical stop projection 256' seen in Fig. 20 which extends between upper and lower stops 258' carried on support plates 250 so that the stop projection 256' can only rotate with input shaft 255 back and forth between the upper and lower stops 258'.
  • a return spring 259' is connected between the input shaft 255 and the support plates 250 so that the input shaft 255 is constantly urged in a clockwise direction in Fig. 20.
  • the return spring 259' urges the input shaft 255 and the mechanical stop projection 256' until the stop projection 256' engages the lower stop 258' between the support plates 250.
  • the motor 232' drives the input shaft 255 and the me- chanical stop projection 256' in the counterclockwise direction in Fig. 20 until the stop projection 256' engages the upper stop 258' to prevent further rotation of the input shaft 255.
  • the return spring 259' rotates the input shaft 255 back to its initial position with the stop projection 256' engaging the lower stop 258'.
  • input ratchet assembly 52' already described is used on drive shaft 249 together with ratchet clutch assembly 270 so that the output spur gear 51 drives shaft 249 when it is rotated clockwise but can rotate back counterclockwise"with input drive pinion 254 without rotating drive shaft 249.
  • the input ratchet assembly 52' function is already described and will not be repeated here.
  • the function of the ratchet assembly 270' has already been described and will not be repeated here.
  • the conventional type drive motor 232' without the projection 256', assembly 70' and ratchet assembly 52' may be used where the amount of rotation of the drive motor 232' can be accurately controlled such as with a brake (not shown) so that, each time the controller 236 is activated, the drive motor 232' will rotate through a known angle or rotation. If such a drive motor is used, it will be appreciated that the controller 236 may be adjusted so that the pulse burst PB may be a single "on" pulse P- ⁇ whose time period t v is varied.
  • the injector 41 may be mounted in the carrier 12 and connected to the connec- tor assembly 14 for injection of liquid medicament into the patient.
  • the injector 411 includes an expelling unit 420 and an ampule 421 which is connected to the expelling unit 420 to expel the liquid medicament carried in the ampule 421 into the patient via the connector assembly 14 (not shown in Fig. 22) .
  • the expelling unit 420 includes an expelling piston assembly 431 which is driven by a battery 435 through a.controller 436.
  • the battery 435 is the same as the battery described hereinbefore and the controller 436 corresponds to the controllers described hereinabove.
  • the expelling piston assembly 431 includes a housing
  • the piston cham ⁇ ber 441 has a length L p as will become more apparent.
  • the piston chamber 441 slidably mounts a magnetically responsive piston 442 therein for sliding movement back and forth along the expelling axis A E within the piston chamber 441.
  • the magnetically responsive piston 442 is in s t ealing engagement with the piston chamber 441 and has a length L p which is slightly less than one-half the length L pf , of the piston chamber 441 as will become more apparent.
  • the magnetically responsive piston 442 can be sli ⁇ dably moved from one end of the piston chamber 441 to the other.
  • An inlet port 444 is provided through the housing 440 into the piston chamber 441 and is centered along the length of the piston chamber 441.
  • the length L p of the piston 442 is selected so that, when the piston 442 is in either of the opposite ends of piston chamber 441, the in- let port is in communication with that end of the piston chamber 441 in which the piston 442 is not located.
  • a pair of solenoid coils 44 ⁇ 5 are wound around the housing 440 at opposite ends of the piston chamber 441 so that when either of the solenoid coils 445 is energized, a magnetic force will be generated which urges the magnetically responsive piston 442 toward that end of the piston chamber 441 around which the solenoid coil 445 extends.
  • the piston 442 can be moved to one end of the piston chamber 441 by energizing one of the solenoid coils 445 while the piston 442 can be moved to the other end of the piston chamber 441 by energizing the other solenoid coil 445.
  • Each of the opposite ends of the piston chamber 441 communicates with a discharge port 446 so that, as the piston 442 moves toward each end of the piston chamber 441, any liquid between the moving piston 442 and the dis- charge port 446 associated with the opposite end of the piston chamber 441 will be discharged through the discharge port 446.
  • a check valve 448 is associated with each of the discharge ports 446 so that the check valves 448 -per ⁇ mit liquid to flow only from the piston chamber 441 out through the discharge port 446 associated therewith and not in the reverse direction.
  • check valves 448 require sufficient pressure to open them that liquid flowing into the piston chamber 441 through the inlet port 444 will not leak out through the discharge port 446 in communication therewith until the piston 442 is forced toward the discharge port 446 to expel the liquid.
  • the discharge ports 446 from opposite ends of the piston chamber 441 are connected to a common outlet port 449 which is'connected to the connector as- sembly 14 (not shown) so that the liquid discharged out of the discharge ports 446 by the piston 442 will be injected into the patient.
  • permanent magnets 450 may be provided in the housing 440 at opposite ends of the piston chamber 441 so that, once the solenoid coil 445 has moved the piston into the end of the piston chamber 441, the permanent magnet 450 at that end of the piston chamber 441 keeps the piston 442 in that end of the piston chamber. 441 until the solenoid coil 445 asso ⁇ ciated with the other end of the piston chamber 441 is energized to drive the piston 442 back toward the other end of the piston chamber 441.
  • an inlet check valve 451 may be provided in the inlet port 444 to prevent fluid from being forced from within the piston chamber 441 out through inlet port 444. While the piston 442 is moving from one end of the chamber 441 to the other, it will be seen that the piston 442 covers the inlet port 444 so that liquid will not flow into the piston chamber 441.
  • the ampule 421 is different than the ampule 21 in that the ampule 421 is flexible so it can be prefilled with a known volume of liquid medicament to be injected into the patient.
  • the controller 436 as already explained, would be about the same as the controllers described hereinbefore
  • the injector 511 may be mounted in the carrier 12 and connected to the connector assembly 14 for injection of liquid medicament into the patient.
  • the injector 511 includes an expelling unit 520 and an ampule 521 which is connected to the ex ⁇ pelling unit 520 to expel the liquid medicament carried in the ampule 521 into the patient via the connector assembly 14 (not shown in Fig. 23).
  • the expelling unit 520 includes an expelling piston assembly 531 which is driven by a battery 535 through a controller 536.
  • the battery 535 is the same as the battery described herein ⁇ before and the controller 536 corresponds to the control- lers described hereinabove.
  • the expelling piston assembly 531 includes a housing 540 which defines a cylindrical piston chamber 541 there ⁇ in about an expelling axis A p .
  • the piston chamber 541 slidably mounts an expelling piston 542 therein for sli- ding movement back and forth along the expelling axis
  • piston 542 can be slidably moved from its re ⁇ tracted position seen in Fig. 23 toward and away from the discharge end 552 of the piston chamber 541.
  • An in- let port 544 is provided through the housing 540 into the piston chamber 541 between piston 542 and discharge end 552 of chamber 541 so that, when piston 542 is in its retracted position, the chamber 541 between piston 542 and discharge end 552 can be filled with liquid medicament via port 544.
  • the discharge end 552 of the pis * ton chamber 541 communicates with a discharge port 546 so that, as the piston 542 moves toward the discharge end 552 of the piston chamber 541, liquid between the moving piston 542 and the discharge port 546 will be discharged through the discharge port 546.
  • a check valve 548 is associated with discharge port 546 to permit liquid to flow only from the piston chamber 541 out through the discharge port 546 and not in the reverse direction. It will also be noted that the check valve 548 requires sufficient pressure to open it that liquid flowing into the piston chamber 541 through the inlet port 544 will not leak out through the discharge port 546 until piston 542 is forced toward the discharge port 546 to expel the li- quid.
  • the discharge port 546 is connected to the con ⁇ nector assembly 14 (not shown) so that the liquid dis ⁇ charged out of the discharge port 546 by the piston 542 will be injected into the patient.
  • an inlet check valve 551 may be provided in the inlet port 544 to prevent fluid from being forced from within the piston chamber 541 out through inlet port 544. While the piston 542 is moving toward and returning from the discharge end 552 of cham ⁇ ber 541, it will be seen that the piston 542 covers the inlet port 544 so that liquid will not flow into the piston chamber 541.
  • Ampule 521 is illustrated as the same as ampule 421 although different configurations can be used.
  • The"- ⁇ e- turn movement of the piston 542 in the piston chamber 541 from discharge end 552 to its retracted position creates a partial vacuum between piston 542 and discharge end 552 so that, when the piston 542 uncovers the inlet port 544 in its retracted position, liquid medicament from the ampule 521 having its outlet connected to the inlet port 544 can flow into the piston chamber 541 to be expelled when the piston 442 moves back toward the discharge end 552 of the piston chamber 541.
  • a driving member 554 such as quartz or the like exhibiting a piezoelectric effect is anchored to housing 540 and connected to piston 542 through an appropriate linkage 555. Because member 554 exhibits a piezoelectric effect, a voltage imposed thereon from controller 536 causes a change of volume of member 554. This change of volume is transmitted to piston 542 via linkage 555 to cause piston 542 to be moved toward the discharge end of chamber 541 to expel the liquid. When the voltage is removed, member 554 moves piston 542 back to its retracted position for chamber 541 to refill from ampule 421. Like the other embodiments of the invention, it will be seen that the movement of the piston 542 toward discharge end 552 can only inject a prescribed volume of fluid so that prevention of overdosage to the patient is insured.
  • Figs. 24-33 disclose injection needle assemblies designed to inject fluids into the subcutaneous fat layer of a patient by injecting the fluid to a known depth below the patient's skin to eliminate the trial and error technique required by the prior art.
  • Figs. 24-26 illustrate a first embodiment of the subcutaneous needle injection assembly of the invention designated 610;
  • Figs. 27-31 illustrate a second embodimentdesignated 710;
  • Figs. 32 and 33 illustrate a third embodiment designated 810.
  • the subcutaneous needle injection assembly 610 includes generally an injection needle 611 and a locator pad 612.
  • the needle 611 de ⁇ fines a fluid passage 615 therethrough from its inlet end 616 to its sharpened outlet end 618.
  • the sharpened outlet end 618 punctures the patient's skin to allow the needle 611 to be inserted into the subcutaneous fat layer as will become more apparent.
  • the injection needle 611 has a right angle bend 619 in it to form a locating sec- tion 620 about axis AT ⁇ adjacent the inlet end and a penetrating section 621 about axis A p adjacent the shar ⁇ pened outlet end 618 with the penetrating section 621 oriented about normal to the locating section 62O.
  • the inlet end 616 of needle 611 is connected to an appro- priate fluid supply source FSS schematically seen in Fig. 26 such as an injection device via tubing T.
  • the locator pad 612 may have a variety of configura ⁇ tions and is illustrated as having a generally recti ⁇ linear base 625 defining a generally flat locating sur- face 626 on the underside thereof.
  • the pad 612 is usu ⁇ ally made of a resilient material such as plastic so that it will be comfortable to wear.
  • the locating surface 626 will be in juxtaposition with the patient's skin when in ⁇ stalled as illustrated in Fig. 26.
  • An integral needle mount 628 is formed on the top of base 625 to hold needle 611 in place .
  • Needle 611 is positioned on pad 612 so that the lo ⁇ cating section 620 extends through mount 628 with its axis A ⁇ generally parallel to the locating surface 626.
  • the penetrating section 621 extends through base 625 so that it projects outwardly from surface 626 generally normal thereto.
  • the base 625 keeps the penetrating section 621 on needle 611 normal to the surface 626.
  • the length of the penetrating section 621 on needle 611 is selected so that the sharpened outlet end 618 projects from surface 626 a prescribed distance d 3. seen in Fig. 26.
  • the distance d is selected to be slightly less than the distance dsalv N the subcutaneous fat layer/muscle interface is located below the skin surface at the likely encoun- tered minimum thickness of the subcutaneous fat layer in the patient. While this minimum thickness may vary be ⁇ tween different parts of the patient's body, this mini ⁇ mum thickness is about the same between corresponding parts of different patients' bodies. Thus, different dis- tances d may be provided for subcutaneous injection into different parts of the body but would normally not have to be different for different patients even though the thick ⁇ ness of the patients' subcutaneous ' fat layers may vary widely above this minimum thickness.
  • a separable needle cover 630 may be provided to fit over the projecting penetrating section 621 of needle 611 to keep it sterile prior to use. The cover 630 would, of course, be removed prior to use.
  • an antimicrobal substance M such as Betadine Jelly may be provided around the penetrating section 621 of needle 611 as seen in Figs.
  • the antimicrobal substance M is in a preformed annulus 632 around the penetrating section 621 of needle 611 at its juncture with the locating surface 626 on pad 612- as seen in Fig. 25 so that the substance M is always in place for use and seals the puncture P in the skin around the needle 611.
  • An enlarged section 631 may be formed in the needle cover 630 as seen in Fig. 25 to accommodate the preformed antimicrobal substance M.
  • the subcutaneous needle in ⁇ jection assembly 710 includes generally an injection needle 711 and a locator pad 712.
  • the needle 711 is like needle 611 with inlet end 716 and sharpened outlet end 718.
  • the injection needle 711 has a right angle bend in it to form the locating section adjacent the inlet end and the penetrating section 721 adjacent the sharpened outlet end 718 with the penetrating section 721 oriented about normal to the locating section.
  • the inlet end 716 of needle 711 is connected to an appropriate fluid sup ⁇ ply source via tubing T.
  • the locator pad 712 has a base 725 with a needle mount 728 to hold needle 711 in place. Unlike pad 612, however,-*the base 725 on pa"d 712 can be folded down around the penetrating section 721 on needle 711 to cover it. When unfolded, as seen in Figs. 30 arid 31, the base 725 corresponds in shape to base 625 and defines the flat locating surface 726 about the penetrating sec ⁇ tion 721 of needle 711.
  • the base 725 is hinged gene- 5 rally along lines 735 on opposite sides of the needle mount 728 as s-een in Fig. 28 so that the base 725 has an effective fold axis A in registration under the axis of the locating section of the needle 711. While different hinging constructions may be used, the con-
  • base 725 is made of a resilient material such as plastic, this forms a living hinge section 738 along the bottom of each of the grooves 736 as best seen in Fig. 29 so that the out-
  • Tabs 740 may be provided on sections 739 to facilitate unfolding them prior to use.
  • microbal substance M is prepackaged around the penetrating end 721 of needle 711 as seen in Fig. 29.
  • the installation of the injection assembly 710 after it is unfolded is the same as that discussed for assembly 610.
  • the depth of injection is positively con ⁇ trolled.
  • the subcutaneous needle injection assembly 810 also includes generally an injec ⁇ tion needle 811 and a locator pad 812. Additionally, a penetration adjustment mechanism 814 is provided to control the amount of exposure of needle 811 as will be- come more apparent.
  • the needle 811 like needle 611, defines a fluid passage therethrough from its inlet end 816 to its sharpened outlet end 818.
  • the injection needle 811 also has a right angle bend 819 in it to form locating section 820 adjacent the inlet end and penetra- ting section 821 adjacent the sharpened outlet end 818 with the penetrating section 821 oriented about normal to the locating section 820.
  • the inlet end 816 of needle 811 is also connected to an appropriate fluid supply source via tubing T.
  • the locator pad 812 corresponds generally to pad 612 with a generally rectilinear base 825 defining a gene ⁇ rally flat locating surface 826 on the underside thereof which will be in juxtaposition with the patient's skin when installed.
  • An integral needle mount 828 is formed on the top of base 825 to hold needle 811 in place; however, needle mount 828 is short as compared with mount 628 and engages the locating section 820 of needle 811 adjacent its inlet end 816.
  • the hole 850 in pad 812 through which penetrating section 821 passes keeps section 821 normal to surface 826.
  • the penetration adjustment mechanism 814 engages the locating section 820 of needle 811 adjacent bend 819 to positively control the distance d the sharpened outlet end 818 projects from surface 826.
  • Mechanism 814 includes a stepped adjustment member 851 which slides on the top of base 825.
  • the steps on member 851 may be grooved as seen at 852 to keep the member 851 in-place.
  • Each groove 852 is located at a different height from the top of base 825 so that the penetration distance d can be changed by shifting the needle 811 to different grooves 852 in member 851.
  • Guides 854 may be provided to keep member 851 in place axially of section 820 on needle 811.
  • injection assembly 810 This allows the injection assembly 810 to be adjusted for use at different body positions. After adjustment is completed, the injection assembly 810 would be installed like injection assembly 610.

Landscapes

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

Abstract

Methode et appareil d'injection de fluide dans un patient a partir d'une chambre (148) contenant le fluide avec une sortie (175) reliant le fluide au patient et avec un piston (146) dans la chambre mobile vers la sortie pour forcer le fluide dans le patient, utilisant des moyens d'entrainement (20) pour ne deplacer le piston que d'une distance predeterminee vers la sortie a chaque fois que les moyens d'entrainement fonctionnent, independamment du temps pendant lequel ces moyens fonctionnent, en actionnant et en arretant alternativement les moyens d'entrainement pour que le fluide soit injecte a une vitesse moyenne predeterminee pendant la duree totale durees de fonctionnement et de non fonctionnement des moyens d'entrainement de sorte que, dans le cas d'un mauvais fonctionnement qui provoquerait le fonctionnement ininterrompu des moyens d'entrainement, le piston serait deplace seulement de la distance predeterminee vers la sortie pour eviter d'administrer une trop forte dose au patient. Un ensemble a aiguille d'injection sous cutanee (610) est egalement decrit.
PCT/US1979/000013 1979-01-12 1979-01-12 Systeme d'injection autonome Ceased WO1980001459A1 (fr)

Priority Applications (5)

Application Number Priority Date Filing Date Title
JP50139479A JPS56500119A (fr) 1979-01-12 1979-01-12
DE19792953494 DE2953494A1 (de) 1979-01-12 1979-01-12 Self-contained injection system
GB8028796A GB2050843B (en) 1979-01-12 1979-01-12 Self-contained injection system
PCT/US1979/000013 WO1980001459A1 (fr) 1979-01-12 1979-01-12 Systeme d'injection autonome
EP19790901050 EP0022776A4 (fr) 1979-01-12 1980-07-29 Systeme d'injection autonome.

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
WOUS79/00013 1979-01-12
PCT/US1979/000013 WO1980001459A1 (fr) 1979-01-12 1979-01-12 Systeme d'injection autonome

Publications (1)

Publication Number Publication Date
WO1980001459A1 true WO1980001459A1 (fr) 1980-07-24

Family

ID=22147486

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1979/000013 Ceased WO1980001459A1 (fr) 1979-01-12 1979-01-12 Systeme d'injection autonome

Country Status (5)

Country Link
EP (1) EP0022776A4 (fr)
JP (1) JPS56500119A (fr)
DE (1) DE2953494A1 (fr)
GB (1) GB2050843B (fr)
WO (1) WO1980001459A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102004063648A1 (de) * 2004-12-31 2006-07-20 Tecpharma Licensing Ag Injektions- oder Infusionsgerät mit Lebensdauer-Ermittlungseinrichtung

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5997501A (en) * 1993-11-18 1999-12-07 Elan Corporation, Plc Intradermal drug delivery device

Citations (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2402306A (en) * 1943-10-07 1946-06-18 Turkel Henry Retaining guard guide for needles
US2602446A (en) * 1950-02-27 1952-07-08 Antonina S Glass Automatic medical injection apparatus
US2627270A (en) * 1946-02-09 1953-02-03 Antonina S Glass Self-propelled automatic syringe
US2690178A (en) * 1950-11-13 1954-09-28 Research Corp Automatic apparatus for administering drugs
US3415419A (en) * 1966-10-27 1968-12-10 Jewett Fluid administering system
US3863631A (en) * 1970-06-02 1975-02-04 Affiliated Hospital Prod Method of applying and securing a needle
US3880138A (en) * 1973-03-12 1975-04-29 Lear Siegler Inc Method for injecting contrast media into the vascular system
US3957048A (en) * 1974-10-03 1976-05-18 Jacobs Herbert V Intravenous device
US3964482A (en) * 1971-05-17 1976-06-22 Alza Corporation Drug delivery device
US4024864A (en) * 1975-09-05 1977-05-24 Cordis Corporation Injector with overspeed protector
DE2809990A1 (de) * 1977-03-09 1978-09-21 Nat Res Dev Injektionsspritze fuer medizinische zwecke
US4150672A (en) * 1976-11-12 1979-04-24 Martin John K Injection device and method

Patent Citations (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2402306A (en) * 1943-10-07 1946-06-18 Turkel Henry Retaining guard guide for needles
US2627270A (en) * 1946-02-09 1953-02-03 Antonina S Glass Self-propelled automatic syringe
US2602446A (en) * 1950-02-27 1952-07-08 Antonina S Glass Automatic medical injection apparatus
US2690178A (en) * 1950-11-13 1954-09-28 Research Corp Automatic apparatus for administering drugs
US3415419A (en) * 1966-10-27 1968-12-10 Jewett Fluid administering system
US3863631A (en) * 1970-06-02 1975-02-04 Affiliated Hospital Prod Method of applying and securing a needle
US3964482A (en) * 1971-05-17 1976-06-22 Alza Corporation Drug delivery device
US3880138A (en) * 1973-03-12 1975-04-29 Lear Siegler Inc Method for injecting contrast media into the vascular system
US3957048A (en) * 1974-10-03 1976-05-18 Jacobs Herbert V Intravenous device
US4024864A (en) * 1975-09-05 1977-05-24 Cordis Corporation Injector with overspeed protector
US4150672A (en) * 1976-11-12 1979-04-24 Martin John K Injection device and method
DE2809990A1 (de) * 1977-03-09 1978-09-21 Nat Res Dev Injektionsspritze fuer medizinische zwecke

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102004063648A1 (de) * 2004-12-31 2006-07-20 Tecpharma Licensing Ag Injektions- oder Infusionsgerät mit Lebensdauer-Ermittlungseinrichtung

Also Published As

Publication number Publication date
DE2953494A1 (de) 1982-02-04
GB2050843B (en) 1983-03-09
JPS56500119A (fr) 1981-02-12
GB2050843A (en) 1981-01-14
EP0022776A4 (fr) 1981-06-17
EP0022776A1 (fr) 1981-01-28

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