CA1103545A - Dispensing device for pharmaceuticals - Google Patents
Dispensing device for pharmaceuticalsInfo
- Publication number
- CA1103545A CA1103545A CA317,906A CA317906A CA1103545A CA 1103545 A CA1103545 A CA 1103545A CA 317906 A CA317906 A CA 317906A CA 1103545 A CA1103545 A CA 1103545A
- Authority
- CA
- Canada
- Prior art keywords
- piston
- pharmaceutical
- rate
- elastic material
- delivery
- 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.)
- Expired
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
- A61M5/14276—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body specially adapted for implantation
-
- 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
- A61M2005/1401—Functional features
- A61M2005/1405—Patient controlled analgesia [PCA]
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/01—Motorized syringe
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)
- Medicines That Contain Protein Lipid Enzymes And Other Medicines (AREA)
Abstract
TITLE
DISPENSING DEVICE FOR PHARMACEUTICALS
INVENTOR
Michael V. Sefton ABSTRACT OF THE DISCLOSURE
An implantable device for dispensing a pharmaceutical in two modes; a basal delivery rate and an augmented rate. The device includes a permeable elastic material adapted to be repeatedly compressed by a solenoid operated piston. The device delivers a basal rate when the piston is inoperative and an augmented rate when the permeable elastic material is compressed.
The device is suitable for delivering insulin in an "artificial endocrine pancreas".
DISPENSING DEVICE FOR PHARMACEUTICALS
INVENTOR
Michael V. Sefton ABSTRACT OF THE DISCLOSURE
An implantable device for dispensing a pharmaceutical in two modes; a basal delivery rate and an augmented rate. The device includes a permeable elastic material adapted to be repeatedly compressed by a solenoid operated piston. The device delivers a basal rate when the piston is inoperative and an augmented rate when the permeable elastic material is compressed.
The device is suitable for delivering insulin in an "artificial endocrine pancreas".
Description
3~
BACKGROUND OF THE INVENTION
This invention relates to a device for dispensing pharmaceuticals. ~
Conventional administration of drugs takes two ~ ;
general forms - periodic injection or ingestion, or continuous infusion. Periodic administration has the disadvantage that the drug level within the body varies from above optimum initially and falls below optimum, resulting in poor maintenance of the patient and ineffi-1~ cient use of the drug. Increasing the number of applications minimizes the adverse effects of high dosages and improves 1 ~;
efficiency but results in hi~her costs and more inconven-ience to the patient. Infusion therapy can provide a relatively con~tant dose level but is limited by the bulky nature of the pharmaceutical preparation and by the ¦~
expert care needed for sa~e administration.
In recent years, polymeric membranes have been used to encapsulate pharmaceutical preparations to slow and control the release of the active substance, allowing ~'.0 the body to be main-tained at the optimum level over a relatively long time. Controlled release formulations have two deficiencies which limit their use ~ the amount of drug that can be encapsulated and implanted is relatively small, and it is not possible to vary the rate of release of the drug. The inability to vary the release rate limits the use to those agents which have a constant demand rate or a constant clearance rate, and is not entirely satisfactory for insulin therapy. 1, Insulin-is required by the body in varying amounts with a grea-ter amount being required during and i~mediately after a meal when the glucose level rises. The controlled 1.
, I .
release formulation rhile maintaining a basal amount of insulin in th~ blood, cannot increase -the amount of ~ ¦
insulin to counteract the increased glucose level after a meal.
It has been proposed, for example, in United States Patent 3,923,060 to E.H. Ellinwood, Jr., to provide an implantable apparatus for dispensing medications within the body over a long period of time in accordance with the needs of the patient by providing sensors which monitor a particular body condition and powered dispensing means responsive to the sensed data.
The aforesaid patent also describes a device specifically for dispensing insulin, having two dispensing elements, one to dispense a aaily average dose on a regular basis and one to dispense intermittently when the need arises.
The device described requires that each dispensing element ;~
is provided with a separate pump, pump driving means and associated logic circuit. This arrangement requires two -separate dispensing units and associated energizing means, and in the event of an interruption of energy, no medlcation would be dispensed.
SUM~IARY OF THE INVENTION `
It has been found that a relatively simple 1~ ;pharmaceutical dispensing device can be provided with the ¦
use o-E a permeable elastic material in which delivery of tne pharmaceutical can be increased by repeated compression of the permeable elastic material to provide a controllable delivery rate.
It has also been found that repeated compression ~;3G of the permeahle material can increase delivery ~i~chout the use of chec]c valves for preventing back flow.
Although the reason for this is not understood with ce~taint ~
it is believed that as the piston compre5ses the elastic permeable material, the portion of the material in contact with and near the piston surface is compressed -to a degree that it is rendered relatively impermeable in comparison with the material at the opposite outlet end, and thereby reduces backflow while allowing flow in the direction o F the outlet.
~he present inven-tion provides a device Eor I -dispensing a pharmaceutical comprising: an elastic 0 material permeable to the pharmaceutical; a housing for conining the elastic material, said housing having an inlet for connection with a supply of the pharmaceutical, ~ ;
and an outlet for delivery; a reciprocatable piston for repeatedly compressing the elastic material, and means for activating said piston; the device being operative to deliver a basal rate of the pharmaceutical when the piston is inoperative, and an ,.~
au~mented rate when the elastic material is compressed.
~he present invention is well suited for 0 delivering a ~ighly concentrated pharmaceutical preparation thereby facilitating the design and use of an implanted dev,ce.
BRIEF nESCRIPTION OF THE DRAWINGS
Figure 1 is a partly sectional view of a device for dispensing a pharmaceutical in accordance with the present invention.
Figvres 2 and 3 are partly sectional views of alternative embodiments of a dispensing device.
Figure 4 is a schematic illustration of a 0 system incorporating the dispensing device of the present invention.
3_ 5~5 ~
DESCRIPTION OF TIIE PREFERRED EMBODIMENTS
Referring to figure 1, the pharmaceutical dispensing device 1 includes an elastic material 2 that is permeable to the pharmaceutical. The permeable elastic material 2 is contained ~y a suitable housing 3 havin~ an inlet 4, for connecting with a supply o:E the pharmaceutical r and an outlet 5. Reciprocata~ly disposed within a cylindrical portion 6 of the housing 3 i5 a piston 7 for compressing the elastic permeable material Z. The piston 7 is made of a magnetic material and compression of the elastic material 2 is effected by means of a solenoid coil 8. The permeable material 2 is confined at the outlet by a suitable porous or apertured plug 9. Means, in the orm of a passageway 10, is provided for allowing the pharmaceutical to bypass the piston 7 to the permeable material 2.
In operation, with the inlet 4 connected to a suitable supply of a pharmaceutical, the concentration difference and/or the pressure difference across the permeahle elastic material 2 results in diffusion or bul]c transport through the material 2. The pharmaceutical flows through the passageway 10, and also around the ~ ;
outside of the piston if sufficient clearance is provided, and exits at outlet 5. Hereinafter, the flow that takes ~t place while tlle solenoid-piston is inactive is referred to as basal delivery. The basal rate for a particular pharmaceutical is a function of the concentration and/or pressure difference across the permeable elastic material, and the permeability of the material.
Augmer.ted delivery is achieved by repeated compression and decompression of the material 2 by means .
3~4S - ~
o-E the piston 7. Compr~ssion of the material 2 is effected by che maynetic pistorl 7 when current is a~plied to the solenoid coil and deco~pression, or recover~ to the original condition, occurs ~rhen current supply is interrupted. The augmented deli~re;ry rate is a function of the perrnea~ y and mecha~ical properti~s, such as the modulus o elasticity, oF the material, and also on the solenoid desi~n. For a given device the augmen-ted delivery rate is a function o~ the fre~uency O of compression and the displacemen~ of the material with each cycle of compression. The displacement can be varied b~ varying the current through the solenoid coil.
It was found that augmented delivery ls more efficient when, for each compression-decompression cycle, the time for decompression is l~n~er than com-Pres9ion ~ime. It appears that such lonqer times for decomp~esslon allows more complete recoverv or decom-pression of thç elastic material.
Figure 2 iliustrates another ernbodiment of the 0 presen, inventio~. The de~ice 20 is basically similar to th~t of fi~ure 1, having a piston 21 for compressing the ~ermeable elastic materJal 23t and inlet ~ and' ;
out]et 25 within a housing 26~ eren~es ~ro~ ~iyure~`
1 include the posit~.on o.~ the inlel and the us~ ^~ a separ~-te, but interconnected, piston and solenoid~ core~
This lattel arsang2lnen-t facili-tates sepaxating the solenoid coil 27 from out]e~ ~5.
For hasal delivery:, the piston 23 is the uppox position, as shown, and the pharnaceutical ent~rs o at inlet 24, ~iffuses through the rn~ter:ial 23 and exits-at outlet 25. T~e inlet 2~ is positioned in ~hc housing ~3~
26 so as to be alternately blocked and unblocked by the piston 21 in the augmented delivery mode. As the piston 21 travels downward t it blocks the inlet 24 reducing backflo~ as the material 23 is compressed and thereby increasing efficiency.
Figure 3 shows another embodiment of the invention in which the outlet portion 31 of the device, including the piston 32 and permeable elas-tic material 33, has a cross-sectional size smaller than that of L0 the inlet portion 34 inc1uding the solenoid core 35.
This embodiment is particularly suitable for the administration of a pharmaceutical directly into a small vessel. Administration to a small vessel using devices with larger outlets, such as shown in figures 1 and 2, can also be achieved by the use of a small diameter tubing connected with the outlet by a suitable tapered connector.
Preferably the permeable elastic material will have a tensile modulus of elasticity of not ~0 greater than 104psi in order to minimize power consump-tion. Examples of suitable materials include:
polyvinyl alcohol hydrogels, polyhydroxyethyl methacr~late hydrogels, polyacrylamide gels, agarose gels, gels made j;
from polyelectrolytes, acrylic polymers, vinyl pyridine, ¦ ;
vinyl pyrrolidone, cellulose and cellulose derivatives, or polyurethane and other polymeric foams. The elastic material may consist of two different materials in series. For example/ a thin polyacrylate membrane can be combined with a thick section of polyurethane O foam. The combined membrane has compressibility .
substantially equal to that of the foam, and the limiting permeabilit-y that o~ the polyacrylate membrane.
Figure ~ illustrates schematically a -complete system for administering a pharmaceutical, which could, for example, be insulin to treat diabetes mellitus~ In this system the dispensiny device 40, which may be of the type illustrated in figures 1,
BACKGROUND OF THE INVENTION
This invention relates to a device for dispensing pharmaceuticals. ~
Conventional administration of drugs takes two ~ ;
general forms - periodic injection or ingestion, or continuous infusion. Periodic administration has the disadvantage that the drug level within the body varies from above optimum initially and falls below optimum, resulting in poor maintenance of the patient and ineffi-1~ cient use of the drug. Increasing the number of applications minimizes the adverse effects of high dosages and improves 1 ~;
efficiency but results in hi~her costs and more inconven-ience to the patient. Infusion therapy can provide a relatively con~tant dose level but is limited by the bulky nature of the pharmaceutical preparation and by the ¦~
expert care needed for sa~e administration.
In recent years, polymeric membranes have been used to encapsulate pharmaceutical preparations to slow and control the release of the active substance, allowing ~'.0 the body to be main-tained at the optimum level over a relatively long time. Controlled release formulations have two deficiencies which limit their use ~ the amount of drug that can be encapsulated and implanted is relatively small, and it is not possible to vary the rate of release of the drug. The inability to vary the release rate limits the use to those agents which have a constant demand rate or a constant clearance rate, and is not entirely satisfactory for insulin therapy. 1, Insulin-is required by the body in varying amounts with a grea-ter amount being required during and i~mediately after a meal when the glucose level rises. The controlled 1.
, I .
release formulation rhile maintaining a basal amount of insulin in th~ blood, cannot increase -the amount of ~ ¦
insulin to counteract the increased glucose level after a meal.
It has been proposed, for example, in United States Patent 3,923,060 to E.H. Ellinwood, Jr., to provide an implantable apparatus for dispensing medications within the body over a long period of time in accordance with the needs of the patient by providing sensors which monitor a particular body condition and powered dispensing means responsive to the sensed data.
The aforesaid patent also describes a device specifically for dispensing insulin, having two dispensing elements, one to dispense a aaily average dose on a regular basis and one to dispense intermittently when the need arises.
The device described requires that each dispensing element ;~
is provided with a separate pump, pump driving means and associated logic circuit. This arrangement requires two -separate dispensing units and associated energizing means, and in the event of an interruption of energy, no medlcation would be dispensed.
SUM~IARY OF THE INVENTION `
It has been found that a relatively simple 1~ ;pharmaceutical dispensing device can be provided with the ¦
use o-E a permeable elastic material in which delivery of tne pharmaceutical can be increased by repeated compression of the permeable elastic material to provide a controllable delivery rate.
It has also been found that repeated compression ~;3G of the permeahle material can increase delivery ~i~chout the use of chec]c valves for preventing back flow.
Although the reason for this is not understood with ce~taint ~
it is believed that as the piston compre5ses the elastic permeable material, the portion of the material in contact with and near the piston surface is compressed -to a degree that it is rendered relatively impermeable in comparison with the material at the opposite outlet end, and thereby reduces backflow while allowing flow in the direction o F the outlet.
~he present inven-tion provides a device Eor I -dispensing a pharmaceutical comprising: an elastic 0 material permeable to the pharmaceutical; a housing for conining the elastic material, said housing having an inlet for connection with a supply of the pharmaceutical, ~ ;
and an outlet for delivery; a reciprocatable piston for repeatedly compressing the elastic material, and means for activating said piston; the device being operative to deliver a basal rate of the pharmaceutical when the piston is inoperative, and an ,.~
au~mented rate when the elastic material is compressed.
~he present invention is well suited for 0 delivering a ~ighly concentrated pharmaceutical preparation thereby facilitating the design and use of an implanted dev,ce.
BRIEF nESCRIPTION OF THE DRAWINGS
Figure 1 is a partly sectional view of a device for dispensing a pharmaceutical in accordance with the present invention.
Figvres 2 and 3 are partly sectional views of alternative embodiments of a dispensing device.
Figure 4 is a schematic illustration of a 0 system incorporating the dispensing device of the present invention.
3_ 5~5 ~
DESCRIPTION OF TIIE PREFERRED EMBODIMENTS
Referring to figure 1, the pharmaceutical dispensing device 1 includes an elastic material 2 that is permeable to the pharmaceutical. The permeable elastic material 2 is contained ~y a suitable housing 3 havin~ an inlet 4, for connecting with a supply o:E the pharmaceutical r and an outlet 5. Reciprocata~ly disposed within a cylindrical portion 6 of the housing 3 i5 a piston 7 for compressing the elastic permeable material Z. The piston 7 is made of a magnetic material and compression of the elastic material 2 is effected by means of a solenoid coil 8. The permeable material 2 is confined at the outlet by a suitable porous or apertured plug 9. Means, in the orm of a passageway 10, is provided for allowing the pharmaceutical to bypass the piston 7 to the permeable material 2.
In operation, with the inlet 4 connected to a suitable supply of a pharmaceutical, the concentration difference and/or the pressure difference across the permeahle elastic material 2 results in diffusion or bul]c transport through the material 2. The pharmaceutical flows through the passageway 10, and also around the ~ ;
outside of the piston if sufficient clearance is provided, and exits at outlet 5. Hereinafter, the flow that takes ~t place while tlle solenoid-piston is inactive is referred to as basal delivery. The basal rate for a particular pharmaceutical is a function of the concentration and/or pressure difference across the permeable elastic material, and the permeability of the material.
Augmer.ted delivery is achieved by repeated compression and decompression of the material 2 by means .
3~4S - ~
o-E the piston 7. Compr~ssion of the material 2 is effected by che maynetic pistorl 7 when current is a~plied to the solenoid coil and deco~pression, or recover~ to the original condition, occurs ~rhen current supply is interrupted. The augmented deli~re;ry rate is a function of the perrnea~ y and mecha~ical properti~s, such as the modulus o elasticity, oF the material, and also on the solenoid desi~n. For a given device the augmen-ted delivery rate is a function o~ the fre~uency O of compression and the displacemen~ of the material with each cycle of compression. The displacement can be varied b~ varying the current through the solenoid coil.
It was found that augmented delivery ls more efficient when, for each compression-decompression cycle, the time for decompression is l~n~er than com-Pres9ion ~ime. It appears that such lonqer times for decomp~esslon allows more complete recoverv or decom-pression of thç elastic material.
Figure 2 iliustrates another ernbodiment of the 0 presen, inventio~. The de~ice 20 is basically similar to th~t of fi~ure 1, having a piston 21 for compressing the ~ermeable elastic materJal 23t and inlet ~ and' ;
out]et 25 within a housing 26~ eren~es ~ro~ ~iyure~`
1 include the posit~.on o.~ the inlel and the us~ ^~ a separ~-te, but interconnected, piston and solenoid~ core~
This lattel arsang2lnen-t facili-tates sepaxating the solenoid coil 27 from out]e~ ~5.
For hasal delivery:, the piston 23 is the uppox position, as shown, and the pharnaceutical ent~rs o at inlet 24, ~iffuses through the rn~ter:ial 23 and exits-at outlet 25. T~e inlet 2~ is positioned in ~hc housing ~3~
26 so as to be alternately blocked and unblocked by the piston 21 in the augmented delivery mode. As the piston 21 travels downward t it blocks the inlet 24 reducing backflo~ as the material 23 is compressed and thereby increasing efficiency.
Figure 3 shows another embodiment of the invention in which the outlet portion 31 of the device, including the piston 32 and permeable elas-tic material 33, has a cross-sectional size smaller than that of L0 the inlet portion 34 inc1uding the solenoid core 35.
This embodiment is particularly suitable for the administration of a pharmaceutical directly into a small vessel. Administration to a small vessel using devices with larger outlets, such as shown in figures 1 and 2, can also be achieved by the use of a small diameter tubing connected with the outlet by a suitable tapered connector.
Preferably the permeable elastic material will have a tensile modulus of elasticity of not ~0 greater than 104psi in order to minimize power consump-tion. Examples of suitable materials include:
polyvinyl alcohol hydrogels, polyhydroxyethyl methacr~late hydrogels, polyacrylamide gels, agarose gels, gels made j;
from polyelectrolytes, acrylic polymers, vinyl pyridine, ¦ ;
vinyl pyrrolidone, cellulose and cellulose derivatives, or polyurethane and other polymeric foams. The elastic material may consist of two different materials in series. For example/ a thin polyacrylate membrane can be combined with a thick section of polyurethane O foam. The combined membrane has compressibility .
substantially equal to that of the foam, and the limiting permeabilit-y that o~ the polyacrylate membrane.
Figure ~ illustrates schematically a -complete system for administering a pharmaceutical, which could, for example, be insulin to treat diabetes mellitus~ In this system the dispensiny device 40, which may be of the type illustrated in figures 1,
2 or 3, has its outlet 41 posltioned in the body to be treated. Alternatively the entire dispensing device may be implanted in the body 42. The dispensing ~;
device 40 is supplied with a pharmaceutical from a suitable reservoir 43 which may also be implanted in ~ -the body.
Xn operation~ a basal rate o a pharmaceutical, such as insulin for example r is delivered while the solenoid-piston is inoperative~ When increased insulin delivery is required, such as duriny and after meals, -the solenoid-piston is activated by control means 44 which provides a periodic pulse of current of selected ~0 magnitude and Irequency to provide the desired augmented flow. The controller 44 may be activated manually or by a suitable programer 45. The programer 45 may, for example, provide for progressively decreasing delivery of insulin from the beginniny of a meal to a pre-determined time later. Alternatively, or in addition, the glucose concentra~ion may be monitored by a suitable sensor 46 to con-trol the amount of insulin delivered.
In addition to treating diabetes mellitus, the present invention may be used for various other ~0 conditions where variable delivery rate is requi~ed, such as cardiac function control or cancer chemotherapy.
_7_ ~ 3~$ Il EX~MP1E
~ 7 mm outside diameter glass -tube was capped at one end with a sintered glass disc. A '~-
device 40 is supplied with a pharmaceutical from a suitable reservoir 43 which may also be implanted in ~ -the body.
Xn operation~ a basal rate o a pharmaceutical, such as insulin for example r is delivered while the solenoid-piston is inoperative~ When increased insulin delivery is required, such as duriny and after meals, -the solenoid-piston is activated by control means 44 which provides a periodic pulse of current of selected ~0 magnitude and Irequency to provide the desired augmented flow. The controller 44 may be activated manually or by a suitable programer 45. The programer 45 may, for example, provide for progressively decreasing delivery of insulin from the beginniny of a meal to a pre-determined time later. Alternatively, or in addition, the glucose concentra~ion may be monitored by a suitable sensor 46 to con-trol the amount of insulin delivered.
In addition to treating diabetes mellitus, the present invention may be used for various other ~0 conditions where variable delivery rate is requi~ed, such as cardiac function control or cancer chemotherapy.
_7_ ~ 3~$ Il EX~MP1E
~ 7 mm outside diameter glass -tube was capped at one end with a sintered glass disc. A '~-
3 mm thick cT,Tlindrical section of flexible polyurethane foam (EIYPOL ~, W.R. Grace fi Co . ~ made from lO0 parts FHP 30001 70 parts water, and l.0 part ~520 ~Union ~, Carbide) was forced into the tube. A 2.5 cm long mild steel rod (4~8 mm diameter) with a l.4 mm diarneter central bore was used as p}ston. ~o thousand turns of number 36 enamelled copper wire was wrapped about the outside of the tube, so that there was a 2 mm offset between the end of the coil and the end of the piston.
.
A piece of transformer iron was then wrapped about the coil to make an external field path.
A feed solution consistîng of 143 ppm amaranth (a tracer molecule~ and 0.35 units/ml of insulin in ; phosphate buffered saline ~pH 7.4)~ was prepared within a sterile infusion bottle. The concentration of ~`
:
amaranth was determined by quantltative ultraviolet spectroscopy, at a wavelength of 220 nm, comparing the absorption of a test solution with the absorption of a set of standards. The addition of a small quantity of insulin labelled~with radiactive iodine tIl25), enabled changes in the concentration of insulin to be determined.
The activity of an insulin solution measured in a gamma counter was compared with that of the feed solution.
The remainder oE the gIass tube was filled with the solution as was a tube connecting with the inverted feed bottle. The outlet end of the glass tuT~e was ~laced in lO0 ml of well stirred saline, the level 3~ of which was maintained a constant amount (17 cm~
below the level of the feed soIution.
., ' ' ' ' - ;
Characterization of the device consisted of following the amaranth concentration and insulin activity in the product receiver as a function of time in the absence of any current th~ough the coil ~basal ;~
delivery~ and in the presence of such a current ¦ '~
(augmented delivery). ¦~
For the particular device described above, i~, the basal delivery rate of amaranth was 18.5 micrograms I -per minute Qf 0. 027 grams~day and the basal delivery :L0 rate of insulin was 5.5 x 10 2 units/minute or 79 ~,:
units/day~ With a current of 620 mA passing through the coil (60 volts), and the foam compressed ~6 times per minute, the delivery rate of amaranth was incre,ased to 54.5 micrograms per minute. The delivery rate of insulin was increased under these conditions to 0.17 units/minute. The amaranth delivery ra-te was augmented by a factor of 2.95 and the insulin delivery rate was `~
augmented by a factor of 3.06. Since the power is on for about 0.1 seconds per cycle, the average power utili~ation is approximately 1~7 watts for augmented delivery and no power consumption for basal delivery.
Additional experiments, under different conditions, indicate that augmentation factors higher than those given above are obtaina~le. For example, a shorter offset of the piston with respect to the solenoid coil produced larger forces and higher augmented delivery. It ~as also found that ~ligher degrees of augmentat~on are obtained by lowering supply pressure.
However, it appears desirable to maintain a small pos;.tive pressure across the permeable elastic matexial, _g_ -,
.
A piece of transformer iron was then wrapped about the coil to make an external field path.
A feed solution consistîng of 143 ppm amaranth (a tracer molecule~ and 0.35 units/ml of insulin in ; phosphate buffered saline ~pH 7.4)~ was prepared within a sterile infusion bottle. The concentration of ~`
:
amaranth was determined by quantltative ultraviolet spectroscopy, at a wavelength of 220 nm, comparing the absorption of a test solution with the absorption of a set of standards. The addition of a small quantity of insulin labelled~with radiactive iodine tIl25), enabled changes in the concentration of insulin to be determined.
The activity of an insulin solution measured in a gamma counter was compared with that of the feed solution.
The remainder oE the gIass tube was filled with the solution as was a tube connecting with the inverted feed bottle. The outlet end of the glass tuT~e was ~laced in lO0 ml of well stirred saline, the level 3~ of which was maintained a constant amount (17 cm~
below the level of the feed soIution.
., ' ' ' ' - ;
Characterization of the device consisted of following the amaranth concentration and insulin activity in the product receiver as a function of time in the absence of any current th~ough the coil ~basal ;~
delivery~ and in the presence of such a current ¦ '~
(augmented delivery). ¦~
For the particular device described above, i~, the basal delivery rate of amaranth was 18.5 micrograms I -per minute Qf 0. 027 grams~day and the basal delivery :L0 rate of insulin was 5.5 x 10 2 units/minute or 79 ~,:
units/day~ With a current of 620 mA passing through the coil (60 volts), and the foam compressed ~6 times per minute, the delivery rate of amaranth was incre,ased to 54.5 micrograms per minute. The delivery rate of insulin was increased under these conditions to 0.17 units/minute. The amaranth delivery ra-te was augmented by a factor of 2.95 and the insulin delivery rate was `~
augmented by a factor of 3.06. Since the power is on for about 0.1 seconds per cycle, the average power utili~ation is approximately 1~7 watts for augmented delivery and no power consumption for basal delivery.
Additional experiments, under different conditions, indicate that augmentation factors higher than those given above are obtaina~le. For example, a shorter offset of the piston with respect to the solenoid coil produced larger forces and higher augmented delivery. It ~as also found that ~ligher degrees of augmentat~on are obtained by lowering supply pressure.
However, it appears desirable to maintain a small pos;.tive pressure across the permeable elastic matexial, _g_ -,
Claims (3)
1. A device for dispensing a pharmaceutical comprising:
- an elastic material permeable to the pharmaceutical;
- a housing for confining the elastic material, said housing having an inlet for connection with a supply of the pharmaceutical, and an outlet for delivery;
- a reciprocatable piston for compressing the elastic material; and - means for activating said piston;
the device being operative to deliver the pharmaceutical at a basal rate when the piston is inoperative, and at an augmented rate when the elastic material is compressed.
- an elastic material permeable to the pharmaceutical;
- a housing for confining the elastic material, said housing having an inlet for connection with a supply of the pharmaceutical, and an outlet for delivery;
- a reciprocatable piston for compressing the elastic material; and - means for activating said piston;
the device being operative to deliver the pharmaceutical at a basal rate when the piston is inoperative, and at an augmented rate when the elastic material is compressed.
2. The device of claim 1 wherein the means for activating the piston comprises a solenoid operatively connected to the piston.
3. The device of claim 1 wherein the means for activating the piston is responsive to sensing means indicating a requirement for the pharmaceutical.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US859,314 | 1977-12-12 | ||
| US05/859,314 US4209014A (en) | 1977-12-12 | 1977-12-12 | Dispensing device for medicaments |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1103545A true CA1103545A (en) | 1981-06-23 |
Family
ID=25330588
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA317,906A Expired CA1103545A (en) | 1977-12-12 | 1978-12-12 | Dispensing device for pharmaceuticals |
Country Status (2)
| Country | Link |
|---|---|
| US (1) | US4209014A (en) |
| CA (1) | CA1103545A (en) |
Families Citing this family (38)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4525165A (en) * | 1979-04-27 | 1985-06-25 | The Johns Hopkins University | Fluid handling system for medication infusion system |
| US4299220A (en) * | 1979-05-03 | 1981-11-10 | The Regents Of The University Of Minnesota | Implantable drug infusion regulator |
| US4468221A (en) * | 1981-04-10 | 1984-08-28 | Parker-Hannifin Corporation | Medication infusion pump |
| US4447233A (en) * | 1981-04-10 | 1984-05-08 | Parker-Hannifin Corporation | Medication infusion pump |
| US4417576A (en) * | 1982-02-25 | 1983-11-29 | Baran Ostap E | Double-wall surgical cuff |
| US4482346A (en) * | 1982-07-30 | 1984-11-13 | Consolidated Controls Corporation | Apparatus for infusing medication into the body |
| US4705503A (en) * | 1986-02-03 | 1987-11-10 | Regents Of The University Of Minnesota | Metabolite sensor including a chemical concentration sensitive flow controller for a drug delivery system |
| GB8602733D0 (en) * | 1986-02-04 | 1986-03-12 | Univ Brunel | Syringe |
| US4701180A (en) * | 1986-02-19 | 1987-10-20 | Kelly L Thomas | Implanted anchor and insert with analog display |
| US4713054A (en) * | 1986-02-19 | 1987-12-15 | Kelly L Thomas | Implanted muscle powered drug dispensing system |
| AT384737B (en) * | 1986-04-04 | 1987-12-28 | Thoma Dipl Ing Dr Techn Herwig | DEVICE FOR CONTINUOUSLY DELIVERING LIQUID MEDICINAL PRODUCTS |
| EP0317705B1 (en) * | 1987-11-25 | 1992-09-30 | Siemens Aktiengesellschaft | Device for the controlled dosage and infusion of liquids from a reservoir into the body |
| CA1294843C (en) * | 1988-04-07 | 1992-01-28 | Paul Y. Wang | Implant for percutaneous sampling of serous fluid and for delivering drug upon external compression |
| US5062841A (en) * | 1988-08-12 | 1991-11-05 | The Regents Of The University Of California | Implantable, self-regulating mechanochemical insulin pump |
| WO1990012611A1 (en) * | 1989-04-21 | 1990-11-01 | Ash Medical Systems, Inc. | Non-intravascular infusion access device |
| US5011477A (en) * | 1989-04-21 | 1991-04-30 | Baxter International Inc. | Continuous/bolus infusor |
| US5562909A (en) * | 1993-07-12 | 1996-10-08 | Massachusetts Institute Of Technology | Phosphazene polyelectrolytes as immunoadjuvants |
| US5743879A (en) * | 1994-12-02 | 1998-04-28 | Science Incorporated | Medicament dispenser |
| JPH10510450A (en) * | 1994-12-02 | 1998-10-13 | サイエンス インコーポレイテッド | Drug dispensing device |
| US6030363A (en) * | 1994-12-02 | 2000-02-29 | Science Incorporated | Medicament dispenser |
| US6042561A (en) * | 1997-10-22 | 2000-03-28 | Ash Medical Systems, Inc. | Non-intravascular infusion access device |
| US5906597A (en) * | 1998-06-09 | 1999-05-25 | I-Flow Corporation | Patient-controlled drug administration device |
| US6575961B2 (en) * | 2001-02-20 | 2003-06-10 | Microlin, L.C. | Fluid delivery device and associated method |
| EP1476209B1 (en) * | 2002-02-18 | 2008-07-30 | Danfoss A/S | Device for administering of medication in fluid form |
| US7235164B2 (en) | 2002-10-18 | 2007-06-26 | Eksigent Technologies, Llc | Electrokinetic pump having capacitive electrodes |
| ES2737835T3 (en) * | 2003-04-23 | 2020-01-16 | Valeritas Inc | Hydraulically driven pump for long-term medication administration |
| US9089636B2 (en) | 2004-07-02 | 2015-07-28 | Valeritas, Inc. | Methods and devices for delivering GLP-1 and uses thereof |
| DE602004017916D1 (en) * | 2004-08-19 | 2009-01-02 | Danfoss As | DEVICE FOR IMPLEMENTING MICRO ANALYSIS |
| DK1957794T3 (en) * | 2005-11-23 | 2014-08-11 | Eksigent Technologies Llc | Electrokinetic pump designs and drug delivery systems |
| SG173319A1 (en) | 2006-03-30 | 2011-08-29 | Valeritas Inc | Multi-cartridge fluid delivery device |
| US7892213B2 (en) * | 2007-04-20 | 2011-02-22 | Carefusion 303, Inc. | Fluid flow control system having capillary fluid flow restrictor |
| DE102007049446A1 (en) * | 2007-10-16 | 2009-04-23 | Cequr Aps | Catheter introducer |
| US8449500B2 (en) * | 2007-11-16 | 2013-05-28 | Baxter International Inc. | Flow pulsatility dampening devices for closed-loop controlled infusion systems |
| US10265454B2 (en) | 2008-07-25 | 2019-04-23 | Baxter International Inc. | Dialysis system with flow regulation device |
| US8366667B2 (en) | 2010-02-11 | 2013-02-05 | Baxter International Inc. | Flow pulsatility dampening devices |
| TWI403342B (en) * | 2010-08-09 | 2013-08-01 | Wiswong Technology Corp | Fluid dispensing device |
| US9211378B2 (en) | 2010-10-22 | 2015-12-15 | Cequr Sa | Methods and systems for dosing a medicament |
| CA2834708A1 (en) | 2011-05-05 | 2012-11-08 | Eksigent Technologies, Llc | Gel coupling for electrokinetic delivery systems |
Family Cites Families (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US1213655A (en) * | 1915-07-28 | 1917-01-23 | John M Keil | Greaser. |
| US1410530A (en) * | 1919-03-29 | 1922-03-21 | Larche Jean Etienne | Pump with permeable piston for multiple purposes |
| US1578517A (en) * | 1924-12-23 | 1926-03-30 | George N Hein | Valve piston and barrel construction for hypodermic syringes |
| US1860277A (en) * | 1931-10-21 | 1932-05-24 | Dennis William | Brush |
| US2605765A (en) * | 1947-06-05 | 1952-08-05 | Kollsman Paul | Automatic syringe |
| US3512940A (en) * | 1968-12-30 | 1970-05-19 | Justin J Shapiro | Test tube filter device |
| US3604417A (en) * | 1970-03-31 | 1971-09-14 | Wayne Henry Linkenheimer | Osmotic fluid reservoir for osmotically activated long-term continuous injector device |
| FR2172443A5 (en) * | 1972-02-11 | 1973-09-28 | Anvar | |
| US3975350A (en) * | 1972-08-02 | 1976-08-17 | Princeton Polymer Laboratories, Incorporated | Hydrophilic or hydrogel carrier systems such as coatings, body implants and other articles |
| US4003379A (en) * | 1974-04-23 | 1977-01-18 | Ellinwood Jr Everett H | Apparatus and method for implanted self-powered medication dispensing |
| US3991750A (en) * | 1975-04-28 | 1976-11-16 | Syntex Corporation | Dromostanolone propionate implant pellet useful for producing weight gains in animals and suppressing estrus in female animals |
| US4055175A (en) * | 1976-05-07 | 1977-10-25 | Miles Laboratories, Inc. | Blood glucose control apparatus |
| US4103686A (en) * | 1977-03-29 | 1978-08-01 | Burron Medical Products, Inc. | Dual valve assembly |
-
1977
- 1977-12-12 US US05/859,314 patent/US4209014A/en not_active Expired - Lifetime
-
1978
- 1978-12-12 CA CA317,906A patent/CA1103545A/en not_active Expired
Also Published As
| Publication number | Publication date |
|---|---|
| US4209014A (en) | 1980-06-24 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKEX | Expiry |