CA1169323A - Insulin infusion device - Google Patents
Insulin infusion deviceInfo
- Publication number
- CA1169323A CA1169323A CA000353268A CA353268A CA1169323A CA 1169323 A CA1169323 A CA 1169323A CA 000353268 A CA000353268 A CA 000353268A CA 353268 A CA353268 A CA 353268A CA 1169323 A CA1169323 A CA 1169323A
- Authority
- CA
- Canada
- Prior art keywords
- medicament
- tube
- drive means
- pulses
- insulin
- 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
- A61M5/148—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons flexible, e.g. independent bags
-
- 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
- A61M2005/14268—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body with a reusable and a disposable component
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
- A61M2005/14506—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons mechanically driven, e.g. spring or clockwork
-
- 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
- Y10S128/12—Pressure infusion
Abstract
ABSTRACT OF THE DISCLOSURE
The invention provides an improved device for the injection of medicament such as insulin subcutaneously. The device provides discrete regular injections from a tube adapted to contain the medicament and having a vented first end. Medicament is squeezed from the tube through its other end in discrete amounts programmed to provide a basal injection rate. Additional discrete injections can be provided at the user's discretion thereby providing the user with sufficient flexibility to control sudden demands for medicament while nevertheless leaving the basal injection schedule essentially uninterrupted.
The invention provides an improved device for the injection of medicament such as insulin subcutaneously. The device provides discrete regular injections from a tube adapted to contain the medicament and having a vented first end. Medicament is squeezed from the tube through its other end in discrete amounts programmed to provide a basal injection rate. Additional discrete injections can be provided at the user's discretion thereby providing the user with sufficient flexibility to control sudden demands for medicament while nevertheless leaving the basal injection schedule essentially uninterrupted.
Description
1 ;1 6~3~3 This invention relates to a device for controlled subcutaneous injection of medicaments such as insulin in discrete ~uantities at selected timed intervals to provide a user's daily requirement at a basal rate, and for permitting additional discrete quantities at time of increased need at the discretion of the user.
Although the present invention will be decribed for use with the treatment of diabetes mellitus, it will be apparent that other treatments requiring similar extended periods of injection of a medicament are possible using the same device.
The current standard therapy of insulin dependent diabetics with depot insulin injections fails to normalize entirely plasma glucose levels as well as the other metabolic abnormalities of the diseaseO The consequences of this imperfect metabolic regulation are believed to significantly contribute to the long term chronic and disabling complications of diabetes mellitus. Recent studies employing crude mechanical devices designed to infuse insulin continuously or by multiple small injections to meet fluctuations in daily requirements have shown a marked improvement in glycemic and other metabolic and hormonal profiles in diabetic subjects.
Although such mechanical devices are an improvement over daily injections, they nevertheless suffer from `:. ~, ' ~ ., ' , 3 ~ ~
disadvantages which -the present invention is intended to overcome.
For a mechanical device to be acceptable for subcutaneous injection of insulin and the like, the device should be compact, and readily located on the pa-tient adjacent sites where a needle can be inserted subcutaneously. Preferably the device should be capable of providing a basal rate of injection while at the same time being capable of use to provide discrete additional doses at the patient's discretion and as directed. The device should also provide a visible and readily recognized indication of whether or not the device is working as well as the amount of medicament injected and the amount remaining in the device. Preferably the user should be able to over-ride the driving mechanism of the device so that in the event of complete failure, the device can be used manually for sufficient time to permit the user to seek help.
In accordance with the present invention there is provided a device for the subcutaneous injection of a predetermined volume of liquid medicament over a predetermined time interval, the device comprising:
a timer for producing a preselected number of individual pulses at regular intervals;
a flexible tube for containing all of the predetermined volume of liquid medicament;
drive ~eans in direct contact with the tube to change the volume of the tube for dispansing medicament from the tube;
, ~ 3 ~
' ` ' ~ '. ~ ,~ , 3 3 ~ ~
means coupling the timer to the drive means for dispensing the medicament in a series o~ discrete amounts in response to the pulses ~rom the -timer, the number of pulses being preselectable by the user to cause the drive means to dispense the predetermined volume o-f the liquid medicament;
a catheter coupled to the tube for receiving the medicament and in~ection the medicament subcutaneously.
The invention will be better understood with reference to the following description taken in combination with the drawings, in which:
Fig. 1 is a perspective and somewhat diagrammatic view of a preferred embodiment of a dévice in position on the user's wrist;
Fig. 2 is a sectional view o~ the device showing the relationship between a nip and a tube containing medicament such as insulin;
Fig~ 3 is a schematic diagram illustrating the control mechanism used in the device; and ~ ig. 4 is a view similar to Fig. 3 illus-trating an alternative embodiment o~ the control system.
Reference is first made to Fig. 1 which illustrates a preferred embodiment o~ the device designated generally by the numeral 20 and shown positioned on a user's wrist. In this embodiment the device is attached by a band 22 and is feeding insulin tor other medicament) subscutaneously by way o~ a needle 24. The needle is attached in conventional ~ashion by adhesive strapping 26. It will be seen that the device includes a fixed scale 28 cooperating with a moving element 30 .
- :
. .
` "' ' :
~ ~ 6~3~3 having a pointer adjacent the scale. This pointer indicates the number of discrete pulses of insulin available from the device and not yet used.. ~ith each pulse the pointer moves one division of the scale and these pulses are timed as will be described. Also visible in Fig. l is a small handle 32 which can be lifted from the plane of the dial 28 to rotate a spindle 34 for winding a clockwork mechanism thereby storing energy for use in moving insulin to the needle 24. The handle is arranged so that it must be lifted out before it can be turned so that it over-rides an escapement mechanism which is to be described. Such arrangements are conventional in clockwork machinery generally. For instance a similar arrangement is used when setting the time on a mechanical clock.
As also seen in Fig. 1, the housing of the device contains a small flush button 36 which permits the user to ;~
over-ride an electronic timing circuit to provide a desired number of extra pulses of insulin which pulses are readily visible by the movement of the element 30 and associated pointer around the scale 28. This permits the user to receive increased dosage of insulin prior to meals and at other times of increased demand. However such extra dosing will not affect the basal rate indicated by prior programming of the device as will be described.
Tarning now to Flg. 2~ which is a section of the :; :
'`
.~i . ~ . . . ~
3 ~ ~-3 device shown in Fig. 1, there is a housing 38 disposed about a central axis 40 and de~ining a cavity having an outer wall 42 which is disposed about the axis 40. This wall is positioned to restrain a flexible tube 44 of larger inside diameter having a vented or open end 46 and connected to a further tube 48 of substantially smaller inside diameter leading to the needle 24 (Fig. 1). A roller 50 is held in position by a structure not shown in Fig. 2 on a pin 52 and is restrained to move about the axis 40 forming a nip between the roller 50 and the outer wall 42. Consequently as the roller is made to move about axis 40, there is a displacement of liquid contained between the nip and the needle through the needle causing subcutaneous injection. The inside diameter of the tube 44 is chosen so that deLivery from the needle corresponds to the calibration on the fixed scale 28.
A preferred embodiment of a control circuit is shown diagrammatically in Fig. 3. A CMOS (complementary metal oxide semiconductor) variable frequency oscillator is used to create a square waveform which is fed to a CMOS divider. The frequency of the waveform can be varied over a range of 8 to 1 by a control 54 and it is possible to identi~y the frequency from a test point 56. The waveform leaving the oscillator 53 is shown diagrammatically in Fig. 3 and the divider then reduces the frequency resulting in intermittent pulses which are then fed to a stepper motor driver. An associated motor .
32~
drives a pinion 58 which is in engagement with a gear wheel 60. The gear wheel carries the pin 52 (Fig~ 2) associated with the roller so that each impulse ~rom the CMOS divider causes the stepper motor to advance the pinion 58 a discrete amount which in turn moves the gear wheel 60. As a result the nip moves around the housing 38 sufficient to cause medicament to be injected subcutaneously.
It will be appreciated that the power required to drive the stepper motor may be available from a miniature battery of the type used for the electronics necessary to drive the variable frequency oscillator and the divider.
Although the connections have not been shown, it ls obvious that additional power could be provided to the stepper motor by way of a separate battery or any other convenient means.
If necessary, an additional battery for this purpose could be attached to the strap 22 of the structure shown in Fig. 1 or remotely as preferred.
Although the preEerred embodiment has many advantages, it will be appreciated that it can take difEerent forms. For instance it could be attached to a patient's abdomen which may be advantageous in some instances but of course makes the visual display less convenient than that shown in Fig. 1.
The structure associated with the stepper motor and roller forms in effect an escapement mechanism. An ~;
.
` ~ 7 _ ~ ~, ;: :
~ .5 8~3~3 alternative escapement mechanism is shown in Fig. 4. As with the structure shown in Fig. 1, a variable frequency oscillator and divider are used but the pulse provided by the divider is fed to a solenoid actuator which again may be fed by an independent battery source. This actuator operates a solenoid 62 and a mechanical rocking escapement element 64. This element is associated with a wheel 66 which, with respect to the roller 50 (Fig. 2) corresponds to the gear wheel 60 shown in Fig. 3.
To use the inventive devices, a user would take a new disposable tube and needle assembly from a sterile package and insert the pump tube into the housing to take up the position shown in Fig. 2. The user would then advance the handle 32 (Fig. 1) in a counter-clockwise direction until the pointer on the element 30 indicated the number of units -to be dispensed during the following 24 hours. The protective needle guard would then be removed from the needle and the needLe inserted into a insulin vial before advancing the timing mechanism (and the arrow on element 30 to zero) to e~pel the air in the tube into the insulin vial. After this has been done, the element would be reversed to aspirate the total daily dose of insulin required ending when the pointer had reached a figure on the scale 28 correspondong to the anticipated need for the day.
Following this the user would then insert the needle into the subcutaneous tissues, tape it in place and tie the ., ..
,~:
-: :
3 ~ 3 h~nd 22 about the arm in watch-like fashion~ Alternatively it could be attached by adhesive or by a belt to the abdomen.
The advancement of the mechanism would depend on the escapement mechanism so that at nominal settings a 1 unit quantity of insulin would be administered each hour. For patients requiring more insulin, the fundamental frequency of the timer device can be adjusted by the control 54 (Fig. 3) so that it advances at a rate slightly more often than once an hour. Conversely, ~or a patient requiring slightly less insulin, this electronic timer can be adjusted in such a way that intermittent injections in the basal period occur less than once per hour. These adjustments would be made by technical staff at the direction of the user's medical adviser.
The propulsion mechanism of the pump includes a watch ~5 or clock spring which is rewound each day by the patient during the filling cycle. It is biased in such a way that the spring is always under tension. The control o~ the device by the electronic timer is with a safety escapement mechanism which prevents the accidental injection of the entire contents of the pump tube so the device can only fail safe by not injecting insulin. Lifting the handle 32 (Fig. 1) overcomes this safety feature and allows the device to be set manually~
At mealtime the device is actuated by depressing the flush button 36 on the surface of the housing which would in turn activate the el-ctronlc escapement mechanlsm and advance g .,, ~
'~`
~ 3~
the device by 1 calibrated graduation, thereby administering 1 unit of insulin. Patients will be instructed by their physicians initially on the use of the device and will adapt their insulin regimen according to their dietary habits. In this way, meal insulin may involve amounts of insulin ranging between 2 and 15 units, depending on the type of the meal and the patient's requirements.
This is a novel device which is an improvement over existing devices in that it uses an electronically controlled escapement mechanism for the control of the administration of a drug. The device does not include an external reservoir to contain the drug and only contains enough drug for a single day's use. On successive days, the patient replaces the disposable portion, recharges it and resets the mechanism.
The adjustment of the electronic timer mechanism allows the establishment of a suitable basal rate. It will be appreciated that the pump tube is vented and only orms a reservoir in so far that it is contained between the nip and the needle. Furthermore, because of the intermittent application of insulin, the device is not suitable for the treatment of diabetes by intravenous insulin delivery During the long time between pulses, blood would diffuse into the needle and eventually clot in situ preventing the pump from ad~ancing or distributing insulin and there is a risk that the pump will overcome the resistance of the clot and inject this :, , . -- 10 --``; ~
:.:
-. i ~6~3~3 into the circulation with adverse aEfects. It is also foreseen that the use of a needle in the blood vessel would not be an appropriate method for gaining access thereto, but it is foreseen that in some circumstances, a so~t rubber catheter in lieu of the needle could be placed in the subcutaneous tissue for the delivery of insulin for longer periods of time than a day. This particular alternative configuration may be useful in animal studies.
SUPPLEMENTARY DISCLOSURE
Figure 5 is a sectional side view of the end of a tube used in an alternative embodiment of the invention and drawn to a larger scale than Fig. 1.
Alternative pump tube structures could be used within the scope of the invention. The vented end of the tube could include a one-way valve or flap to allow air to be expelled but which limits air flow back into the tube. In this case the tube would simply collapse behind the roller as medicament is dispensed. Another pump tube can be sealed at the end as seen in Fig. 5. In this embodiment the end of the tube is closed by a small stopper or bung 68 having a thin wall or septum 70.
In use the pump tube shown in Fig. 5 is filled using a syringe and needle which pierces the septum. Once full o medicament, the pump tube is placed in the device and after reassembly, the over-ride is used to move the pointer to register with the number if discrete injections required~ The outlet tube 48 is then connected for injecting the remaining :
- 10 ~
~; . .
- - , .. .
, ~, ' ' ~:
,~ , :
3 ~ 3 medicament in the same manner as described previously. BecauSe the tube is not vented it will si.mply collapse behind the roller as the medicament is dispensed in front of the roller.
These and other modifications are within the scope of the invention as described and c]aimed.
-- 11 -- , .
. ~. : ~ . . : :
Although the present invention will be decribed for use with the treatment of diabetes mellitus, it will be apparent that other treatments requiring similar extended periods of injection of a medicament are possible using the same device.
The current standard therapy of insulin dependent diabetics with depot insulin injections fails to normalize entirely plasma glucose levels as well as the other metabolic abnormalities of the diseaseO The consequences of this imperfect metabolic regulation are believed to significantly contribute to the long term chronic and disabling complications of diabetes mellitus. Recent studies employing crude mechanical devices designed to infuse insulin continuously or by multiple small injections to meet fluctuations in daily requirements have shown a marked improvement in glycemic and other metabolic and hormonal profiles in diabetic subjects.
Although such mechanical devices are an improvement over daily injections, they nevertheless suffer from `:. ~, ' ~ ., ' , 3 ~ ~
disadvantages which -the present invention is intended to overcome.
For a mechanical device to be acceptable for subcutaneous injection of insulin and the like, the device should be compact, and readily located on the pa-tient adjacent sites where a needle can be inserted subcutaneously. Preferably the device should be capable of providing a basal rate of injection while at the same time being capable of use to provide discrete additional doses at the patient's discretion and as directed. The device should also provide a visible and readily recognized indication of whether or not the device is working as well as the amount of medicament injected and the amount remaining in the device. Preferably the user should be able to over-ride the driving mechanism of the device so that in the event of complete failure, the device can be used manually for sufficient time to permit the user to seek help.
In accordance with the present invention there is provided a device for the subcutaneous injection of a predetermined volume of liquid medicament over a predetermined time interval, the device comprising:
a timer for producing a preselected number of individual pulses at regular intervals;
a flexible tube for containing all of the predetermined volume of liquid medicament;
drive ~eans in direct contact with the tube to change the volume of the tube for dispansing medicament from the tube;
, ~ 3 ~
' ` ' ~ '. ~ ,~ , 3 3 ~ ~
means coupling the timer to the drive means for dispensing the medicament in a series o~ discrete amounts in response to the pulses ~rom the -timer, the number of pulses being preselectable by the user to cause the drive means to dispense the predetermined volume o-f the liquid medicament;
a catheter coupled to the tube for receiving the medicament and in~ection the medicament subcutaneously.
The invention will be better understood with reference to the following description taken in combination with the drawings, in which:
Fig. 1 is a perspective and somewhat diagrammatic view of a preferred embodiment of a dévice in position on the user's wrist;
Fig. 2 is a sectional view o~ the device showing the relationship between a nip and a tube containing medicament such as insulin;
Fig~ 3 is a schematic diagram illustrating the control mechanism used in the device; and ~ ig. 4 is a view similar to Fig. 3 illus-trating an alternative embodiment o~ the control system.
Reference is first made to Fig. 1 which illustrates a preferred embodiment o~ the device designated generally by the numeral 20 and shown positioned on a user's wrist. In this embodiment the device is attached by a band 22 and is feeding insulin tor other medicament) subscutaneously by way o~ a needle 24. The needle is attached in conventional ~ashion by adhesive strapping 26. It will be seen that the device includes a fixed scale 28 cooperating with a moving element 30 .
- :
. .
` "' ' :
~ ~ 6~3~3 having a pointer adjacent the scale. This pointer indicates the number of discrete pulses of insulin available from the device and not yet used.. ~ith each pulse the pointer moves one division of the scale and these pulses are timed as will be described. Also visible in Fig. l is a small handle 32 which can be lifted from the plane of the dial 28 to rotate a spindle 34 for winding a clockwork mechanism thereby storing energy for use in moving insulin to the needle 24. The handle is arranged so that it must be lifted out before it can be turned so that it over-rides an escapement mechanism which is to be described. Such arrangements are conventional in clockwork machinery generally. For instance a similar arrangement is used when setting the time on a mechanical clock.
As also seen in Fig. 1, the housing of the device contains a small flush button 36 which permits the user to ;~
over-ride an electronic timing circuit to provide a desired number of extra pulses of insulin which pulses are readily visible by the movement of the element 30 and associated pointer around the scale 28. This permits the user to receive increased dosage of insulin prior to meals and at other times of increased demand. However such extra dosing will not affect the basal rate indicated by prior programming of the device as will be described.
Tarning now to Flg. 2~ which is a section of the :; :
'`
.~i . ~ . . . ~
3 ~ ~-3 device shown in Fig. 1, there is a housing 38 disposed about a central axis 40 and de~ining a cavity having an outer wall 42 which is disposed about the axis 40. This wall is positioned to restrain a flexible tube 44 of larger inside diameter having a vented or open end 46 and connected to a further tube 48 of substantially smaller inside diameter leading to the needle 24 (Fig. 1). A roller 50 is held in position by a structure not shown in Fig. 2 on a pin 52 and is restrained to move about the axis 40 forming a nip between the roller 50 and the outer wall 42. Consequently as the roller is made to move about axis 40, there is a displacement of liquid contained between the nip and the needle through the needle causing subcutaneous injection. The inside diameter of the tube 44 is chosen so that deLivery from the needle corresponds to the calibration on the fixed scale 28.
A preferred embodiment of a control circuit is shown diagrammatically in Fig. 3. A CMOS (complementary metal oxide semiconductor) variable frequency oscillator is used to create a square waveform which is fed to a CMOS divider. The frequency of the waveform can be varied over a range of 8 to 1 by a control 54 and it is possible to identi~y the frequency from a test point 56. The waveform leaving the oscillator 53 is shown diagrammatically in Fig. 3 and the divider then reduces the frequency resulting in intermittent pulses which are then fed to a stepper motor driver. An associated motor .
32~
drives a pinion 58 which is in engagement with a gear wheel 60. The gear wheel carries the pin 52 (Fig~ 2) associated with the roller so that each impulse ~rom the CMOS divider causes the stepper motor to advance the pinion 58 a discrete amount which in turn moves the gear wheel 60. As a result the nip moves around the housing 38 sufficient to cause medicament to be injected subcutaneously.
It will be appreciated that the power required to drive the stepper motor may be available from a miniature battery of the type used for the electronics necessary to drive the variable frequency oscillator and the divider.
Although the connections have not been shown, it ls obvious that additional power could be provided to the stepper motor by way of a separate battery or any other convenient means.
If necessary, an additional battery for this purpose could be attached to the strap 22 of the structure shown in Fig. 1 or remotely as preferred.
Although the preEerred embodiment has many advantages, it will be appreciated that it can take difEerent forms. For instance it could be attached to a patient's abdomen which may be advantageous in some instances but of course makes the visual display less convenient than that shown in Fig. 1.
The structure associated with the stepper motor and roller forms in effect an escapement mechanism. An ~;
.
` ~ 7 _ ~ ~, ;: :
~ .5 8~3~3 alternative escapement mechanism is shown in Fig. 4. As with the structure shown in Fig. 1, a variable frequency oscillator and divider are used but the pulse provided by the divider is fed to a solenoid actuator which again may be fed by an independent battery source. This actuator operates a solenoid 62 and a mechanical rocking escapement element 64. This element is associated with a wheel 66 which, with respect to the roller 50 (Fig. 2) corresponds to the gear wheel 60 shown in Fig. 3.
To use the inventive devices, a user would take a new disposable tube and needle assembly from a sterile package and insert the pump tube into the housing to take up the position shown in Fig. 2. The user would then advance the handle 32 (Fig. 1) in a counter-clockwise direction until the pointer on the element 30 indicated the number of units -to be dispensed during the following 24 hours. The protective needle guard would then be removed from the needle and the needLe inserted into a insulin vial before advancing the timing mechanism (and the arrow on element 30 to zero) to e~pel the air in the tube into the insulin vial. After this has been done, the element would be reversed to aspirate the total daily dose of insulin required ending when the pointer had reached a figure on the scale 28 correspondong to the anticipated need for the day.
Following this the user would then insert the needle into the subcutaneous tissues, tape it in place and tie the ., ..
,~:
-: :
3 ~ 3 h~nd 22 about the arm in watch-like fashion~ Alternatively it could be attached by adhesive or by a belt to the abdomen.
The advancement of the mechanism would depend on the escapement mechanism so that at nominal settings a 1 unit quantity of insulin would be administered each hour. For patients requiring more insulin, the fundamental frequency of the timer device can be adjusted by the control 54 (Fig. 3) so that it advances at a rate slightly more often than once an hour. Conversely, ~or a patient requiring slightly less insulin, this electronic timer can be adjusted in such a way that intermittent injections in the basal period occur less than once per hour. These adjustments would be made by technical staff at the direction of the user's medical adviser.
The propulsion mechanism of the pump includes a watch ~5 or clock spring which is rewound each day by the patient during the filling cycle. It is biased in such a way that the spring is always under tension. The control o~ the device by the electronic timer is with a safety escapement mechanism which prevents the accidental injection of the entire contents of the pump tube so the device can only fail safe by not injecting insulin. Lifting the handle 32 (Fig. 1) overcomes this safety feature and allows the device to be set manually~
At mealtime the device is actuated by depressing the flush button 36 on the surface of the housing which would in turn activate the el-ctronlc escapement mechanlsm and advance g .,, ~
'~`
~ 3~
the device by 1 calibrated graduation, thereby administering 1 unit of insulin. Patients will be instructed by their physicians initially on the use of the device and will adapt their insulin regimen according to their dietary habits. In this way, meal insulin may involve amounts of insulin ranging between 2 and 15 units, depending on the type of the meal and the patient's requirements.
This is a novel device which is an improvement over existing devices in that it uses an electronically controlled escapement mechanism for the control of the administration of a drug. The device does not include an external reservoir to contain the drug and only contains enough drug for a single day's use. On successive days, the patient replaces the disposable portion, recharges it and resets the mechanism.
The adjustment of the electronic timer mechanism allows the establishment of a suitable basal rate. It will be appreciated that the pump tube is vented and only orms a reservoir in so far that it is contained between the nip and the needle. Furthermore, because of the intermittent application of insulin, the device is not suitable for the treatment of diabetes by intravenous insulin delivery During the long time between pulses, blood would diffuse into the needle and eventually clot in situ preventing the pump from ad~ancing or distributing insulin and there is a risk that the pump will overcome the resistance of the clot and inject this :, , . -- 10 --``; ~
:.:
-. i ~6~3~3 into the circulation with adverse aEfects. It is also foreseen that the use of a needle in the blood vessel would not be an appropriate method for gaining access thereto, but it is foreseen that in some circumstances, a so~t rubber catheter in lieu of the needle could be placed in the subcutaneous tissue for the delivery of insulin for longer periods of time than a day. This particular alternative configuration may be useful in animal studies.
SUPPLEMENTARY DISCLOSURE
Figure 5 is a sectional side view of the end of a tube used in an alternative embodiment of the invention and drawn to a larger scale than Fig. 1.
Alternative pump tube structures could be used within the scope of the invention. The vented end of the tube could include a one-way valve or flap to allow air to be expelled but which limits air flow back into the tube. In this case the tube would simply collapse behind the roller as medicament is dispensed. Another pump tube can be sealed at the end as seen in Fig. 5. In this embodiment the end of the tube is closed by a small stopper or bung 68 having a thin wall or septum 70.
In use the pump tube shown in Fig. 5 is filled using a syringe and needle which pierces the septum. Once full o medicament, the pump tube is placed in the device and after reassembly, the over-ride is used to move the pointer to register with the number if discrete injections required~ The outlet tube 48 is then connected for injecting the remaining :
- 10 ~
~; . .
- - , .. .
, ~, ' ' ~:
,~ , :
3 ~ 3 medicament in the same manner as described previously. BecauSe the tube is not vented it will si.mply collapse behind the roller as the medicament is dispensed in front of the roller.
These and other modifications are within the scope of the invention as described and c]aimed.
-- 11 -- , .
. ~. : ~ . . : :
Claims (4)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. A device for the subcutaneous injection of a predetermined volume of liquid medicament over a predetermined time interval, the device comprising:
a timer for producing a preselected number of individual pulses at regular intervals;
a flexible tube for containing all of the predetermined volume of liquid medicament;
drive means in direct contact with the tube to change the volume of the tube for dispensing medicament from the tube;
means coupling the timer to the drive means for dispensing the medicament in a series of discrete amounts in response to the pulses from the timer, the number of pulses being preselectable by the user to cause the drive means to dispense the predetermined volume of the liquid medicament;
a CATHETER coupled to the tube for receiving the medicament and injecting the medicament subcutaneously.
a timer for producing a preselected number of individual pulses at regular intervals;
a flexible tube for containing all of the predetermined volume of liquid medicament;
drive means in direct contact with the tube to change the volume of the tube for dispensing medicament from the tube;
means coupling the timer to the drive means for dispensing the medicament in a series of discrete amounts in response to the pulses from the timer, the number of pulses being preselectable by the user to cause the drive means to dispense the predetermined volume of the liquid medicament;
a CATHETER coupled to the tube for receiving the medicament and injecting the medicament subcutaneously.
2. A device as claimed in Claim 1 wherein the drive means is rotatable and all of the predetermined amount of medicament is dispensable within a single revolution of the drive means.
CLAIMS SUPPORTED BY THE SUPPLEMENTARY DISCLOSURE
CLAIMS SUPPORTED BY THE SUPPLEMENTARY DISCLOSURE
3. A device as claimed in Claim 1 in which the flexible tube has an end structure adapted to prevent air flowing into the tube as the liquid medicament is expelled from the tube.
4. A device as claimed in Claim 3 and further including a dial coupled to the drive means to indicate the number of energy pulses available, and hence with reference to a starting point, how many have been used.
Priority Applications (12)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CA000353268A CA1169323A (en) | 1980-06-03 | 1980-06-03 | Insulin infusion device |
US06/267,364 US4601707A (en) | 1980-06-03 | 1981-05-22 | Insulin infusion device |
GB8116435A GB2077110B (en) | 1980-06-03 | 1981-05-29 | Insulin infusion device |
NL8102652A NL8102652A (en) | 1980-06-03 | 1981-06-02 | INSULIN INFUSION DEVICE. |
SE8103469A SE444509B (en) | 1980-06-03 | 1981-06-02 | PORTABLE DEVICE FOR SUBCUTAN INJECTION OF LIQUID MEDICINES |
LU83407A LU83407A1 (en) | 1980-06-03 | 1981-06-02 | INSULIN INFUSION DEVICE |
DE3121888A DE3121888C2 (en) | 1980-06-03 | 1981-06-02 | Portable device for subcutaneous injection of a liquid drug |
BE0/204980A BE889071A (en) | 1980-06-03 | 1981-06-03 | INSULIN INFUSION DEVICE |
JP8554081A JPS5722761A (en) | 1980-06-03 | 1981-06-03 | Injector for medicine |
FR8111002A FR2486403B1 (en) | 1980-06-03 | 1981-06-03 | PORTABLE SUBCUTANEOUS MEDICAMENT INJECTION DEVICE |
CA000421583A CA1169324A (en) | 1980-06-03 | 1983-02-14 | Insulin infusion device |
CN96108173A CN1169324A (en) | 1980-06-03 | 1996-06-28 | Electric rotary-rubbing magnetic plate |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CA000353268A CA1169323A (en) | 1980-06-03 | 1980-06-03 | Insulin infusion device |
Publications (1)
Publication Number | Publication Date |
---|---|
CA1169323A true CA1169323A (en) | 1984-06-19 |
Family
ID=4117097
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA000353268A Expired CA1169323A (en) | 1980-06-03 | 1980-06-03 | Insulin infusion device |
CA000421583A Expired CA1169324A (en) | 1980-06-03 | 1983-02-14 | Insulin infusion device |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA000421583A Expired CA1169324A (en) | 1980-06-03 | 1983-02-14 | Insulin infusion device |
Country Status (11)
Country | Link |
---|---|
US (1) | US4601707A (en) |
JP (1) | JPS5722761A (en) |
CN (1) | CN1169324A (en) |
BE (1) | BE889071A (en) |
CA (2) | CA1169323A (en) |
DE (1) | DE3121888C2 (en) |
FR (1) | FR2486403B1 (en) |
GB (1) | GB2077110B (en) |
LU (1) | LU83407A1 (en) |
NL (1) | NL8102652A (en) |
SE (1) | SE444509B (en) |
Families Citing this family (131)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4685902A (en) * | 1983-08-24 | 1987-08-11 | Becton, Dickinson And Company | Disposable reservoir cassette |
DE3439322A1 (en) * | 1984-10-26 | 1986-05-07 | Infors GmbH, 8000 München | INFUSION PUMP |
EP0231371B1 (en) * | 1985-08-06 | 1993-02-17 | BAXTER INTERNATIONAL INC. (a Delaware corporation) | Patient-controlled delivery of beneficial agents |
FR2600258A1 (en) * | 1986-06-18 | 1987-12-24 | Hazon Bernard | PUSH-SYRINGE DEVICE FOR AUTOMATIC PARENTERAL INJECTION WITH SERVICING AND PROGRAMMING |
CA1283827C (en) * | 1986-12-18 | 1991-05-07 | Giorgio Cirelli | Appliance for injection of liquid formulations |
FR2608929A1 (en) * | 1986-12-29 | 1988-07-01 | Godefroy Alain | Very-long-life time infusion apparatus |
US5128503A (en) * | 1987-07-31 | 1992-07-07 | Frantz Medical Development Ltd. | Rotational control dial with flush/protruding flip handle |
US5803712A (en) | 1988-05-17 | 1998-09-08 | Patient Solutions, Inc. | Method of measuring an occlusion in an infusion device with disposable elements |
US5074756A (en) | 1988-05-17 | 1991-12-24 | Patient Solutions, Inc. | Infusion device with disposable elements |
US5246347A (en) | 1988-05-17 | 1993-09-21 | Patients Solutions, Inc. | Infusion device with disposable elements |
US5011477A (en) * | 1989-04-21 | 1991-04-30 | Baxter International Inc. | Continuous/bolus infusor |
US5232448A (en) * | 1989-12-05 | 1993-08-03 | Prime Medical Products | Patient-controlled analgesia device |
CH686816A5 (en) * | 1992-02-04 | 1996-07-15 | Asulab Ag | Means for delivering a drug. |
DE4312454A1 (en) * | 1992-09-04 | 1994-03-10 | Wolfgang Dr Med Baetz | Crescent shaped pump syringe for intravenous durable infusion - has arm bands, and is externally supportable |
US5389078A (en) * | 1993-10-06 | 1995-02-14 | Sims Deltec, Inc. | Programmable infusion pump for administering medication to patients |
US5352201A (en) * | 1994-02-03 | 1994-10-04 | Block Medical, Inc. | Compact uniform pressure infusion apparatus |
US6171298B1 (en) | 1996-05-03 | 2001-01-09 | Situs Corporation | Intravesical infuser |
US6558900B2 (en) * | 1996-07-12 | 2003-05-06 | Emory University | Regulation of apoptosis and in vitro model for studies thereof |
WO1999021596A1 (en) * | 1997-10-23 | 1999-05-06 | Mernoee Morten | An infusion pump system and an infusion pump unit |
US5957895A (en) * | 1998-02-20 | 1999-09-28 | Becton Dickinson And Company | Low-profile automatic injection device with self-emptying reservoir |
US6183461B1 (en) | 1998-03-11 | 2001-02-06 | Situs Corporation | Method for delivering a medication |
US5906597A (en) * | 1998-06-09 | 1999-05-25 | I-Flow Corporation | Patient-controlled drug administration device |
US6554798B1 (en) | 1998-08-18 | 2003-04-29 | Medtronic Minimed, Inc. | External infusion device with remote programming, bolus estimator and/or vibration alarm capabilities |
US6092699A (en) * | 1998-08-25 | 2000-07-25 | Schmidt; Philip Arthur | Gravity flow microprocessor controlled portable plant dispensing system |
AUPP863599A0 (en) * | 1999-02-12 | 1999-03-04 | Cade, John F. | Method of, and apparatus for, controlling the delivery of a medication |
US6139535A (en) * | 1999-05-27 | 2000-10-31 | Situs Corporation | Method and apparatus for placement and activation of a medical device within a body cavity |
US6535523B1 (en) * | 1999-09-30 | 2003-03-18 | Qualcomm Incorporated | System and method for persistence vector based rate assignment |
US6485461B1 (en) | 2000-04-04 | 2002-11-26 | Insulet, Inc. | Disposable infusion device |
US6589229B1 (en) | 2000-07-31 | 2003-07-08 | Becton, Dickinson And Company | Wearable, self-contained drug infusion device |
ES2287156T3 (en) * | 2000-09-08 | 2007-12-16 | Insulet Corporation | DEVICES AND SYSTEMS FOR THE INFUSION OF A PATIENT. |
US6669669B2 (en) | 2001-10-12 | 2003-12-30 | Insulet Corporation | Laminated patient infusion device |
EP1702635B1 (en) | 2000-11-09 | 2008-01-16 | Insulet Corporation | Transcutaneous delivery means |
DE60115707T2 (en) | 2000-12-21 | 2006-08-10 | Insulet Corp., Beverly | REMOTE CONTROL MEDICAL DEVICE |
CA2434731C (en) | 2001-02-22 | 2010-01-26 | Insulet Corporation | Modular infusion device and method |
KR20020070705A (en) * | 2001-03-02 | 2002-09-11 | 파워뱅크 주식회사 | Insulin patch device |
US20040078028A1 (en) * | 2001-11-09 | 2004-04-22 | Flaherty J. Christopher | Plunger assembly for patient infusion device |
US6692457B2 (en) | 2002-03-01 | 2004-02-17 | Insulet Corporation | Flow condition sensor assembly for patient infusion device |
US6830558B2 (en) | 2002-03-01 | 2004-12-14 | Insulet Corporation | Flow condition sensor assembly for patient infusion device |
US6780171B2 (en) * | 2002-04-02 | 2004-08-24 | Becton, Dickinson And Company | Intradermal delivery device |
US20040153032A1 (en) * | 2002-04-23 | 2004-08-05 | Garribotto John T. | Dispenser for patient infusion device |
US6656159B2 (en) | 2002-04-23 | 2003-12-02 | Insulet Corporation | Dispenser for patient infusion device |
US6656158B2 (en) | 2002-04-23 | 2003-12-02 | Insulet Corporation | Dispenser for patient infusion device |
US20050238507A1 (en) * | 2002-04-23 | 2005-10-27 | Insulet Corporation | Fluid delivery device |
US6960192B1 (en) | 2002-04-23 | 2005-11-01 | Insulet Corporation | Transcutaneous fluid delivery system |
JP3854190B2 (en) * | 2002-04-26 | 2006-12-06 | 株式会社ジェイテクト | Motor control device |
US6723072B2 (en) | 2002-06-06 | 2004-04-20 | Insulet Corporation | Plunger assembly for patient infusion device |
US7018360B2 (en) * | 2002-07-16 | 2006-03-28 | Insulet Corporation | Flow restriction system and method for patient infusion device |
US7128727B2 (en) * | 2002-09-30 | 2006-10-31 | Flaherty J Christopher | Components and methods for patient infusion device |
US7144384B2 (en) * | 2002-09-30 | 2006-12-05 | Insulet Corporation | Dispenser components and methods for patient infusion device |
JP4599296B2 (en) * | 2002-10-11 | 2010-12-15 | ベクトン・ディキンソン・アンド・カンパニー | System and method for initiating and maintaining continuous long-term control of the concentration of a substance in a patient's body using a feedback or model-based controller coupled to a single needle or multi-needle intradermal (ID) delivery device |
US20040116866A1 (en) * | 2002-12-17 | 2004-06-17 | William Gorman | Skin attachment apparatus and method for patient infusion device |
US8771183B2 (en) | 2004-02-17 | 2014-07-08 | Abbott Diabetes Care Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US7587287B2 (en) | 2003-04-04 | 2009-09-08 | Abbott Diabetes Care Inc. | Method and system for transferring analyte test data |
US20050182366A1 (en) * | 2003-04-18 | 2005-08-18 | Insulet Corporation | Method For Visual Output Verification |
CA2523267C (en) | 2003-04-23 | 2013-09-03 | Biovalve Technologies, Inc. | Hydraulically actuated pump for long duration medicament administration |
US8066639B2 (en) | 2003-06-10 | 2011-11-29 | Abbott Diabetes Care Inc. | Glucose measuring device for use in personal area network |
US20050065760A1 (en) * | 2003-09-23 | 2005-03-24 | Robert Murtfeldt | Method for advising patients concerning doses of insulin |
US20050070847A1 (en) * | 2003-09-29 | 2005-03-31 | Van Erp Wilhelmus Petrus Martinus Maria | Rapid-exchange balloon catheter with hypotube shaft |
ES2739529T3 (en) * | 2003-11-06 | 2020-01-31 | Lifescan Inc | Drug administration pen with event notification means |
WO2006014425A1 (en) | 2004-07-02 | 2006-02-09 | Biovalve Technologies, Inc. | Methods and devices for delivering glp-1 and uses thereof |
GB2418144A (en) * | 2004-09-17 | 2006-03-22 | Psimedica Ltd | Medical device for delivery of beneficial substance |
US20060178633A1 (en) * | 2005-02-03 | 2006-08-10 | Insulet Corporation | Chassis for fluid delivery device |
US8112240B2 (en) | 2005-04-29 | 2012-02-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing leak detection in data monitoring and management systems |
US8137314B2 (en) * | 2006-08-23 | 2012-03-20 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with compressible or curved reservoir or conduit |
US20070093786A1 (en) * | 2005-08-16 | 2007-04-26 | Medtronic Minimed, Inc. | Watch controller for a medical device |
US20090227855A1 (en) | 2005-08-16 | 2009-09-10 | Medtronic Minimed, Inc. | Controller device for an infusion pump |
US20070060869A1 (en) * | 2005-08-16 | 2007-03-15 | Tolle Mike C V | Controller device for an infusion pump |
US20070060870A1 (en) * | 2005-08-16 | 2007-03-15 | Tolle Mike Charles V | Controller device for an infusion pump |
US7766829B2 (en) | 2005-11-04 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing basal profile modification in analyte monitoring and management systems |
US8353881B2 (en) * | 2005-12-28 | 2013-01-15 | Abbott Diabetes Care Inc. | Infusion sets for the delivery of a therapeutic substance to a patient |
US7981034B2 (en) | 2006-02-28 | 2011-07-19 | Abbott Diabetes Care Inc. | Smart messages and alerts for an infusion delivery and management system |
CN103239773B (en) | 2006-03-30 | 2015-08-26 | 瓦莱里塔斯公司 | Multi-cartridge fluid delivery device |
US8226891B2 (en) | 2006-03-31 | 2012-07-24 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods therefor |
US9119582B2 (en) | 2006-06-30 | 2015-09-01 | Abbott Diabetes Care, Inc. | Integrated analyte sensor and infusion device and methods therefor |
US8932216B2 (en) | 2006-08-07 | 2015-01-13 | Abbott Diabetes Care Inc. | Method and system for providing data management in integrated analyte monitoring and infusion system |
US8206296B2 (en) | 2006-08-07 | 2012-06-26 | Abbott Diabetes Care Inc. | Method and system for providing integrated analyte monitoring and infusion system therapy management |
US8732188B2 (en) | 2007-02-18 | 2014-05-20 | Abbott Diabetes Care Inc. | Method and system for providing contextual based medication dosage determination |
US8930203B2 (en) | 2007-02-18 | 2015-01-06 | Abbott Diabetes Care Inc. | Multi-function analyte test device and methods therefor |
US8123686B2 (en) | 2007-03-01 | 2012-02-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing rolling data in communication systems |
US8456301B2 (en) | 2007-05-08 | 2013-06-04 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8461985B2 (en) | 2007-05-08 | 2013-06-11 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8665091B2 (en) | 2007-05-08 | 2014-03-04 | Abbott Diabetes Care Inc. | Method and device for determining elapsed sensor life |
US7928850B2 (en) | 2007-05-08 | 2011-04-19 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8641618B2 (en) | 2007-06-27 | 2014-02-04 | Abbott Diabetes Care Inc. | Method and structure for securing a monitoring device element |
US8085151B2 (en) | 2007-06-28 | 2011-12-27 | Abbott Diabetes Care Inc. | Signal converting cradle for medical condition monitoring and management system |
US20090112155A1 (en) * | 2007-10-30 | 2009-04-30 | Lifescan, Inc. | Micro Diaphragm Pump |
US7959598B2 (en) | 2008-08-20 | 2011-06-14 | Asante Solutions, Inc. | Infusion pump systems and methods |
US8223028B2 (en) | 2008-10-10 | 2012-07-17 | Deka Products Limited Partnership | Occlusion detection system and method |
US8066672B2 (en) | 2008-10-10 | 2011-11-29 | Deka Products Limited Partnership | Infusion pump assembly with a backup power supply |
US9180245B2 (en) * | 2008-10-10 | 2015-11-10 | Deka Products Limited Partnership | System and method for administering an infusible fluid |
US8262616B2 (en) | 2008-10-10 | 2012-09-11 | Deka Products Limited Partnership | Infusion pump assembly |
US8708376B2 (en) | 2008-10-10 | 2014-04-29 | Deka Products Limited Partnership | Medium connector |
EP2196231B1 (en) * | 2008-12-12 | 2013-02-27 | F. Hoffmann-La Roche AG | System for ambulatory drug infusion comprising a filling apparatus for flexible containers |
US8103456B2 (en) | 2009-01-29 | 2012-01-24 | Abbott Diabetes Care Inc. | Method and device for early signal attenuation detection using blood glucose measurements |
US9226701B2 (en) | 2009-04-28 | 2016-01-05 | Abbott Diabetes Care Inc. | Error detection in critical repeating data in a wireless sensor system |
US9184490B2 (en) | 2009-05-29 | 2015-11-10 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
TWI528121B (en) * | 2009-08-21 | 2016-04-01 | 魯西恩 沃拉摩茲 | Visual indicator |
US9314195B2 (en) | 2009-08-31 | 2016-04-19 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
WO2011026148A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods for managing power and noise |
WO2011041469A1 (en) | 2009-09-29 | 2011-04-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing notification function in analyte monitoring systems |
WO2011153511A2 (en) * | 2010-06-03 | 2011-12-08 | Elix, Llc | Dispenser |
US10441767B2 (en) * | 2010-10-27 | 2019-10-15 | Asti Corporation | Jig for microneedle array placement and microneedle array device |
US9980669B2 (en) | 2011-11-07 | 2018-05-29 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
WO2013149186A1 (en) | 2012-03-30 | 2013-10-03 | Insulet Corporation | Fluid delivery device with transcutaneous access tool, insertion mechansim and blood glucose monitoring for use therewith |
US9968306B2 (en) | 2012-09-17 | 2018-05-15 | Abbott Diabetes Care Inc. | Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems |
EP2908881A2 (en) | 2012-10-16 | 2015-08-26 | SwissInnov Product Sàrl | Fluid delivery system and methods |
CN105769545A (en) * | 2014-12-26 | 2016-07-20 | 李茜莲 | Acupoint massage device for old people |
EP3380061A4 (en) | 2015-11-24 | 2019-07-24 | Insulet Corporation | Wearable automated medication delivery system |
WO2017091584A1 (en) | 2015-11-25 | 2017-06-01 | Insulet Corporation | Wearable medication delivery device |
WO2017123525A1 (en) | 2016-01-13 | 2017-07-20 | Bigfoot Biomedical, Inc. | User interface for diabetes management system |
EP3453414A1 (en) | 2016-01-14 | 2019-03-13 | Bigfoot Biomedical, Inc. | Adjusting insulin delivery rates |
WO2017205816A1 (en) | 2016-05-26 | 2017-11-30 | Insulet Corporation | Single dose drug delivery device |
US10363372B2 (en) | 2016-08-12 | 2019-07-30 | Insulet Corporation | Plunger for drug delivery device |
WO2018035051A1 (en) | 2016-08-14 | 2018-02-22 | Insulet Corporation | Drug delivery device with detection of position of the plunger |
US11547791B2 (en) * | 2016-09-27 | 2023-01-10 | Sanofi-Aventis Deutschland Gmbh | Medicament delivery device |
WO2018067645A1 (en) | 2016-10-07 | 2018-04-12 | Insulet Corporation | Multi-stage delivery system |
US10780217B2 (en) | 2016-11-10 | 2020-09-22 | Insulet Corporation | Ratchet drive for on body delivery system |
US10603440B2 (en) | 2017-01-19 | 2020-03-31 | Insulet Corporation | Cartridge hold-up volume reduction |
WO2018156548A1 (en) | 2017-02-22 | 2018-08-30 | Insulet Corporation | Needle insertion mechanisms for drug containers |
US10695485B2 (en) | 2017-03-07 | 2020-06-30 | Insulet Corporation | Very high volume user filled drug delivery device |
CN111032122A (en) | 2017-07-18 | 2020-04-17 | 贝克顿·迪金森公司 | Drug delivery system, delivery device and notification device for communicating the status of a medical device |
EP3662161A1 (en) | 2017-08-03 | 2020-06-10 | Insulet Corporation | Micro piston pump |
US10973978B2 (en) | 2017-08-03 | 2021-04-13 | Insulet Corporation | Fluid flow regulation arrangements for drug delivery devices |
US11786668B2 (en) | 2017-09-25 | 2023-10-17 | Insulet Corporation | Drug delivery devices, systems, and methods with force transfer elements |
WO2019067367A1 (en) | 2017-09-26 | 2019-04-04 | Insulet Corporation | Needle mechanism module for drug delivery device |
US11147931B2 (en) | 2017-11-17 | 2021-10-19 | Insulet Corporation | Drug delivery device with air and backflow elimination |
USD928199S1 (en) | 2018-04-02 | 2021-08-17 | Bigfoot Biomedical, Inc. | Medication delivery device with icons |
US10874803B2 (en) | 2018-05-31 | 2020-12-29 | Insulet Corporation | Drug cartridge with drive system |
US11229736B2 (en) | 2018-06-06 | 2022-01-25 | Insulet Corporation | Linear shuttle pump for drug delivery |
EP3887680B1 (en) | 2018-11-28 | 2022-10-26 | Insulet Corporation | Drug delivery shuttle pump system and valve assembly |
US11369735B2 (en) | 2019-11-05 | 2022-06-28 | Insulet Corporation | Component positioning of a linear shuttle pump |
Family Cites Families (30)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CA28096A (en) * | 1887-11-29 | Eugene E. Allen | Instrument for the transfusion of blood | |
US2605765A (en) * | 1947-06-05 | 1952-08-05 | Kollsman Paul | Automatic syringe |
US3151616A (en) * | 1962-07-25 | 1964-10-06 | Paul M Selfon | Automatic transfusion apparatus |
US3198385A (en) * | 1962-09-06 | 1965-08-03 | Palmer M Maxwell | High pressure medical injection direct from a fluid containing ampule |
US3384080A (en) * | 1964-10-16 | 1968-05-21 | Us Catheter & Instr Corp | Portable spring powered infusion device having escapement means controlling speed ofinfusion |
US3469578A (en) * | 1965-10-12 | 1969-09-30 | Howard R Bierman | Infusion device for ambulatory patients with flow control means |
US3685697A (en) * | 1969-01-17 | 1972-08-22 | Lear Siegler Inc | Portable infusion pump |
US4201207A (en) * | 1973-03-26 | 1980-05-06 | Alza Corporation | Bladder for liquid dispenser |
JPS5010073A (en) * | 1973-05-23 | 1975-02-01 | ||
US3858581A (en) * | 1973-07-02 | 1975-01-07 | Dean Kamen | Medication injection device |
US3886938A (en) * | 1973-10-23 | 1975-06-03 | Scala Anthony | Power operated fluid infusion device |
US4013074A (en) * | 1974-06-21 | 1977-03-22 | Siposs George G | Implantable medication-dispensing device |
DE2513467C3 (en) * | 1975-03-26 | 1979-10-31 | Siemens Ag, 1000 Berlin Und 8000 Muenchen | Device for infusing liquids into the human or animal body |
US4155362A (en) * | 1976-01-26 | 1979-05-22 | Baxter Travenol Laboratories, Inc. | Method and apparatus for metered infusion of fluids |
FR2348709A1 (en) * | 1976-04-23 | 1977-11-18 | Pistor Michel | MESOTHERAPIC TREATMENT PROCESS AND INJECTION DEVICE, FORMING AUTOMATIC MICRO-INJECTOR, INCLUDING APPLICATION |
US4059110A (en) * | 1976-10-07 | 1977-11-22 | Timex Corporation | Clockwork driven hypodermic syringe |
US4273122A (en) * | 1976-11-12 | 1981-06-16 | Whitney Douglass G | Self contained powered injection system |
DE2652026C2 (en) * | 1976-11-15 | 1983-01-05 | Siemens AG, 1000 Berlin und 8000 München | Device for infusing liquids |
FR2387046A1 (en) * | 1977-04-12 | 1978-11-10 | Moulet Camille | Infusion pump for transfusion and perfusion - has peristaltic pump with three rollers and graduated control to vary motor speed and flow time |
DE2721752C2 (en) * | 1977-05-13 | 1983-12-29 | Siemens AG, 1000 Berlin und 8000 München | Device implantable in a human or animal body for the infusion of a medical liquid |
JPS5436089A (en) * | 1977-08-25 | 1979-03-16 | Nikkiso Co Ltd | Liquid administering pump drive control system |
US4221219A (en) * | 1978-07-31 | 1980-09-09 | Metal Bellows Corporation | Implantable infusion apparatus and method |
SE426783B (en) * | 1978-10-19 | 1983-02-14 | Figueiredo Nuno R M | DEVICE FOR AUTOMATIC CONTROL OF THE INFUSION FLUID IN AN INFUSER |
GB2035094B (en) * | 1978-11-02 | 1982-11-10 | Vickers Ltd | Liquid dispensing apparatus |
NL7900459A (en) * | 1979-01-19 | 1980-07-22 | Hendrik Coenraad Hemker Prof D | PHARMACEUTICAL PREPARATION AND METHOD OF PREPARATION THEREOF. |
DE2906830C2 (en) * | 1979-02-22 | 1981-07-16 | B. Braun Melsungen Ag, 3508 Melsungen | Device for continuous infusions |
DE2920975C2 (en) * | 1979-05-23 | 1985-08-14 | Siemens AG, 1000 Berlin und 8000 München | Extracorporeally portable infusion device |
WO1981001658A1 (en) * | 1979-12-13 | 1981-06-25 | M Loeb | Wearable insulin infusion system having a tubular reservoir and a positive displacement metering means |
US4313439A (en) * | 1980-03-24 | 1982-02-02 | Biotek, Inc. | Automated, spring-powered medicament infusion system |
US4525164A (en) * | 1981-04-24 | 1985-06-25 | Biotek, Inc. | Wearable medication infusion system with arcuated reservoir |
-
1980
- 1980-06-03 CA CA000353268A patent/CA1169323A/en not_active Expired
-
1981
- 1981-05-22 US US06/267,364 patent/US4601707A/en not_active Expired - Fee Related
- 1981-05-29 GB GB8116435A patent/GB2077110B/en not_active Expired
- 1981-06-02 DE DE3121888A patent/DE3121888C2/en not_active Expired
- 1981-06-02 SE SE8103469A patent/SE444509B/en not_active IP Right Cessation
- 1981-06-02 LU LU83407A patent/LU83407A1/en unknown
- 1981-06-02 NL NL8102652A patent/NL8102652A/en not_active Application Discontinuation
- 1981-06-03 BE BE0/204980A patent/BE889071A/en not_active IP Right Cessation
- 1981-06-03 FR FR8111002A patent/FR2486403B1/en not_active Expired
- 1981-06-03 JP JP8554081A patent/JPS5722761A/en active Pending
-
1983
- 1983-02-14 CA CA000421583A patent/CA1169324A/en not_active Expired
-
1996
- 1996-06-28 CN CN96108173A patent/CN1169324A/en active Pending
Also Published As
Publication number | Publication date |
---|---|
DE3121888C2 (en) | 1986-01-30 |
CA1169324A (en) | 1984-06-19 |
FR2486403A1 (en) | 1982-01-15 |
LU83407A1 (en) | 1981-09-11 |
SE8103469L (en) | 1981-12-04 |
US4601707A (en) | 1986-07-22 |
GB2077110A (en) | 1981-12-16 |
DE3121888A1 (en) | 1982-03-04 |
SE444509B (en) | 1986-04-21 |
BE889071A (en) | 1981-10-01 |
CN1169324A (en) | 1998-01-07 |
FR2486403B1 (en) | 1985-10-18 |
NL8102652A (en) | 1982-01-04 |
JPS5722761A (en) | 1982-02-05 |
GB2077110B (en) | 1984-12-12 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA1169323A (en) | Insulin infusion device | |
CA1156114A (en) | Wearable insulin infusion system having a tubular reservoir and a positive displacement metering means | |
EP1691883B1 (en) | Dispenser for patient infusion device | |
US6656159B2 (en) | Dispenser for patient infusion device | |
US4342312A (en) | Method of injecting fluid | |
US4435173A (en) | Variable rate syringe pump for insulin delivery | |
US4568335A (en) | Device for the controlled infusion of medications | |
JP6685236B2 (en) | Catheter insertion device | |
JP5580094B2 (en) | New drive system for use with insulin delivery devices | |
ES2959467T3 (en) | Infusion system with simultaneous TPN/insulin infusion | |
DE8217879U1 (en) | DEVICE, IN PARTICULAR FOR SUBCUTANEOUS INFUSION OF MEDICINES | |
JP2005523397A (en) | Plunger of fluid dosing device | |
US11364339B2 (en) | Infusion unit | |
JPS605797B2 (en) | Microinjection pump device | |
AU6700481A (en) | Wearable insulin infusion system having a tubular reservoir and a positive displacement and metering means |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
MKEX | Expiry |