CA1187366A - Infusion device intended for implantation in a living body - Google Patents
Infusion device intended for implantation in a living bodyInfo
- Publication number
- CA1187366A CA1187366A CA000412170A CA412170A CA1187366A CA 1187366 A CA1187366 A CA 1187366A CA 000412170 A CA000412170 A CA 000412170A CA 412170 A CA412170 A CA 412170A CA 1187366 A CA1187366 A CA 1187366A
- Authority
- CA
- Canada
- Prior art keywords
- reservoir
- fluid
- infusion
- diaphragm
- pressure
- 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
-
- 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 exemplary embodiments relate to a device housing implantable in the body and having a reservoir for the infusion of fluid and having a conveying and dosing unit for conveying the fluid from the reservoir to the discharge opening of a discharge catheter. In known devices of this type, the reservoir is held at a reference pressure which is lower in comparison to the pressure at the fluid discharge location in order, in case of a defect, to prevent fluid from flowing out. According to the present disclosure, pressure equalization between the inside space of the housing and the environ-ment is effected for example by a hydrophobic or hydrophilic diaphragm with pores of a specific size or a diffusion diaphragm in combination with a pres-sure control valve in the wall of the device housing.
The exemplary embodiments relate to a device housing implantable in the body and having a reservoir for the infusion of fluid and having a conveying and dosing unit for conveying the fluid from the reservoir to the discharge opening of a discharge catheter. In known devices of this type, the reservoir is held at a reference pressure which is lower in comparison to the pressure at the fluid discharge location in order, in case of a defect, to prevent fluid from flowing out. According to the present disclosure, pressure equalization between the inside space of the housing and the environ-ment is effected for example by a hydrophobic or hydrophilic diaphragm with pores of a specific size or a diffusion diaphragm in combination with a pres-sure control valve in the wall of the device housing.
Description
3~
BACKGROUND OF THE INVENTION
The invention relates to an infusion device intended for implanta-tion in a living body, said infusion device being comprised of a device housing implantable in the patient's body having a reservoir for infusion fluid and llaving a conveying and dosing unit for conveying the Eluid from the reservoir to thc discharge opening of a catheter.
An in:Eusion device of the type initially cited is known, for example, from the United States Patent No. 4,191,181. For safety reasons the infusion fluid in the reservoir of the device is kept under a pressure which is lower than the pressure at the discharge opening of the catheter. Such a measure pre-vents fluid Erom discharging out of the reservoir into the patient's body due to a leak in the capsule or pump. In order to execute this measure, fo:r example, a flexible fluid reservoir is charged by a vapor pressure of such a substance as has a corresponding pressure at body -temperature. It is also possible to fill a buffered gas into the-tightly encapsulated device housing under such a pressure that, taking the gas equation into consideration, an under-pressure in comparison to the pressure of the environment is still maintained even given a full fluid reservoir.
A hermetic encapsulation of the device housing given maintenance of under-pressure over longer times, however, also produces a series of problems.
For example, temperature fluctuations and external changes of air pressure which can change the pressure differential between the body tissues and the in-side of the housing must be taken into consideration. As a result, one must proceed from a relatively great under-pressure, for example up to 0.5 bar.
The consequence of this, however, specifically given employment of roller pumps as the conveying and dosing unit, is that the danger of a reflux of fluid in the catheter exists during disengagement of the successive pump rollers from the 36~3 fluid conveyor tube.
SUri~lARY OF TilE INVENTION
.
It is -therefore an object of the invention to create a device of the type initially cited with safety features such as make the maintenance of under-pressure in the device housing unnecessary.
This object is inventively achieved in that means for balancing the pressure between the inside space o:E the housing and the environment are allocated to the device housing.
The environment can both be the tissue surrounding the implanted infusion device and the environment outside of the body. The point of depart-ure is that the pressure in the body tissue or, respectively, in the body fluid largely corresponds to the external barometric pressure.
The pressure equalization in the invention ensues over a gas-permeable or fluid-permeable diaphragm. Such a diaphragm can consist of hydrophobic material with pores of a specific size given which only gas is passed through; the diaphrag-n, however, can also consist of a fine-pore, hydro-philic materiai so that the pressure equalization is accomplished by an ex-change of body fluid.
In a preferred realization of the invention, a high permeability dif-fusion diaphragm can also be employed, particularly in conjunction with a pres-sure control valve. Thereby, given a slow emptying of the reservoir, a match-ing of the pressure inside the housing to the external pressure can be achieved solely by means oE gas diffusion, whereas an immediate pressure compensa-tion of the inside of the housing and the environment in the body tissue is effected by the valve during percutaneows re-filling of infusion fluid. By so doing, a build-up of excess pressure in the device housing is avoided. In a simplest embodiment, such a valve can consist of an elastic stopper which 3~
closes an opening and provides a ventilation channel in the housing wall.
Instead of the valve, it is also possible to briefly produce a connection of the inside of the housing with the envir-onment outside of the patien-t's body over a special paracentesis septum. This, however, is only required given re--filling of infus-ion Eluid and does not negatively influence the inventive pressure equilibrium given a long-time application of the implanted infusion device.
In an advantageous development of the invention, the dia-phragm for pressure equalization can be a part of the device housing, for example the diaphragm can also directly form the housing wall;
however, it can also be connected via a tube to the inside of the housing or, respectively, can itself be designed tube-like, so that it can be placed at a suitable location in the pa-tient's body.
A device for supplying medications to the human or animal body has already been proposed in the United States Patent No.
4,217,894 in which a diaphragm is introduced in the housing wall.
Thereby, however, that diaphragm is to have specific, hydrophilic properties in order to be able to suction bodily fluid quantitatively in by means of a conveying and dosing unit in order to be able to dissolve a solid medication therein. As a result of the suctioning of bodily fluid for the purpose of dissolving solid medications, however, a completely difEerent situation arises wherein, in part-icular, -the storage of medications as infusion fluid as well as problems connected with emptying and/or re-fi].ling fluid are to be avoided. In this regard, thus, -there are no points of contact with the present invention.
~ _ :., 3 ~
Thus, in accordance with a broacl aspect of the inven-tion, there is provided an infusion device for implantation in a pa-tient's body, comprising (a) a device housing implantable in the patient's body, said device housing having an outer surface, (b) a reservoir contained in sai.d device housing for storing an infusion liquid therein, said reservoir comprising reservoir wall means formed of a Elexible and fluid impermeable material, (c) pressure equalization means arranged between said reservoir and said outer surface for pressure equalization between the outer space of said reservoir and the outer environment of said device housing, (d) a conveying and dosing unit contained in said device housing for conveying said infusion liquid from said reservoir to a catheter discharge opening, and (e) re-filling means for re-filling said reservoir with said infusion liquid from outside of said housing.
In accordance with another broad aspect of the invention there is provided an infusion device intended for implantation in a living body, comprising a device housing implantable in the patient's body and having a reservoir for infusion fluid and having a conveying and dosing unit for conveying the i.nfusion fluid from the reservoir to a catheter discharge opening, and pressure equaliæation means operatively associated with said reservoir for tending to maintain pressure equalization between the pressure of infusion fluid and the environment of the device housing, said pressure equalization means comprising body fluid isolating means for preventing admixture of body fluid with the infusion fluid of said reservoir.
Further advantages and details of the invention derive - 3a -3~
from the following figure description of exempl~ry embodiments with reference to the accompanying drawing sheets; ancl other objects, features and advan-tages will be - 3b -361~5 apparent from this detailed disclosure and from the appended claims.
BRIEF DESCRIPTION OF THE DRAWING
Figures 1 through 5 show in a highly schematic illustration various-ly constructed infusion devices in cross section; and ~ igure 6 schematically illustrates an external view of an infusion device representing a further embodiment of the invention.
DETAILED DESCR PTION
In Figure 1, reference numeral 1 indicates a device housing of an implantable infusion device. As a flat capsule, this is a three-dimensional shape roughly equivalent to the housing of a heart pacemaker and is formed of implantable material compatible with body tissue~ for example titanium. A
conveying and dosing unit 2, a unit 3 with electronic circuits for the drive and control of the conveying and dosing unit 2, and an energy supply unit ~
(battery) are indicated in the device housing 1; 5 indicates a catheter which can be placed at a suitable location inside the patient's body. 6 indicates a reservoir for infusion fluid.
Insulin, for example, can be percutaneously introduced as infusion fluid into the reservoir 6 over a re-filling septum 8 introduced into the device housing and having a connecting line 10. To this end~ the re-filling septum 8 consists of a self-sealing elastomer which can be punctured with a standard injection cannula.
The reservoir 6 :Eor the :Eluid is protected against damage during re-filling of infusion fluid by means of a so-called needle stopper 9. A
conveying wick can be situated within the reservoir 6, the fluid being suctioned off bubble-free over a conveyor tube 7 to the discharge catheter 5 from said wick by means of the conveying and dosing unit 2.
In this regard~ the structure of an infusion device is known Erom 3~;~
the prior art. Where the known infusion devices are hermetically encapsulated for the purpose of maintaining under-pressure in the device housing, a dia-phragm 11 is now inserted to form part of the wall of the device housing 1.
In the embodiment according to Figure 1, the diaphragm 11 consists oE hydrophobic material with porcs which are so fine that, even given the maximum pressure dif:Eeren-tial between the housing interior and the environment, no body fluid is allowed to pass through the pores. The same also applies to body cells and/or bacteria. To this end, standard hydrophobic filters such as frits or diaphragm filters can be employed which, for example, consist of polyolefins, PTFE or of similar materials.
With such a design of the infusion device, it is guaranteed that, given a continuous fluid disharge from the reservoir, the gas dissolved in the surrounding body tissue or in the body fluids can enter into the device housing.
As a result, a pressure equalization is largely seen to. Since the gas pressure in the body tissue or, respectively, in the body fluid approximately corresponds to the external air pressure, a matching to the barometric pressure of the environment is likewise guaranteed.
Given transcutaneous re-filling of the reservoir, it is expedient to first always suction the remaining content of fluid in the reservoir out.
Given such a comparatively fast operation, practically no gas from the environ-ment of the device housing can di:Efuse-in so that an under-pressure can briefly arise. Given the immediately following re-filling of the reservoir, the gas present in the device housing is d:isplaced into the surrounding body tissue and is absorbed there. It can be expedient to suction off a device-external gas bubble which may potentially arise.
In Figure 2, the reference numerals 21 through 28 as well as 31 correspond in their sequence to the reference numerals of Eigure 1 increased ~ 3~3~
by twenty. Specifically indicated with 29 is a suction wick in the reservoir.
In the embodiment according to Figure 2, the reservoir 26 is rigidly designed for containing the infusion fluid. This has the advantage that a part of the reservoir 26 simultaneously forms the housing wall and that the re-Eilling septum 28 can lead directly into the reservoir 26. Thereby, the needle stopper is advantageously directly integrated in the housing wall. Certain structural simplifications also derive. A syringe for percutaneous sucking or, respective-ly, re-filling of the infusion fluid through the indicated body tissue is referenced with 30.
In this exemplary embodiment, the diaphragm 31 directly closes off the reservoir 26 with infusion fluid from the body tissue. ~o leakage of fluids can be permitted, so that the hydrophobia of the diaphragm 31 is an unCOJI-ditional prerequisite~
Given this embodiment of the invention, the pressure equalization ensues by means of direct gas exchange between the environment and the reservoir 26. For this reason, the bubble-free sucking of fluid by the conveying and dosing unit 22 is to be guaranteed by means of the wick 29. Further, it must also be seen to that the conveyor wick 29 is in contact with infusion fluid given all filling conditions of the reservoir 26 and given every possible patient position.
In the infusion device of Figure 3, the sequence of reference numerals 41 to 51 again represent units corresponding to those in Figure l; in accord with Figure 1, a flexible fluid reservoir 46 is provided. According to this embodiment of the invention, the diaphragm 51 which is introduced in the housing wall of the device housing 41 consists of fine-pore, hydrophilic material so that low-molecular body fluids can proceed through the pores. The pore size of the diaphragm 51 is selected in such manner that larger fluid ;6 molecules and, in particular, body cells and/or bacteria as well are arrested.
In this embodiment, the pressure equalization is achieved solely by means of the exchange of body fluid. BeFore the transcutaneous re~filling of the inEusion fluid, medication residues are again to be suctioned out via thc re-filling septum 48 with a syringe. To that end, a buffer volume with a compressible agent, i.e., a gas, must exist in the device housing 41. Ex-pediently, a separate, flexible bellows 53 with a gas contained therein is pro-vided, said bellows matching to the respectively existing volume. Likewise, the elastic container of the bellows 53 can also contain a liquid or some other substance with a vapor pressure which is lower than the external barometric pressure and, thus, guarantees a volume-dependent pressure.
Given the embodiment of Figure 3, the thickness, area and the mater-ial of the hydrophilic diaphragm 51 are selected in such manner that the dia-phragm has a relatively low flow resistance. By so doing, no significant under-pressure arises in the reservoir 46 even given the maximum pump rate of the conveying and dosing unit 42. Fabric or fiber strengthened hydrogels, for example, are suitable as materials for the diaphragm 51. In order to quickly remove the excess body fluid from the inside space of the housing 41 and to re-introduce it into the body tissue during transcutaneous re-filling of the reservoir 46 with infusion fluid, a valve 52 is additionally provided in the housing, said valve opening given over-pressure in the inside o:F the housing and letting the fluid out.
The exemplary embodiment according to ~igure 4 is fundamentally constructed in accord with Figure 3, whereby corresponding units derive in the numerical sequence of 61 through 71. A so-called diffusion diaphragm 71 having a high permeability for gases is specifically provided here as the diaphragm, consisting for example~ of silicone. rhe pressure equal:ization between the 3~i~
inside of the housing and the environment given this embodiment of the inven-tion, thus, ensues solely by means of diffusion, this completely sufficing given the usual, slow emptying of the reservoir as a result of the micro-dosing by the conveying and dosing unit 62. Since a diffusion-determined rate of gas exchange does not suffice during re-filling, a valve 72 is again addition-ally provided. As a result, a significantly faster escape of the gas from the device housing 1 in comparison to the diffusion rate is possible given per-cutaneous re-filling of the reservoir 66. It is also possible as an alternative to a valve, that an elastic diffusion diaphragm of such nature is employed which bulges toward the outside until the excess pressure has been dismantled by diffusion.
The valve 72 can consist of a rubber plug 73 in the wall of the device housing 61 which plug 73 covers an opening 74 in the housing wall and tightly closes it under normal pressure but opens given excess pressure in the inside of the housing.
In Figure 5, the reference numeral 81 through 91 denote the units described on the basis of the preceding Figures in a corresponding numerial se-quence. Given this embodiment of the invention, a gas-permeable or fluid-permeable diaphragm can be facultatively employed as the diaphragm 91. In addition to the fluid re-filling septum 88, a further septum 92 is provided as a separate paracentesis system which again consists of a self-sealing elastomer with following needle stopper 93. An internal tube 9~ is conducted from the septum 92 to the lowest location of the housing.
Given the infusion device according to Figure 5, the pressure equali-zation during the slow conveying operation and emptying of the reservoir 86 by the conveying and dosing unit 82 ensues over the gas-permeable or fluid-permeable diaphragm in accord with the exemplary embodiments described above.
736~
Now, however, the pressure or, respectively, volume equalization in the per-cutaneous re-filling of -the reservoir does not ensue by means of gas or fluid exchange with the surrounding body tissue but, rather, with the environment outside o:E the patient's body. Such an equalization can be particularly quickly accomplished; at the same time, the substances temporarily collected in the device housing are removed.
For the re-filling operation, thus, a cannula 95 is tapped into the second septum 92, said cannula 95 leading through the tissue toward the outside.
Particularly given employment of the hydrophilic diaphragm, this has the advan-tage that the body fluid is not expressed from the inside of the housing into the body but, rather, can flow off toward the outside. For the embodiment having the gas-permeable diaphragm, however, the second septum 92 is expediently disposed in such manner that condensed water or other body fluids which may have penetrated can be directly sucked off from the lowest housing parts with paracentesis cannula.
The further access to the inside of the capsule present in Figure 6 also has additional advantages in the manufacture and encapsulation of the overall infusion device.
Given the infusion devices according to Figures 1, 3, as well as 4 and 6, a flexible reservoir for the infusion fluid is respectively provided in the device housing. In the normal case, the fluid is filled into the reservoir bubble-free through the septum by means of a cannula or, respectively, syringe.
However, it can also be useful given these embodiments to provide an additional suction wick in accord with Figure 2 in order to safely guarantee a bubble-free pumping of the fluid even given gas bubbles which may potentially exist.
In the preceding Figures, the respective, differently designed diaphragms 11, 31, 51, 71 and 91 were always illustrated as a part of the g 3~
housing wall. ~lowever, it can be expedient to connect such a diaphragm to the device housing via an additional tube; this can be of significance particularly given a pressure equalization by means of exchanging body fluid.
In Figure 6, a correspondingly designed device housing with catheter 105 as well as a tube llO with terminating diaphragm lll is referenced with lOl.
'I'hcreby, the tube llO discharges at its proximal end in the corresponding chamber of the device housing lOl and is selected of such length that it can be placed in patient's body up to a reservoir of body fluid. The tube llO can itself consist of diaphragm material.
The inventive dif*usion devices described on the basis of the various exemplary embodiments can particularly be employed as an artificial pancreas for administering insulin in diabetes therapy. Thereby, considerable problems in the implantation of such devices into a living body are overcome with the invention. The pressure equalization between the inside space of the housing and the environment of the housing is respectively accomplished in that, during operation of the implanted diffusion device, the infused fluid is replaced by body gases or by body fluid as well. Thereby, the flexible reservoir in Figures l, 3, 4 and 5 respectively encloses the entire infusion fluid (not visibly illustrated), while the space not filled by the in-fusion fluid in the rigid reservoir in Figure 2 is filled up by body gases.
A reliable aspiration of infusion fluid is always guaranteed as a result of the above features independently of the filling condition of the reservoir even given changing spatial attitudes of the infusion device due to changes of position of the patient's body. The additional disposition of a pressure control valve in the housing wall particularly serves for the equali-zation of excess pressures occurring relatively briefly, for example in an airplane or when filling the reservoir.
3~;6 It will be apparent that many modifications and variations may be made without departing from the scope of the teachings and concepts of the present invention.
BACKGROUND OF THE INVENTION
The invention relates to an infusion device intended for implanta-tion in a living body, said infusion device being comprised of a device housing implantable in the patient's body having a reservoir for infusion fluid and llaving a conveying and dosing unit for conveying the Eluid from the reservoir to thc discharge opening of a catheter.
An in:Eusion device of the type initially cited is known, for example, from the United States Patent No. 4,191,181. For safety reasons the infusion fluid in the reservoir of the device is kept under a pressure which is lower than the pressure at the discharge opening of the catheter. Such a measure pre-vents fluid Erom discharging out of the reservoir into the patient's body due to a leak in the capsule or pump. In order to execute this measure, fo:r example, a flexible fluid reservoir is charged by a vapor pressure of such a substance as has a corresponding pressure at body -temperature. It is also possible to fill a buffered gas into the-tightly encapsulated device housing under such a pressure that, taking the gas equation into consideration, an under-pressure in comparison to the pressure of the environment is still maintained even given a full fluid reservoir.
A hermetic encapsulation of the device housing given maintenance of under-pressure over longer times, however, also produces a series of problems.
For example, temperature fluctuations and external changes of air pressure which can change the pressure differential between the body tissues and the in-side of the housing must be taken into consideration. As a result, one must proceed from a relatively great under-pressure, for example up to 0.5 bar.
The consequence of this, however, specifically given employment of roller pumps as the conveying and dosing unit, is that the danger of a reflux of fluid in the catheter exists during disengagement of the successive pump rollers from the 36~3 fluid conveyor tube.
SUri~lARY OF TilE INVENTION
.
It is -therefore an object of the invention to create a device of the type initially cited with safety features such as make the maintenance of under-pressure in the device housing unnecessary.
This object is inventively achieved in that means for balancing the pressure between the inside space o:E the housing and the environment are allocated to the device housing.
The environment can both be the tissue surrounding the implanted infusion device and the environment outside of the body. The point of depart-ure is that the pressure in the body tissue or, respectively, in the body fluid largely corresponds to the external barometric pressure.
The pressure equalization in the invention ensues over a gas-permeable or fluid-permeable diaphragm. Such a diaphragm can consist of hydrophobic material with pores of a specific size given which only gas is passed through; the diaphrag-n, however, can also consist of a fine-pore, hydro-philic materiai so that the pressure equalization is accomplished by an ex-change of body fluid.
In a preferred realization of the invention, a high permeability dif-fusion diaphragm can also be employed, particularly in conjunction with a pres-sure control valve. Thereby, given a slow emptying of the reservoir, a match-ing of the pressure inside the housing to the external pressure can be achieved solely by means oE gas diffusion, whereas an immediate pressure compensa-tion of the inside of the housing and the environment in the body tissue is effected by the valve during percutaneows re-filling of infusion fluid. By so doing, a build-up of excess pressure in the device housing is avoided. In a simplest embodiment, such a valve can consist of an elastic stopper which 3~
closes an opening and provides a ventilation channel in the housing wall.
Instead of the valve, it is also possible to briefly produce a connection of the inside of the housing with the envir-onment outside of the patien-t's body over a special paracentesis septum. This, however, is only required given re--filling of infus-ion Eluid and does not negatively influence the inventive pressure equilibrium given a long-time application of the implanted infusion device.
In an advantageous development of the invention, the dia-phragm for pressure equalization can be a part of the device housing, for example the diaphragm can also directly form the housing wall;
however, it can also be connected via a tube to the inside of the housing or, respectively, can itself be designed tube-like, so that it can be placed at a suitable location in the pa-tient's body.
A device for supplying medications to the human or animal body has already been proposed in the United States Patent No.
4,217,894 in which a diaphragm is introduced in the housing wall.
Thereby, however, that diaphragm is to have specific, hydrophilic properties in order to be able to suction bodily fluid quantitatively in by means of a conveying and dosing unit in order to be able to dissolve a solid medication therein. As a result of the suctioning of bodily fluid for the purpose of dissolving solid medications, however, a completely difEerent situation arises wherein, in part-icular, -the storage of medications as infusion fluid as well as problems connected with emptying and/or re-fi].ling fluid are to be avoided. In this regard, thus, -there are no points of contact with the present invention.
~ _ :., 3 ~
Thus, in accordance with a broacl aspect of the inven-tion, there is provided an infusion device for implantation in a pa-tient's body, comprising (a) a device housing implantable in the patient's body, said device housing having an outer surface, (b) a reservoir contained in sai.d device housing for storing an infusion liquid therein, said reservoir comprising reservoir wall means formed of a Elexible and fluid impermeable material, (c) pressure equalization means arranged between said reservoir and said outer surface for pressure equalization between the outer space of said reservoir and the outer environment of said device housing, (d) a conveying and dosing unit contained in said device housing for conveying said infusion liquid from said reservoir to a catheter discharge opening, and (e) re-filling means for re-filling said reservoir with said infusion liquid from outside of said housing.
In accordance with another broad aspect of the invention there is provided an infusion device intended for implantation in a living body, comprising a device housing implantable in the patient's body and having a reservoir for infusion fluid and having a conveying and dosing unit for conveying the i.nfusion fluid from the reservoir to a catheter discharge opening, and pressure equaliæation means operatively associated with said reservoir for tending to maintain pressure equalization between the pressure of infusion fluid and the environment of the device housing, said pressure equalization means comprising body fluid isolating means for preventing admixture of body fluid with the infusion fluid of said reservoir.
Further advantages and details of the invention derive - 3a -3~
from the following figure description of exempl~ry embodiments with reference to the accompanying drawing sheets; ancl other objects, features and advan-tages will be - 3b -361~5 apparent from this detailed disclosure and from the appended claims.
BRIEF DESCRIPTION OF THE DRAWING
Figures 1 through 5 show in a highly schematic illustration various-ly constructed infusion devices in cross section; and ~ igure 6 schematically illustrates an external view of an infusion device representing a further embodiment of the invention.
DETAILED DESCR PTION
In Figure 1, reference numeral 1 indicates a device housing of an implantable infusion device. As a flat capsule, this is a three-dimensional shape roughly equivalent to the housing of a heart pacemaker and is formed of implantable material compatible with body tissue~ for example titanium. A
conveying and dosing unit 2, a unit 3 with electronic circuits for the drive and control of the conveying and dosing unit 2, and an energy supply unit ~
(battery) are indicated in the device housing 1; 5 indicates a catheter which can be placed at a suitable location inside the patient's body. 6 indicates a reservoir for infusion fluid.
Insulin, for example, can be percutaneously introduced as infusion fluid into the reservoir 6 over a re-filling septum 8 introduced into the device housing and having a connecting line 10. To this end~ the re-filling septum 8 consists of a self-sealing elastomer which can be punctured with a standard injection cannula.
The reservoir 6 :Eor the :Eluid is protected against damage during re-filling of infusion fluid by means of a so-called needle stopper 9. A
conveying wick can be situated within the reservoir 6, the fluid being suctioned off bubble-free over a conveyor tube 7 to the discharge catheter 5 from said wick by means of the conveying and dosing unit 2.
In this regard~ the structure of an infusion device is known Erom 3~;~
the prior art. Where the known infusion devices are hermetically encapsulated for the purpose of maintaining under-pressure in the device housing, a dia-phragm 11 is now inserted to form part of the wall of the device housing 1.
In the embodiment according to Figure 1, the diaphragm 11 consists oE hydrophobic material with porcs which are so fine that, even given the maximum pressure dif:Eeren-tial between the housing interior and the environment, no body fluid is allowed to pass through the pores. The same also applies to body cells and/or bacteria. To this end, standard hydrophobic filters such as frits or diaphragm filters can be employed which, for example, consist of polyolefins, PTFE or of similar materials.
With such a design of the infusion device, it is guaranteed that, given a continuous fluid disharge from the reservoir, the gas dissolved in the surrounding body tissue or in the body fluids can enter into the device housing.
As a result, a pressure equalization is largely seen to. Since the gas pressure in the body tissue or, respectively, in the body fluid approximately corresponds to the external air pressure, a matching to the barometric pressure of the environment is likewise guaranteed.
Given transcutaneous re-filling of the reservoir, it is expedient to first always suction the remaining content of fluid in the reservoir out.
Given such a comparatively fast operation, practically no gas from the environ-ment of the device housing can di:Efuse-in so that an under-pressure can briefly arise. Given the immediately following re-filling of the reservoir, the gas present in the device housing is d:isplaced into the surrounding body tissue and is absorbed there. It can be expedient to suction off a device-external gas bubble which may potentially arise.
In Figure 2, the reference numerals 21 through 28 as well as 31 correspond in their sequence to the reference numerals of Eigure 1 increased ~ 3~3~
by twenty. Specifically indicated with 29 is a suction wick in the reservoir.
In the embodiment according to Figure 2, the reservoir 26 is rigidly designed for containing the infusion fluid. This has the advantage that a part of the reservoir 26 simultaneously forms the housing wall and that the re-Eilling septum 28 can lead directly into the reservoir 26. Thereby, the needle stopper is advantageously directly integrated in the housing wall. Certain structural simplifications also derive. A syringe for percutaneous sucking or, respective-ly, re-filling of the infusion fluid through the indicated body tissue is referenced with 30.
In this exemplary embodiment, the diaphragm 31 directly closes off the reservoir 26 with infusion fluid from the body tissue. ~o leakage of fluids can be permitted, so that the hydrophobia of the diaphragm 31 is an unCOJI-ditional prerequisite~
Given this embodiment of the invention, the pressure equalization ensues by means of direct gas exchange between the environment and the reservoir 26. For this reason, the bubble-free sucking of fluid by the conveying and dosing unit 22 is to be guaranteed by means of the wick 29. Further, it must also be seen to that the conveyor wick 29 is in contact with infusion fluid given all filling conditions of the reservoir 26 and given every possible patient position.
In the infusion device of Figure 3, the sequence of reference numerals 41 to 51 again represent units corresponding to those in Figure l; in accord with Figure 1, a flexible fluid reservoir 46 is provided. According to this embodiment of the invention, the diaphragm 51 which is introduced in the housing wall of the device housing 41 consists of fine-pore, hydrophilic material so that low-molecular body fluids can proceed through the pores. The pore size of the diaphragm 51 is selected in such manner that larger fluid ;6 molecules and, in particular, body cells and/or bacteria as well are arrested.
In this embodiment, the pressure equalization is achieved solely by means of the exchange of body fluid. BeFore the transcutaneous re~filling of the inEusion fluid, medication residues are again to be suctioned out via thc re-filling septum 48 with a syringe. To that end, a buffer volume with a compressible agent, i.e., a gas, must exist in the device housing 41. Ex-pediently, a separate, flexible bellows 53 with a gas contained therein is pro-vided, said bellows matching to the respectively existing volume. Likewise, the elastic container of the bellows 53 can also contain a liquid or some other substance with a vapor pressure which is lower than the external barometric pressure and, thus, guarantees a volume-dependent pressure.
Given the embodiment of Figure 3, the thickness, area and the mater-ial of the hydrophilic diaphragm 51 are selected in such manner that the dia-phragm has a relatively low flow resistance. By so doing, no significant under-pressure arises in the reservoir 46 even given the maximum pump rate of the conveying and dosing unit 42. Fabric or fiber strengthened hydrogels, for example, are suitable as materials for the diaphragm 51. In order to quickly remove the excess body fluid from the inside space of the housing 41 and to re-introduce it into the body tissue during transcutaneous re-filling of the reservoir 46 with infusion fluid, a valve 52 is additionally provided in the housing, said valve opening given over-pressure in the inside o:F the housing and letting the fluid out.
The exemplary embodiment according to ~igure 4 is fundamentally constructed in accord with Figure 3, whereby corresponding units derive in the numerical sequence of 61 through 71. A so-called diffusion diaphragm 71 having a high permeability for gases is specifically provided here as the diaphragm, consisting for example~ of silicone. rhe pressure equal:ization between the 3~i~
inside of the housing and the environment given this embodiment of the inven-tion, thus, ensues solely by means of diffusion, this completely sufficing given the usual, slow emptying of the reservoir as a result of the micro-dosing by the conveying and dosing unit 62. Since a diffusion-determined rate of gas exchange does not suffice during re-filling, a valve 72 is again addition-ally provided. As a result, a significantly faster escape of the gas from the device housing 1 in comparison to the diffusion rate is possible given per-cutaneous re-filling of the reservoir 66. It is also possible as an alternative to a valve, that an elastic diffusion diaphragm of such nature is employed which bulges toward the outside until the excess pressure has been dismantled by diffusion.
The valve 72 can consist of a rubber plug 73 in the wall of the device housing 61 which plug 73 covers an opening 74 in the housing wall and tightly closes it under normal pressure but opens given excess pressure in the inside of the housing.
In Figure 5, the reference numeral 81 through 91 denote the units described on the basis of the preceding Figures in a corresponding numerial se-quence. Given this embodiment of the invention, a gas-permeable or fluid-permeable diaphragm can be facultatively employed as the diaphragm 91. In addition to the fluid re-filling septum 88, a further septum 92 is provided as a separate paracentesis system which again consists of a self-sealing elastomer with following needle stopper 93. An internal tube 9~ is conducted from the septum 92 to the lowest location of the housing.
Given the infusion device according to Figure 5, the pressure equali-zation during the slow conveying operation and emptying of the reservoir 86 by the conveying and dosing unit 82 ensues over the gas-permeable or fluid-permeable diaphragm in accord with the exemplary embodiments described above.
736~
Now, however, the pressure or, respectively, volume equalization in the per-cutaneous re-filling of -the reservoir does not ensue by means of gas or fluid exchange with the surrounding body tissue but, rather, with the environment outside o:E the patient's body. Such an equalization can be particularly quickly accomplished; at the same time, the substances temporarily collected in the device housing are removed.
For the re-filling operation, thus, a cannula 95 is tapped into the second septum 92, said cannula 95 leading through the tissue toward the outside.
Particularly given employment of the hydrophilic diaphragm, this has the advan-tage that the body fluid is not expressed from the inside of the housing into the body but, rather, can flow off toward the outside. For the embodiment having the gas-permeable diaphragm, however, the second septum 92 is expediently disposed in such manner that condensed water or other body fluids which may have penetrated can be directly sucked off from the lowest housing parts with paracentesis cannula.
The further access to the inside of the capsule present in Figure 6 also has additional advantages in the manufacture and encapsulation of the overall infusion device.
Given the infusion devices according to Figures 1, 3, as well as 4 and 6, a flexible reservoir for the infusion fluid is respectively provided in the device housing. In the normal case, the fluid is filled into the reservoir bubble-free through the septum by means of a cannula or, respectively, syringe.
However, it can also be useful given these embodiments to provide an additional suction wick in accord with Figure 2 in order to safely guarantee a bubble-free pumping of the fluid even given gas bubbles which may potentially exist.
In the preceding Figures, the respective, differently designed diaphragms 11, 31, 51, 71 and 91 were always illustrated as a part of the g 3~
housing wall. ~lowever, it can be expedient to connect such a diaphragm to the device housing via an additional tube; this can be of significance particularly given a pressure equalization by means of exchanging body fluid.
In Figure 6, a correspondingly designed device housing with catheter 105 as well as a tube llO with terminating diaphragm lll is referenced with lOl.
'I'hcreby, the tube llO discharges at its proximal end in the corresponding chamber of the device housing lOl and is selected of such length that it can be placed in patient's body up to a reservoir of body fluid. The tube llO can itself consist of diaphragm material.
The inventive dif*usion devices described on the basis of the various exemplary embodiments can particularly be employed as an artificial pancreas for administering insulin in diabetes therapy. Thereby, considerable problems in the implantation of such devices into a living body are overcome with the invention. The pressure equalization between the inside space of the housing and the environment of the housing is respectively accomplished in that, during operation of the implanted diffusion device, the infused fluid is replaced by body gases or by body fluid as well. Thereby, the flexible reservoir in Figures l, 3, 4 and 5 respectively encloses the entire infusion fluid (not visibly illustrated), while the space not filled by the in-fusion fluid in the rigid reservoir in Figure 2 is filled up by body gases.
A reliable aspiration of infusion fluid is always guaranteed as a result of the above features independently of the filling condition of the reservoir even given changing spatial attitudes of the infusion device due to changes of position of the patient's body. The additional disposition of a pressure control valve in the housing wall particularly serves for the equali-zation of excess pressures occurring relatively briefly, for example in an airplane or when filling the reservoir.
3~;6 It will be apparent that many modifications and variations may be made without departing from the scope of the teachings and concepts of the present invention.
Claims (25)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. An infusion device for implantation in a patient's body, comprising (a) a device housing implantable in the patient's body said device housing having an outer surface, (b) a reservoir contained in said device housing for storing an infusion liquid therein, said reservoir comprising reservoir wall means formed of a flexible and fluid impermeable material, (c) pressure equalization means arranged between said reser-voir and said outer surface for pressure equalization between the outer space of said reservoir and the outer environment of said device housing, (d) a conveying and dosing unit contained in said device housing for conveying said infusion liquid from said reservoir to a catheter discharge opening, and (e) re-filling means for re-filling said reservoir with said infusion liquid from outside of said housing.
2. The infusion device according to claim 1, wherein said pressure equalization means comprises a gas-permeable diaphragm such that gas from the patient's interior may penetrate therethrough.
3. The infusion device according to claim 2, wherein said gas-permeable diaphragm is a part of said device housing.
4. Infusion device according to claim 1, characterized in that the pressure equalization means comprises a fluid-permeable diaphragm.
5. Infusion device according to claim 4, characterized in that the diaphragm is a part of the housing.
6. Infusion device according to claim 4, characterized in that the diaphragm is a part of a tube which can be placed at a suitable location in the patient's body.
7. Infusion device according to claim 4, characterized in that a pressure control valve is allocated to the device housing for the equalization of excess pressures occurring relatively briefly (for example, in an airplane or when filling the reservoir).
8. Infusion device according to claim 4, characterized in that a second paracentesis system which is conntected to the inside space of the housing is allocated to the device housing for the purpose of pressure equalization during the re-filling operation.
9. Infusion device according to claim 4, characterized in that the pressure equalization ensues by means of gases dissolved in the body.
10. Infusion device according to claim 9, characterized in that the diaphragm is comprised of hydrophobic material and exhib-its pores of a specific size.
11. Infusion device according to claim 7, characterized in that the diaphragm is a diffusion diaphragm having high gas perm-eability.
12. Infusion device according to claim 10, characterized in that the pores of the hydrophobic diaphragm are so small that, given the maximum pressure differential between the inside space of the housing and the environment in the patient's body, no body fluid as well as no body cells and/or bacteria can pass.
13. Infusion device according to claim 10, characterized in that the fluid reservoir forms a part of the device housing as a rigid container, whereby gases are let into the fluid reservoir with the infusion fluid via the hydrophobic diaphragm having pores of a specific size.
14. Infusion device according to claim 13, characterized in that a hydrophilic wick is provided in the reservoir for the purpose of avoiding an aspiration of gas, the infusion fluid being pumped out of the reservoir by the conveying and dosing unit via the hydrophilic wick.
15. Infusion device according to claim 4, characterized in that the pressure equalization ensues by means of an exchange of body fluid.
16. Infusion device according to claim 15, characterized in that the diaphragm is comprised of hydrophilic material and has pores of a specific size.
17. Infusion device according to claim 16, characterized in that diaphragm is comprised of a hydrophilic membrane whose pores are so small that no body cells and/or bacteria can pass through.
18. Infusion device according to claim 16, characterized in that the material of the hydrophilic diaphragm is a fiber streng-thened hydrogel.
19. Infusion device according to claim 16, characterized in that an elastic container for a buffered gas is allocated to the reservoir for the infusion fluid.
20. Infusion device according to claim 16, characterized in that the inside space of the housing contains an elastic container having a liquid with a vapor pressure lower than the external barometric pressure.
21. Infusion device according to claim 7, characterized in that the pressure equalization means comprises a chamber for rec-eiving body fluid via the diaphragm for effecting pressure equal-ization during discharge of infusion fluid from the reservoir, the pressure control valve being a liquid flow control valve for letting off body fluid from the chamber in the event of a trans-itory excess pressure.
22. Infusion device according to claim 7, characterized in that the pressure control valve is comprised of a silicone rubber plug sealing a flow channel in the housing.
23. Infusion device intended for implantation in a living body, comprising a device housing implantable in the patient's body and having a reservoir for infusion fluid and having a conveying and dosing unit for conveying the infusion fluid from the reservoir to a catheter discharge opening, and pressure equalization means operatively associated with said reservoir for tending to maintain pressure equalization between the pressure of infusion fluid and the environment of the device housing, said pressure equalization means comprising body fluid isolating means for preventing admix-ture of body fluid with the infusion fluid of said reservoir.
24. Infusion device according to claim 23 with said pressure equalization means comprising a fluid permeable diaphragm, said body fluid isolating means comprising reservoir wall means defining said reservoir and formed of fluid impermeable material.
25. Infusion device according to claim 23 with said pressure equalization means comprising a pressure equalizing diaphragm defin-ing a portion of the wall of said reservoir for infusion fluid, said pressure equalizing diaphragm being exposed to body fluid, and said body fluid isolating means comprising the construction of said pressure equalizing diaphragm which is exposed to body fluid so as to be permeable only to the gaseous phase and to prevent entry of body fluid in liquid phase into the reservoir for infusion fluid.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE19813138320 DE3138320A1 (en) | 1981-09-25 | 1981-09-25 | INFUSION DEVICE PROVIDED FOR IMPLANTATION IN A LIVING BODY |
| DEP3138320.3 | 1981-09-25 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1187366A true CA1187366A (en) | 1985-05-21 |
Family
ID=6142658
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000412170A Expired CA1187366A (en) | 1981-09-25 | 1982-09-24 | Infusion device intended for implantation in a living body |
Country Status (6)
| Country | Link |
|---|---|
| US (1) | US4511355A (en) |
| EP (1) | EP0075762B2 (en) |
| JP (1) | JPS5873365A (en) |
| AT (1) | ATE18996T1 (en) |
| CA (1) | CA1187366A (en) |
| DE (2) | DE3138320A1 (en) |
Families Citing this family (56)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| IL69431A (en) * | 1983-08-04 | 1987-12-31 | Omikron Scient Ltd | Liquid delivery system particularly useful as an implantable micro-pump for delivering insulin or other drugs |
| US4685902A (en) * | 1983-08-24 | 1987-08-11 | Becton, Dickinson And Company | Disposable reservoir cassette |
| US4661097A (en) * | 1984-06-01 | 1987-04-28 | The Johns Hopkins University | Method for clearing a gas bubble from a positive displacement pump contained within a fluid dispensing system |
| CA1254091A (en) * | 1984-09-28 | 1989-05-16 | Vladimir Feingold | Implantable medication infusion system |
| US4687468A (en) * | 1984-10-01 | 1987-08-18 | Cook, Incorporated | Implantable insulin administration device |
| US4626244A (en) * | 1985-02-01 | 1986-12-02 | Consolidated Controls Corporation | Implantable medication infusion device |
| NO165378C (en) * | 1985-11-22 | 1991-02-06 | Ellingsen O & Co | MEDICINE-GIVING DEVICE FOR IMPLANTATION IN THE HUMAN BODY. |
| US4813951A (en) * | 1987-05-20 | 1989-03-21 | Joel Wall | Self-actuated implantable pump |
| US5006997A (en) * | 1987-12-15 | 1991-04-09 | Shiley Infusaid, Inc. | Pump diagnostic system |
| US4898585A (en) * | 1988-05-18 | 1990-02-06 | Baxter Healthcare Corporation | Implantable patient-activated fluid delivery device with bolus injection port |
| US4898584A (en) * | 1988-05-18 | 1990-02-06 | Baxter Healthcare Corporation | Implantable patient-activated fluid delivery device |
| US4898583A (en) * | 1988-05-18 | 1990-02-06 | Baxter Healthcare Corporation | Implantable patient-activated fluid delivery device and outlet valve therefor |
| US4898582A (en) * | 1988-08-09 | 1990-02-06 | Pharmetrix Corporation | Portable infusion device assembly |
| FR2637188A1 (en) * | 1988-10-03 | 1990-04-06 | France Neurone Sa | Device for distributing a quantity of medical fluid, and the use of the device with a filling syringe |
| US4969884A (en) * | 1988-12-28 | 1990-11-13 | Alza Corporation | Osmotically driven syringe |
| US5019047A (en) * | 1989-06-16 | 1991-05-28 | Science Incorporated | Fluid delivery apparatus |
| AU644550B2 (en) * | 1989-06-16 | 1993-12-09 | Science Incorporated | Fluid delivery apparatus |
| US5163920A (en) * | 1991-01-30 | 1992-11-17 | Infusaid Inc. | Flow regulator damper element |
| FR2672803A1 (en) * | 1991-02-15 | 1992-08-21 | Renaudeaux Jean Pierre | Device for injecting medicaments in liquid phase |
| US5201728A (en) * | 1991-05-03 | 1993-04-13 | Giampapa Vincent C | Subcutaneous implantable multiple-agent delivery system |
| US5398850A (en) * | 1993-08-06 | 1995-03-21 | River Medical, Inc. | Gas delivery apparatus for infusion |
| US5578005A (en) * | 1993-08-06 | 1996-11-26 | River Medical, Inc. | Apparatus and methods for multiple fluid infusion |
| US5398851A (en) * | 1993-08-06 | 1995-03-21 | River Medical, Inc. | Liquid delivery device |
| DE4402380A1 (en) * | 1994-01-27 | 1995-08-03 | Hans Peter Prof Dr Med Zenner | Implantable dosing system |
| US5540665A (en) * | 1994-01-31 | 1996-07-30 | Alza Corporation | Gas driven dispensing device and gas generating engine therefor |
| SE9400821D0 (en) * | 1994-03-10 | 1994-03-10 | Siemens Elema Ab | Implantable infusion system with pressure neutral drug container |
| WO1996014834A1 (en) * | 1994-11-10 | 1996-05-23 | University Of Kentucky Research Foundation | Implantable refillable controlled release device to deliver drugs directly to an internal portion of the body |
| US5769823A (en) * | 1995-03-23 | 1998-06-23 | Tricumed Gmbh | Implantable infusion pump |
| US5700245A (en) * | 1995-07-13 | 1997-12-23 | Winfield Medical | Apparatus for the generation of gas pressure for controlled fluid delivery |
| US5957891A (en) * | 1995-10-11 | 1999-09-28 | Science Incorporated | Fluid delivery device with fill adapter |
| US5964261A (en) * | 1996-05-29 | 1999-10-12 | Baxter International Inc. | Implantation assembly |
| US6217556B1 (en) | 1998-03-19 | 2001-04-17 | Allegiance Corporation | Drainage catheter |
| US6564105B2 (en) * | 2000-01-21 | 2003-05-13 | Medtronic Minimed, Inc. | Method and apparatus for communicating between an ambulatory medical device and a control device via telemetry using randomized data |
| US6497699B1 (en) * | 2000-08-09 | 2002-12-24 | The Research Foundation Of State University Of New York | Hybrid neuroprosthesis for the treatment of brain disorders |
| US20040073175A1 (en) * | 2002-01-07 | 2004-04-15 | Jacobson James D. | Infusion system |
| AU2003208901A1 (en) * | 2002-02-01 | 2003-09-02 | The Cleveland Clinic Foundation | Microinfusion device |
| WO2005002642A2 (en) * | 2003-06-25 | 2005-01-13 | Medical Research Products-A, Inc. | Medication infusion device using negatively biased ambient pressure medication chamber |
| US20060264897A1 (en) * | 2005-01-24 | 2006-11-23 | Neurosystec Corporation | Apparatus and method for delivering therapeutic and/or other agents to the inner ear and to other tissues |
| US20110077579A1 (en) * | 2005-03-24 | 2011-03-31 | Harrison William V | Cochlear implant with localized fluid transport |
| WO2006133400A2 (en) * | 2005-06-08 | 2006-12-14 | California Institute Of Technology | Intravascular diagnostic and therapeutic sampling device |
| EP1839692B1 (en) * | 2006-03-30 | 2007-11-28 | Roche Diagnostics GmbH | Infusion system comprising an infusion unit and a remote control unit |
| US8221354B2 (en) * | 2006-04-27 | 2012-07-17 | Medtronic, Inc. | Infusion device with positive pressure elastic bladder reservoir |
| US8267905B2 (en) * | 2006-05-01 | 2012-09-18 | Neurosystec Corporation | Apparatus and method for delivery of therapeutic and other types of agents |
| US7803148B2 (en) * | 2006-06-09 | 2010-09-28 | Neurosystec Corporation | Flow-induced delivery from a drug mass |
| JP2009544355A (en) * | 2006-07-20 | 2009-12-17 | ニューロシステック コーポレイション | Devices, systems, and methods for ophthalmic drug delivery |
| GB0623395D0 (en) | 2006-11-23 | 2007-01-03 | Renishaw Plc | Port |
| US20090209945A1 (en) * | 2008-01-18 | 2009-08-20 | Neurosystec Corporation | Valveless impedance pump drug delivery systems |
| EP3075406A1 (en) * | 2008-04-30 | 2016-10-05 | ResMed R&D Germany GmbH | Apparatus and method for controlled delivery of a breathing gas to the respiratory tracts of a user |
| NZ589990A (en) | 2008-06-05 | 2013-04-26 | Resmed Ltd | Treatment of respiratory conditions by automatic control of humidity in high flow rate and with gas leakage at interface to nares |
| WO2010116363A1 (en) * | 2009-04-06 | 2010-10-14 | Realview Medical Limited | An implantable system, a device for inserting the implantable system and a method thereof |
| GB201002370D0 (en) | 2010-02-12 | 2010-03-31 | Renishaw Ireland Ltd | Percutaneous drug delivery apparatus |
| GB201217606D0 (en) | 2012-10-02 | 2012-11-14 | Renishaw Plc | Neurosurgical device and method |
| AU2014281685A1 (en) * | 2013-06-17 | 2016-01-21 | Minipumps, Llc | Vented implantable drug-delivery device |
| US11278665B2 (en) | 2016-11-22 | 2022-03-22 | Eitan Medical Ltd. | Method for delivering a therapeutic substance |
| US11357909B2 (en) | 2018-10-05 | 2022-06-14 | Eitan Medical Ltd. | Triggering sequence |
| CN112827009B (en) * | 2021-02-20 | 2022-11-25 | 山东第一医科大学附属省立医院(山东省立医院) | Embedded nutrition input port for gastrointestinal fistulization |
Family Cites Families (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3506005A (en) * | 1967-02-23 | 1970-04-14 | Arthur S Gilio | Pressure infusion device for medical use |
| US3647117A (en) * | 1969-08-22 | 1972-03-07 | Thomas S Hargest | Apparatus for intravenous feeding and the like |
| US3765414A (en) * | 1972-03-10 | 1973-10-16 | Hydro Med Sciences Inc | Drug release system |
| US4013074A (en) * | 1974-06-21 | 1977-03-22 | Siposs George G | Implantable medication-dispensing device |
| US4041944A (en) * | 1975-07-21 | 1977-08-16 | Rhodes William A | Body fluid transfusion and displacement apparatus and method |
| DE2652026C2 (en) * | 1976-11-15 | 1983-01-05 | Siemens AG, 1000 Berlin und 8000 München | Device for infusing liquids |
| 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 |
| DE2920975C2 (en) * | 1979-05-23 | 1985-08-14 | Siemens AG, 1000 Berlin und 8000 München | Extracorporeally portable infusion device |
| US4398908A (en) * | 1980-11-28 | 1983-08-16 | Siposs George G | Insulin delivery system |
-
1981
- 1981-09-25 DE DE19813138320 patent/DE3138320A1/en not_active Withdrawn
-
1982
- 1982-09-10 DE DE8282108368T patent/DE3270434D1/en not_active Expired
- 1982-09-10 AT AT82108368T patent/ATE18996T1/en active
- 1982-09-10 EP EP82108368A patent/EP0075762B2/en not_active Expired
- 1982-09-14 JP JP57160758A patent/JPS5873365A/en active Pending
- 1982-09-15 US US06/418,525 patent/US4511355A/en not_active Expired - Lifetime
- 1982-09-24 CA CA000412170A patent/CA1187366A/en not_active Expired
Also Published As
| Publication number | Publication date |
|---|---|
| DE3138320A1 (en) | 1983-04-14 |
| ATE18996T1 (en) | 1986-04-15 |
| JPS5873365A (en) | 1983-05-02 |
| US4511355A (en) | 1985-04-16 |
| EP0075762B2 (en) | 1989-06-14 |
| DE3270434D1 (en) | 1986-05-15 |
| EP0075762A1 (en) | 1983-04-06 |
| EP0075762B1 (en) | 1986-04-09 |
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