WO2004033000A1 - Mikrodialysesonde mit spiralförmiger leitung - Google Patents
Mikrodialysesonde mit spiralförmiger leitung Download PDFInfo
- Publication number
- WO2004033000A1 WO2004033000A1 PCT/EP2003/010534 EP0310534W WO2004033000A1 WO 2004033000 A1 WO2004033000 A1 WO 2004033000A1 EP 0310534 W EP0310534 W EP 0310534W WO 2004033000 A1 WO2004033000 A1 WO 2004033000A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- probe
- support body
- membrane
- probe needle
- perfusion solution
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14525—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using microdialysis
- A61B5/14528—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using microdialysis invasively
Definitions
- the present invention relates to a microdialysis probe, in particular a microdialysis probe for measuring the concentration of a dissolved substance in a tissue.
- Microdialysis probes generally have a probe body and an injection needle as a probe needle for insertion, for example, into a human or animal tissue, the probe needle being completely surrounded by the tissue.
- the probe needle comprises a feed line and a discharge line for a perfusion solution.
- a dialysis membrane is arranged in an area of the line of the perfusion solution, which comes into contact with the surrounding environment of the tissue. Between the ambient environment and the perfusion solution, the concentration compensation of permeable substances dissolved in the tissue occurs along the membrane surface.
- a conventional microdialysis probe has a coaxial structure, for example.
- Two hollow cylinders are arranged one inside the other, the inner hollow cylinder serving as a feed line for the perfusion solution, which is transferred in a transition region at a distal end region of the probe needle into the region between the inner cylinder and the outer cylinder and is returned in this annular channel.
- the dialysis membrane can, for example, be arranged in a front area when the perfusion solution is reversed, or it can partially form the outer hollow cylinder.
- microdialysis probes have the disadvantage that the perfusion solution only comes into contact with the surrounding environment of the tissue over a small membrane area and at most over the length of the probe needle, or that a membrane hollow fiber as the outer cylinder is exposed to the pressure of the tissue and the drainage can therefore be blocked , Furthermore, with a short probe needle there is often not enough time to allow the concentration to be fully balanced. In contrast, a long probe needle is uncomfortable for a user. With a straight one When the perfusion solution is returned, the flow rate may be too high to completely enable the desired concentration equalization.
- AI microdialysis probes in which the supply and discharge for a perfusion solution are arranged side by side.
- two tubes arranged next to one another with an overflow area are provided for the perfusion solution.
- concentration compensation may not be optimal.
- a microdialysis probe with a probe body and a probe needle for insertion into a tissue, which comprises an inlet and an outlet for a perfusion solution and a dialysis membrane
- at least the outlet of the perfusion solution is formed by a hollow channel, which at least on an outer circumference of the probe needle partially spiral, or helical, around the probe needle.
- the spiral-shaped part of the hollow channel preferably extends from a distal end region of the sod needle with the needle tip to the probe body from which the probe needle emerges.
- the entire hollow channel for the discharge is preferably provided with a dialysis membrane on its surface directed outward from the probe needle. In this way, the concentration can be equalized over the entire length of the spiral hollow channel.
- a hollow channel for the supply of the perfusion solution can run inside the probe needle, that is to say through the spiral hollow channel of the lead to the tip of the probe needle.
- a cylindrical plastic element can be provided with a central bore, which has a bore to the outer circumferential surface, which opens into the drainage spiraling around the plastic body.
- a further spiral hollow channel is provided for the supply of the perfusion solution.
- the two hollow channels for the supply and the discharge merge into one another in a reversal area at the distal end area of the probe needle.
- a dialysis membrane is preferably provided both on the surface of the spiral feed line that is directed outward from the probe needle and on the spiral discharge line. In principle, it is possible to provide the dialysis membrane only in partial areas of the probe needle. However, it is advantageous to arrange the dialysis membrane over the entire length of the hollow channels.
- the dialysis membrane can, for example, be a hollow fiber, which at the same time forms the hollow channel for the discharge, or also the feed line.
- a membrane hollow fiber has the advantage that no transitions between the membrane material and the needle material are necessary within the fabric.
- Both the feed line and the discharge line are preferably formed by a single hollow membrane fiber which is reversed in a distal end region of the probe tip.
- An elongated support body or a frame on which the membrane fiber is arranged in the manner according to the invention can be used to form the probe needle becomes.
- the feed line in the form of the hollow fiber can be guided through the central region of the support body or the frame and only emerge from the support body at the distal end region of the support body and run spirally around the support body back to the probe housing. However, it is preferred that the feed line also runs spirally around the outer region of the probe needle or the support body to the distal end region of the needle.
- the hollow fiber membrane undergoes a reversal and spirally runs in the spaces between the supply channel back to the probe housing and thereby forms the discharge of the perfusion liquid.
- the probe needle is preferably formed by a cylindrical support body which has at least one outwardly open recess in the form of a recess on its outer circumferential surface, which extends at least in sections, but preferably over the entire length of this support body, in a spiral around the support body.
- a membrane hollow fiber can be embedded in the recess in such a support body.
- the depressions are preferably as deep as the outer diameter of the hollow membrane fiber.
- the membrane hollow fiber is flush with the surface of the support body and is not exposed to a pressure exerted by the fabric.
- a dialysis membrane in the form of a hollow fiber over a cylindrical support body with a spiral recess for the supply or discharge, which has approximately the same inner diameter as the outer diameter of the support body. At least the areas of the support body should be covered with the recess by the hollow fiber membrane.
- the hollow fiber membrane can be attached, for example, on the peripheral surfaces of the support body between the depressions. For example, an adhesive or an adhesive can be used for this.
- the space between the slipped hollow fiber and the recess then forms the hollow channel at least for the supply of the perfusion solution, but preferably also for the discharge of the perfusion solution. If the hollow membrane fiber is closed in a region of the tip, that is to say it forms a type of membrane sock, then in this embodiment there is also no formation Transitions between the membrane material and the probe needle material within the tissue.
- a dialysis membrane in the form of a membrane layer or a membrane sheet is wrapped around a cylindrical support body with a spiral-shaped recess or depressions around the outer circumference of the support body.
- the abutting edges of the membrane layer are sealed tight and the membrane layer is fastened in the intermediate areas of the recess on the peripheral surface of the support body.
- This in turn creates the hollow channels for the discharge and supply of the perfusion solution between the membrane layer and the recess.
- the dialysis area corresponds to the width of a recess times the length of the spiral-shaped recess.
- the perfusion solution can come into contact with the surrounding environment over the entire length of the probe needle within the tissue.
- both the supply line and the discharge line spiral around the probe needle form a kind of double helix.
- the slope of the spiral is to be matched to a desired flow rate or a desired residence time of the perfusion solution within the tissue.
- a support body which forms the probe needle may be made of various plastics such as "example liquid crystal polymers, polybutylene terephthalate (PBT), or can be formed of PE or PET. Such materials can be for example processed by injection molding.
- Depressions for the supply or derivation can already be formed in the molding during the production of a cylindrical molding for the support body or can be provided subsequently by further processing such as milling, cutting or etching in this area cylindrical support body, or a frame, is generally cut obliquely to form a tip for insertion into a tissue.
- the distal end region of the support body is preferably ground in such a way that little pain arises for a user and the surrounding environment is little changed, as is the case, for. B. is described in the patent application with the title "injection needle tip", which goes back to the applicant and has the same filing date as the present application.
- the probe needle of the microdialysis probe can be self-piercing. However, it is also possible to use an insertion aid for the probe needle. This is particularly advantageous if large areas of the membrane are arranged unprotected on the surface of the support body.
- the design according to the invention of a microdialysis probe extends the way in which the perfusion solution comes into contact with the surrounding environment of the tissue without the probe needle having to be extended for this. Conversely, it is possible to produce the same length of cable with a shorter probe needle. This makes it easier for a user to wear a microdialysis probe.
- the leads according to the invention have a comparatively small diameter, the ratio of area to volume is improved, so that more perfusion fluid with an outer surface of the dialysis membrane and thus with the surrounding environment of the tissue in Can make contact.
- FIG. 1 shows a perspective view of a first embodiment of a probe needle according to the invention with a spiral feed and discharge line
- Figure 2 is a perspective view of a second embodiment of the present invention with a spiral lead and a straight lead.
- FIG. 1 shows a cylindrical support body (1), or a frame, which forms a probe needle for a microdialysis probe.
- a recess or recess (3) begins, which initially runs in the longitudinal direction of the support body (1) on its outer surface.
- the depression (3) changes into a spiral course. The spiral course extends up to a distal end region (2) of the support body (1) and forms the depression for a supply of a perfusion solution.
- the depression (3) undergoes a reversal (5) and runs from there in a spiral between the first spiral course for the supply line back to the initial area of the support body 1 and thus forms the depression for the discharge of the perfusion liquid.
- a reversal (5) runs from there in a spiral between the first spiral course for the supply line back to the initial area of the support body 1 and thus forms the depression for the discharge of the perfusion liquid.
- a hollow membrane fiber can then be inserted, which follows the course of the depression, that is, from an initial area of the support body (1) along the depression (3) through the area (4 ) over the deflection (5) to the distal end region (2) of the support body (1) and back through the spiral region (4) to the start region of the support body (1). It is also possible, as described above, to place a hollow membrane fiber with an inside diameter that approximately corresponds to the outside diameter of the support body (1) over the support body (1) and to fasten it in the interstices of the surface between the depressions (3), the Inlet and outlet is formed by the recess closed by the membrane.
- FIG. 2 shows a further embodiment of a microdialysis probe according to the invention with a cylindrical support body (1), which likewise has a spiral recess or depression (3) on its outer surface. This recess is intended for the derivation of the perfusion solution.
- a straight hollow channel (6) is provided as the lead of the perfusion solution in a central region of the support body (1) along the longitudinal axis of the support body, which runs from an initial region of the support body 1 to just before the distal end region (2) of the support body. Shortly before the end region (2), the hollow channel (6) is deflected in the direction of the outer peripheral surface of the supporting body (1), so that it emerges from the outer peripheral surface and forms the reversal (5).
- the outlet opening of the straight hollow channel opens into the spiral-shaped recess (3).
- a membrane hollow fiber (7) in the form of a membrane sock, which is closed at the tip (1), is arranged above the support body (1).
- the membrane hollow fiber has an inner diameter that is slightly larger than the outer diameter of the support body (1).
- the hollow membrane fiber (7) is fastened in the intermediate areas (8) between the spiral course of the depression on the support body (1), as a result of which a hollow channel for the derivation of the perfusion solution is formed between the hollow membrane fiber and the support body.
- the support body (1) is completely enclosed in the example shown by the dialysis membrane. When inserting such a probe needle, there are no transition points between the membrane material and the material of the support body within the tissue.
- the probe needle made of support body (1) and membrane hollow fiber (7) is connected to a probe body (9), from which the supply line is supplied with perfusion solution and into which the perfusion solution is returned via the discharge line after the concentration compensation.
- a support body for the probe tip which does not provide any recesses for forming the lines or for receiving a hollow membrane fiber.
- a hollow fiber membrane can be wound spirally around such a smooth cylindrical support body and attached to it at certain intervals by an adhesive.
- a method can be used to lay a dialysis membrane in the spiral-curved manner described, as described in the patent application entitled "Microdialysis probe and method for its production", which goes back to the applicant and has the same filing date as the present invention
- the dialysis membrane first lies against a shaping agent and is then brought into a predetermined shape by bending or shaping the shaping agent, after which an adhesive or a connecting means, such as a putty or an adhesive, is at least partially attached a bending point of the dialysis membrane so that the membrane is held in the predetermined shape.
- the shaping agent is removed from the dialysis membrane.
- the shaping agent can be a filament that is drawn through the hollow fiber membrane. The shape is determined by the spiral course the e microdialysis membrane according to the invention.
Abstract
Description
Claims
Priority Applications (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CA002499808A CA2499808A1 (en) | 2002-10-04 | 2003-09-22 | Microdialysis probe with a spiral line |
EP03770947A EP1545651A1 (de) | 2002-10-04 | 2003-09-22 | Mikrodialysesonde mit spiralförmiger leitung |
AU2003280339A AU2003280339A1 (en) | 2002-10-04 | 2003-09-22 | Microdialysis probe with a spiral line |
JP2004542365A JP2006501909A (ja) | 2002-10-04 | 2003-09-22 | ら旋状の線を有するマイクロ透析プローブ |
US11/096,708 US20050277820A1 (en) | 2002-10-04 | 2005-04-01 | Microdialysis probe with a spiral line |
US11/940,636 US7828763B2 (en) | 2002-10-04 | 2007-11-15 | Microdialysis probe with a spiral line |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE10246207.0 | 2002-10-04 | ||
DE10246207A DE10246207B4 (de) | 2002-10-04 | 2002-10-04 | Mikrodialysesonde mit spiralförmiger Leitung |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/096,708 Continuation US20050277820A1 (en) | 2002-10-04 | 2005-04-01 | Microdialysis probe with a spiral line |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2004033000A1 true WO2004033000A1 (de) | 2004-04-22 |
Family
ID=32086842
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/EP2003/010534 WO2004033000A1 (de) | 2002-10-04 | 2003-09-22 | Mikrodialysesonde mit spiralförmiger leitung |
Country Status (7)
Country | Link |
---|---|
US (2) | US20050277820A1 (de) |
EP (1) | EP1545651A1 (de) |
JP (1) | JP2006501909A (de) |
AU (1) | AU2003280339A1 (de) |
CA (1) | CA2499808A1 (de) |
DE (1) | DE10246207B4 (de) |
WO (1) | WO2004033000A1 (de) |
Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2006263290A (ja) * | 2005-03-25 | 2006-10-05 | Masayuki Kitano | 検査プローブ及び検査方法 |
GB2457469A (en) * | 2008-02-13 | 2009-08-19 | Probe Scient Ltd | Molecular exchange device |
US8142389B2 (en) | 2002-10-09 | 2012-03-27 | Roche Diagnostics International Ag | Microdialysis probe and method for the production thereof |
US8790586B2 (en) | 2006-09-28 | 2014-07-29 | Probe Scientific Limited | Molecular exchange device |
US8961791B2 (en) | 2008-02-13 | 2015-02-24 | Probe Scientific Limited | Molecular exchange device |
WO2020179780A1 (ja) * | 2019-03-05 | 2020-09-10 | エーザイ・アール・アンド・ディー・マネジメント株式会社 | 五環式複素環化合物 |
Families Citing this family (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE10246207B4 (de) * | 2002-10-04 | 2008-04-03 | Disetronic Licensing Ag | Mikrodialysesonde mit spiralförmiger Leitung |
US10251993B2 (en) | 2016-02-26 | 2019-04-09 | Feng Chen | Hemodialysis device |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1999059655A1 (en) * | 1998-05-19 | 1999-11-25 | Transvivo, Inc. | Apparatus and method for in vivo hemodialysis |
DE19937099A1 (de) | 1999-08-06 | 2001-02-15 | Disetronic Licensing Ag | Mikrodialysesonde |
Family Cites Families (16)
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US4016863A (en) * | 1975-08-27 | 1977-04-12 | Brantigan John W | Tissue tonometer device for use in measuring gas in body tissue |
DE2734248A1 (de) * | 1977-07-29 | 1979-02-08 | Fresenius Chem Pharm Ind | Tragbare kuenstliche niere |
DE2734247C2 (de) * | 1977-07-29 | 1984-07-19 | Fresenius AG, 6380 Bad Homburg | Vorrichtung zur fortlaufenden chemischen Analyse im lebenden Körper |
DE2737922A1 (de) * | 1977-08-23 | 1979-03-08 | Fresenius Chem Pharm Ind | Kuenstliche endokrine druese |
US4516580A (en) * | 1981-12-28 | 1985-05-14 | Polanyi Michael L | Continuous blood gas monitoring |
SE434214B (sv) * | 1982-12-01 | 1984-07-16 | Carl Urban Ungerstedt | Dialysprob, avsedd for inforing i biologiska vevnader |
US4726381A (en) * | 1986-06-04 | 1988-02-23 | Solutech, Inc. | Dialysis system and method |
US4763658A (en) * | 1986-06-04 | 1988-08-16 | Solutech, Inc. | Dialysis system 2nd method |
US4774955A (en) * | 1986-06-04 | 1988-10-04 | Solutech, Inc. | Programmable dialyzer system analyzer and method of use |
US4765339A (en) * | 1986-06-04 | 1988-08-23 | Solutech, Inc. | Closed loop dialysis system |
US4901727A (en) * | 1988-05-05 | 1990-02-20 | The Boc Group, Inc. | Micro-probe for gas sampling |
GB9320850D0 (en) * | 1993-10-09 | 1993-12-01 | Terwee Thomas H M | Monitoring the concentration of a substance or a group of substances in a body fluid of a human or an animal |
DE19714572C1 (de) * | 1997-04-09 | 1998-06-25 | Haindl Hans | Katheter zur Messung chemischer Parameter, insbesondere zum Einführen in biologisches Gewebe, Flüssigkeiten oder dergleichen |
US6272370B1 (en) * | 1998-08-07 | 2001-08-07 | The Regents Of University Of Minnesota | MR-visible medical device for neurological interventions using nonlinear magnetic stereotaxis and a method imaging |
DE10246207B4 (de) * | 2002-10-04 | 2008-04-03 | Disetronic Licensing Ag | Mikrodialysesonde mit spiralförmiger Leitung |
US20050137471A1 (en) * | 2003-12-18 | 2005-06-23 | Hans-Peter Haar | Continuous glucose monitoring device |
-
2002
- 2002-10-04 DE DE10246207A patent/DE10246207B4/de not_active Expired - Lifetime
-
2003
- 2003-09-22 CA CA002499808A patent/CA2499808A1/en not_active Abandoned
- 2003-09-22 EP EP03770947A patent/EP1545651A1/de not_active Withdrawn
- 2003-09-22 AU AU2003280339A patent/AU2003280339A1/en not_active Abandoned
- 2003-09-22 WO PCT/EP2003/010534 patent/WO2004033000A1/de not_active Application Discontinuation
- 2003-09-22 JP JP2004542365A patent/JP2006501909A/ja active Pending
-
2005
- 2005-04-01 US US11/096,708 patent/US20050277820A1/en not_active Abandoned
-
2007
- 2007-11-15 US US11/940,636 patent/US7828763B2/en not_active Expired - Lifetime
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1999059655A1 (en) * | 1998-05-19 | 1999-11-25 | Transvivo, Inc. | Apparatus and method for in vivo hemodialysis |
DE19937099A1 (de) | 1999-08-06 | 2001-02-15 | Disetronic Licensing Ag | Mikrodialysesonde |
Cited By (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8142389B2 (en) | 2002-10-09 | 2012-03-27 | Roche Diagnostics International Ag | Microdialysis probe and method for the production thereof |
JP2006263290A (ja) * | 2005-03-25 | 2006-10-05 | Masayuki Kitano | 検査プローブ及び検査方法 |
JP4658656B2 (ja) * | 2005-03-25 | 2011-03-23 | 雅之 北野 | 検査プローブ及び検査方法 |
US8790586B2 (en) | 2006-09-28 | 2014-07-29 | Probe Scientific Limited | Molecular exchange device |
GB2457469A (en) * | 2008-02-13 | 2009-08-19 | Probe Scient Ltd | Molecular exchange device |
GB2457469B (en) * | 2008-02-13 | 2012-11-07 | Probe Scient Ltd | Molecular exchange device |
US8961791B2 (en) | 2008-02-13 | 2015-02-24 | Probe Scientific Limited | Molecular exchange device |
WO2020179780A1 (ja) * | 2019-03-05 | 2020-09-10 | エーザイ・アール・アンド・ディー・マネジメント株式会社 | 五環式複素環化合物 |
Also Published As
Publication number | Publication date |
---|---|
CA2499808A1 (en) | 2004-04-22 |
DE10246207A1 (de) | 2004-05-06 |
US7828763B2 (en) | 2010-11-09 |
DE10246207B4 (de) | 2008-04-03 |
US20050277820A1 (en) | 2005-12-15 |
AU2003280339A1 (en) | 2004-05-04 |
US20080228131A1 (en) | 2008-09-18 |
EP1545651A1 (de) | 2005-06-29 |
JP2006501909A (ja) | 2006-01-19 |
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