KR20060109859A - Catheter for uniform delivery of medication - Google Patents

Abstract

Provided is a catheter for uniform delivery of medication which has an improved configuration for delivering a fluid medication to a cut zone of an anatomical region. The catheter(200) for uniform delivery of medication comprises: an elongated tube(202); and an elongated member(206). The elongated tube(202) has a proper size for being inserted into an anatomical region, and includes: a closed remote end(210); and many exit holes(204) which are arranged along the length of the elongated tube(202) itself and build an infusion section. The elongated member(206) is located inside the elongated tube(202), and has a size for building an annular space(208) between itself and the elongated tube(202), as well as is configured by means of a porous substance.

Description

Catheters for Uniform Delivery of Therapeutic Agents

1 is a schematic side view of a catheter with features and advantages in accordance with a first embodiment of the present invention.

FIG. 2 is a cross-sectional view of the catheter of FIG. 1 taken along line 2-2 of FIG.

3 is a cross-sectional view of the catheter of FIG. 1 taken along line 3-3 of FIG.

4 is a perspective view of the distal end and the support beam of the catheter of FIG. 1, taken along line 4-4 of FIG.

5 is a side view of a catheter with features and advantages according to a second embodiment of the present invention.

6 is a cross-sectional view of the catheter injection portion of FIG. 5 taken along line 6-6 of FIG.

7 is a cross-sectional view of a catheter with features and advantages in accordance with a third embodiment of the present invention.

8 is a side view of a catheter with features and advantages according to a fourth embodiment of the present invention.

9 is a side view of a catheter with features and advantages in accordance with a fifth embodiment of the present invention.

FIG. 10A is a cross-sectional view of the catheter of FIG. 9, illustrating an unextended state of the spring. FIG.

FIG. 10B is a cross-sectional view of the catheter of FIG. 9, illustrating an extended state of the spring. FIG.

11 is a cross-sectional view of a catheter with features and advantages in accordance with a sixth embodiment of the present invention.

12 is a side view of a catheter with features and advantages in accordance with a sixth embodiment of the present invention.

13 is a longitudinal cross-sectional view of a catheter with features and advantages according to a seventh embodiment of the present invention.

Figures 14 to 16 are longitudinal cross-sectional views of the catheter, similar to the catheter, showing an alternative attachment between the inner porous member and the tube.

17 is a cross-sectional view of the catheter according to FIGS. 13 to 16, wherein the porous member inside shares a center with the outer tube.

FIG. 18 is a cross-sectional view of the catheter according to FIGS. 13 to 16, wherein the inner porous member does not share a center with the outer tube.

19 is a schematic diagram of the catheter of the present invention, used in conjunction with an air removal filter.

20 is a side view of a catheter with features and advantages in accordance with an eighth embodiment of the present invention.

21 is a side view of a catheter with features and advantages in accordance with a ninth embodiment of the present invention.

22 is a schematic of the use of the catheter of the present invention to treat blood clotting.

The present invention relates to a catheter. More specifically, the present invention relates to a catheter that uniformly delivers fluid medication to the infusion portion.

Infusion catheters for delivery of liquid therapeutics to anatomical systems such as the human body are well known in the art. Such catheters generally have a flexible hollow tube that is inserted into any part of the anatomy. Hollow tubes generally have one or more axial lumens through which fluid can flow. The proximal end of this catheter tube is connected to a source of fluid from which the fluid enters the catheter tube. The fluid flows into one of the lumens under pressure provided at the proximal end. Each lumen commonly has one or more exit holes along the inlet of the distal end of the tube to allow fluid to exit the tube. These exit holes are created by drilling the side walls of the hollow tube.

For any medical condition, it is advantageous to deliver the liquid therapeutic agent to multiple sites in the wound area. For example, some wounds that require analgesics are connected to multiple nerve endings rather than one nerve stem. An example of such a wound is a surgical incision. As mentioned earlier, it is known that there are a number of exit holes through which the liquid therapeutic agent exits the catheter tube. The exit holes are located at various axial and circumferential positions along the catheter tube to adjust the position of the site where the drug is to be delivered. One example of a catheter of this type is described in Eldor, US Pat. No. 5,800,407. In addition, in some cases, it is desirable to deliver such therapeutic agents under low pressure so that the fluid is delivered at a relatively slow rate. For example, some analgesics should be delivered slowly to avoid toxicity and other side effects. In addition, in many cases, it is desirable to administer the liquid therapeutic agent at a substantially constant rate through the catheter infusion so that the therapeutic agent is evenly distributed throughout the wound area.

Unfortunately, existing catheters with multiple outlet holes, such as the catheter disclosed by Elder, have a tendency for fluid to be discharged only through the outlet hole (s) closest to the proximal end of the inlet of the catheter tube, when transporting liquid therapy under low pressure. There are disadvantages. This is because the fluid flowing through the tube is more easily discharged through the exit hole providing the least flow resistance. The longer the flow path of the fluid in the lumen, the greater the flow resistance and pressure drop experienced by the fluid. The proximal outlet hole provides the smallest flow resistance and pressure drop. Therefore, the fluid tends to exit the catheter tube mainly through this exit hole. As a result, the liquid medication is delivered only to a small area within the wound area. The tendency for the fluid to flow undesirably only through the nearest exit hole depends on the size of the exit hole, the total number of outlets and the flow rate. As the size or number of outlets increases, the tendency for the fluid to exit only to the nearest outlet increases. On the contrary, when the flow rate increases, such a tendency of the fluid decreases.

The tendency for fluid to flow undesirably only through the closest exit hole of the catheter can be solved in some cases by increasing the flow rate or hydraulic pressure, which causes the fluid to flow through more exit holes of the catheter. In fact, if the flow rate or hydraulic pressure is high enough, the fluid will flow through all exit holes. However, sometimes it is medically desirable to deliver the formulation at a relatively slow rate, ie at a low pressure. Also, even if it is acceptable or desirable to deliver the fluid at high pressure, previous catheters do not deliver the fluid evenly along the infusion. Rather, the flow rate through the exit hole closer to the distal end of the infusion tends to be greater than the flow rate through the exit hole closer to the distal end. This is because the fluid passing through the closer outlet hole experiences less flow resistance and pressure drop. In contrast, the fluid flowing through the distant outlet holes experiences greater flow resistance and pressure drop, resulting in a lower flow rate. The farther the exit hole, the lower the discharge flow rate of the fluid. As a result, the formulation distribution is uneven throughout the wound area.

In another known type of injection catheter, there are several lumens within the catheter tube. Each lumen has an exit hole made by drilling a hole in the wall of the tube. These outlets are in different axial directions along the inlet of the catheter tube. In this way, the liquid therapeutic agent can be delivered to various sites within the wound area. This type has improved latex distribution, but there are some disadvantages. One of them is that the flow rate of the fluid through the outlets is not the same, because the larger the exit hole, the greater the flow resistance, for the same reason as discussed above. Another disadvantage is that the number of lumens and the resulting number of fluid outlets is limited because of the small diameter of the catheter tube. As a result, the fluid is delivered only to very limited locations within the wound area. Another disadvantage is that the proximal ends of the lumens must be attached to one complex manifold, which increases the cost of producing the catheter.

An example of a catheter that more uniformly administers a liquid therapeutic agent through the catheter infusion is disclosed in Wang, US Pat. No. 5,425,723. Wang discloses an injection catheter comprising one outer tube, one inner tube concentrically within the outer tube, and a central lumen within the inner tube. The inner tube is smaller in diameter than the outer tube so that an annular passage is formed therebetween. The outer tube has a plurality of exit holes spaced at regular intervals, defining the inlet of the catheter. In use, the fluid flowing into the central lumen passes through side holes strategically disposed on the sidewalls of the inner tube. In particular, the spacing between adjacent side holes decreases along the length of the inner tube, leading to more fluid to escape through the farther side holes. The fluid then flows longitudinally through the annular passageway before exiting through the exit hole in the outer tube wall. In the annular passage, the fluid may flow in either the distal or proximal end, depending on the location of the nearest outlet in the outer tube. This form allows fluid to exit the catheter at a more constant flow rate.

Unfortunately, Wang's catheter is only effective for delivering relatively high pressure fluids. When used to deliver fluids at relatively low pressures, Wang initiated catheter does not provide uniform administration of fluids. Instead, the fluid is likely to exit through the side holes of the inner and outer tubes closest to the proximal end of the catheter inlet. Because these holes provide the lowest flow resistance. Even with high pressure delivery, there are some limitations to this structure. One limitation is that the concentric tube structures are relatively complex and difficult to manufacture. Both tubes should be flexible enough to maneuver through the anatomy, while the annular passage should be open to allow the fluid to flow uniformly therein. Another limitation is that if there is a bend in the inlet of the tube, the annular passage can be interrupted. Flexure in the catheter deforms the annular passageway or allows the inner and outer tubes to contact. This results in a non-uniform hydraulic pressure in the longitudinal cross section of the annular passage, resulting in an uneven fluid transfer.

Accordingly, there is a need for an improved injection catheter that uniformly delivers a liquid therapeutic agent along the infusion portion, both effective and relatively simple and easy to manufacture, for both high and low flow rate delivery. In addition, it is recognized that certain classes of catheters, such as Wang's catheter, deliver fluid evenly only at high hydraulic pressures or high flow rates. However, there is a need for an injection catheter that belongs to this class but is relatively simple and easy to manufacture, and that can maintain uniform fluid delivery even when bent or otherwise physically modified.

Accordingly, it is a major object and advantage of the present invention to address some or all of these limitations and to provide an improved catheter for delivering a liquid therapeutic agent to the wound area of the anatomical site.

According to one embodiment of the present invention, there is provided a catheter comprising an elongated tubular member made of a porous membrane, which uniformly delivers fluid to the anatomical site. The membrane is sized to be inserted through the subcutaneous layer surrounding its anatomical portion, such as human skin. The membrane is of a type such that, under a certain pressure, the fluid flowing into one open end of the tubular member can flow through the side wall of the tubular member at a sufficiently constant velocity along the tubular member. The present invention also provides a method for uniformly delivering fluid to an anatomical site, the method comprising inserting an elongated tubular member into the anatomical site and introducing the fluid to one open end of the tubular member under some pressure. do.

In another embodiment, the present invention provides a catheter and method for uniformly delivering fluid to an anatomical site. The catheter consists of one long support and one porous membrane surrounding the support. The support is such that one or more lumens are formed between it and the film. Alternatively, the support may be a tubular member having a plurality of holes therein. The method consists of inserting the catheter described above into the dissection and introducing the fluid under pressure into the proximal end of the one or more lumens. Advantageously, the fluid enters the anatomy through the membrane at a sufficiently constant rate. The present invention further provides a method of making the catheter comprising forming a long support and wrapping the support with a porous membrane such that at least one lumen is formed between it and the membrane.

In another embodiment, the present invention provides a catheter and method for uniformly delivering fluid to an anatomical site. The catheter consists of an elongated tube containing a plurality of exit holes along its length and a tubular porous membrane existing concentrically within the tube. The tube and membrane define the lumen. The method consists of inserting the catheter into the anatomical site and introducing the fluid at a certain pressure into the proximal end of the lumen so that the fluid enters the anatomical site, preferably through the membrane and the exit hole, at a sufficiently constant velocity. . The present invention further provides the formation of one elongated tube, providing a plurality of outlet holes along the length of the tube, forming one tubular porous membrane and allowing the tubular porous membrane to exist concentrically into the tube. It provides a method of making the catheter comprising the step of defining a single lumen.

In another embodiment, the present invention provides an apparatus and method for uniformly delivering fluid to an anatomical site. The instrument comprises one long catheter with a plurality of exit holes along its length, and is preferably simple and easy to manufacture. The exit hole may function as a flow-restricting orifice. Alternatively, the flow restriction orifice can be made anywhere in the catheter or near the catheter. The exit hole may gradually increase in size along the length of the catheter such that the largest exit hole is at the distal side. Alternatively, the outlets may be laser drilled and approximately the same size. Preferably, the fluid flowing into the catheter under any pressure will flow through virtually all exit holes at substantially the same speed. The method consists of inserting the catheter into the anatomical site and introducing fluid into the proximal end of the catheter under some pressure. The fluid flows through the exit hole and enters the anatomy, preferably through all the exit holes at sufficiently the same speed. The present invention further provides a plurality of exit holes along the length of the catheter in such a way as to form a long catheter and allow the exit holes to gradually increase in size along their length from the proximal end to the distal end of the catheter. It provides a method for manufacturing the apparatus comprising the step of providing.

In another embodiment, the present invention provides a catheter and method for delivering a liquid therapeutic agent to an anatomical site. The catheter consists of a tube, a weeping tubular coil spring attached to the distal end of the tube and a stop to close the distal end of the spring. The tube and spring each define a portion of the central lumen. The spring has neighboring coils in contact with each other to prevent the fluid from escaping the lumen by radially flowing between the coils within the spring and below the threshold dispensation pressure. The spring has the property of increasing when the fluid pressure is greater than or equal to the threshold distribution pressure that causes the fluid to be administered from its lumen radially through the coils, ie "weep" through the spring. Alternatively, the fluid may whip through the defect of the spring coil. Preferably, the emulsion is distributed substantially uniformly throughout the length and circumference of the spring. In use, the fluid flows into one open proximal end of the tube and flows into the spring, allowing the fluid to whip through the spring by applying a pressure greater than or equal to the threshold dispense pressure.

In another embodiment, the present invention provides a catheter and method for delivering a liquid therapeutic agent to an anatomical site. The catheter consists of one tube with a distal end closed and one "weeping" tubular coil spring as described above, surrounded by the tube and concentrically present therein. There are a number of exit holes in the side wall along the length of the tube to define the inlet of the tube. The spring is present in its infusion to allow the lumen to be confined within the tube and the spring. In use, fluid flows into one proximal end of the tube, flows into the spring, and exerts a lumen as the fluid is whipped through the spring and then flows through the exit hole of the tube by applying a pressure greater than or equal to the threshold distribution pressure. To be dispensed from.

In another embodiment, the present invention provides a catheter consisting of one long tube and a solid, flexible member located within the tube. The tube has a closed distal end and a number of exit holes in the side wall of the tube. The outlets follow the length of the tube, defining the inlet of the catheter. The tube is sized to be inserted into the anatomy. The member is located in the tube and the size is such that an annular space is formed between the tube and the member. The member is formed of a porous material. Preferably, the catheter is shaped such that the fluid entering the proximal end of the tube can flow through the exit hole at a substantially constant rate throughout the inlet.

In a final embodiment, the present invention provides a catheter comprising one elongate tube having a plurality of exit slots in the side wall. The slots extend along the length of the tube, defining the catheter catheter portion. The outlet slots are generally in a direction parallel to the longitudinal axis of the tube. Preferably, the tube is shaped such that the fluid flowing therein can flow through virtually all outlet slots at substantially the same speed. In an optional aspect, the slots increase in length from the proximal end to the distal end of the infusion.

In order to summarize the invention and its advantages over the prior art, certain objects and advantages of the invention have been described above. Of course, not all such objects or advantages are necessarily achieved in accordance with any particular embodiment of the present invention. Thus, for example, one of ordinary skill in the art will appreciate that one or more groups of advantages taught in the present invention may be practiced without necessarily fulfilling the other objects or advantages taught or suggested herein. It will be appreciated that it may be implemented or implemented in a manner that is utilized.

All these embodiments are intended to be within the scope of the invention described herein. These and other embodiments of the invention will be apparent to those skilled in the art from the following detailed description of the preferred embodiments in conjunction with the accompanying drawings. The invention is not limited to the particular preferred embodiment (s) described.

1-4 illustrate an infusion catheter 20 according to one embodiment of the invention. Catheter 20 preferably comprises a flexible support 22 (FIGS. 2-4), a nonporous membrane 24, and a porous membrane 26. Membranes 24 and 26 surround a support 22 to form a plurality of axial lumens between the inner surface of the membrane 24 and the membrane 26 and the surface of the support 22, which are described in greater detail below. The non-porous membrane 24 defines the non-infusion section 28 of the catheter 20 and preferably covers the support 22 from the proximal end of the support to point 30 as shown in FIG. 1. Similarly, the porous membrane 26 defines the injection portion 32 of the catheter 20 and preferably covers from point 30 to the distal end of the support 22. Alternatively, catheter 20 can be formed without nonporous membrane 24. In this embodiment, the porous membrane 26 covers the entire length of the support 22 so that the entire length of the support 22 corresponds to the injection portion of the catheter 20. The injection portion can have any desired length desired. The proximal end of catheter 20 is attached to a feed 34 containing an emulsion 36, such as a liquid therapeutic agent. The distal end of catheter 20 includes a cap 48 (FIG. 4), which defines the end point of the axial lumen within catheter 20.

In use, catheter 20 is inserted into an anatomical system such as the human body to transport fluid medication directly to the wounded area within the anatomical system. In particular, catheter 20 delivers medication throughout the generally linear segment of the wound, corresponding to infusion 32 of catheter 20. Thus, the catheter is preferably inserted so that the infusion 32 is located within the wound site. Using known methods, the surgeon or nurse can insert the catheter 20 with the help of an axial guide wire 46 located within the catheter's axial guide wire lumen 44. Once the catheter is in the desired position, the guide wire 46 is simply pulled through the proximal end of the catheter 20. Alternatively, catheter 20 may be provided without a guide wire or guide wire lumen.

2 and 3 show a preferred form of the support 22. The surface of the support 22 includes an interruption, such as a plurality of ribs 40, as shown in the figure. By configuring the interruption, when the membranes 24 and 26 surround the support 22, the membrane forms part of the walls of several axial lumens 38, and the fluid 38 can flow into this axial lumen. In a preferred form, the plurality of ribs 40 extend radially from the common axial center 42 of the support 22. Rib 40 extends along any length of support 22, preferably along its entire length. For the non-injection 28, as shown in FIG. 2, the non-porous membrane 24 preferably tightly surrounds the outer rim of the rib 40. As a result, an axial lumen 38 is formed between the inner surface of the nonporous membrane 24 and the outer surface of the support 22. Similarly, for injection 32, as shown in FIG. 3, porous membrane 26 preferably tightly surrounds the outer rim of rib 40 so as to be axially oriented between the inner surface of porous membrane 26 and the outer surface 22 of support 22. Allow lumen 38 to form.

In an alternative embodiment of catheter 20, porous membrane 26 can wrap around the entire length of support 20, resulting in replacement for nonporous membrane 24. In this embodiment, the overall length of the support 22 corresponds to the injection section 32. According to another alternative embodiment of the invention, the support 22 only extends in the inlet 32 and a long tube can be provided from the fluid supply 34 to the proximal end of the support 22. In this embodiment, the tube replaces the portion of the support 22 that extends within the non-porous membrane 24 and, in the preferred embodiment, the non-injection 28. In other words, the tube defines the non-injection 28.

In a preferred embodiment, the number of ribs 40 is equal to the number of axial lumens 38. Although two ribs 40 and axial lumens are shown in FIGS. 2 and 3, appropriate titrations may be made, appropriately taking into account the purpose of providing several lumens within the catheter 20 while maintaining flexibility and, if necessary, fluid independence of the lumen. Of rib 40 and lumen 38 can be provided. Here, the words "liquid independence" and "liquid separation" used when describing a plurality of axial lumens simply mean that the lumens are not in fluid communication with each other. Preferably, membranes 24 and 26 are bonded along the outer rim of the ribs using any suitable adhesive, such as a medical grade adhesive or epoxy. This prevents slippage that can occur when membranes 24 and 26 are inserted or removed from the catheter into the anatomy. More preferably the membrane is glued along the entire length of each outer rim of rib 40. As an alternative, the membrane surrounds the support and may not be attached to the support by foreign material. The membrane and the support can be fixed to each other by other means known to those skilled in the art. This maintains latex independence of lumen 38. If desired, an axial guide wire lumen 44 may be provided in the axial center 42 of the support 22. Guide wire lumen 44 is adapted to accept guide wire 46 that can be used to assist in inserting catheter 20 into the anatomy, as described above and as can be readily understood by those skilled in the art.

As shown in FIG. 4, the catheter 20 preferably comprises a tip or cap 48 secured to the distal end of the support 22. The end portion 48 may be integrally formed with the support 22 or adhesively bonded thereto. Preferably, as can be seen, the proximal end of end 48 is circular and has a diameter such that the outer surface of the proximal end of end 48 lines up with the outer rim of rib 40 of support 22. Porous membrane 26 wraps around the proximal end of end 48. Membrane 26 is preferably adhered to distal end 48 such that fluid 36 in lumen 38 does not exit catheter 20 without passing through membrane 26. Tip 48 prevents axial fluid flow through the distal end of catheter 20. However, if desired, tip 48 may optionally be formed of a porous material to allow any axial dosing from the distal end of catheter 20. The distal end of tip 48 is preferably dome-shaped as shown so that catheter 20 can be more easily inserted into the anatomy.

The support 22 can be formed of a variety of materials with due regard to flexibility, light weight, strength, smoothness, and non-reactivity to the anatomical system, ie, safety. Suitable materials for the support 22 include nylon, polyamide, Teflon and other materials known to those skilled in the art. The porous membrane 26 is preferably a sponge or foam material or hollow fiber. Membrane 26 may be formed from a variety of suitable materials, with due regard for purposes that are flexible and nonreactive to anatomical systems. Membrane 26 preferably has porosity resulting in a substantially even distribution of fluid along the surface area of the inlet 32 of the catheter 20, with an average pore size small enough to limit the flow of bacteria through the membrane wall. Suitable materials for membrane 26 are polyethylene, polysulfone, polyether sulfones, polypropylene, polyvinylidene difluoride, polycarbonate, nylon or high density polyethylene. The material is advantageously biocompatible. Porous membrane 26 can filter bacteria from the liquid therapeutic agent as it flows through the membrane 26. It is known that even the smallest bacteria cannot pass pores smaller than 0.23 microns. Thus, the average pore size or pore diameter of porous membrane 26 is less than 0.23 microns to prevent bacteria from passing through membrane 26. The average pore size or pore diameter of membrane 26 is preferably about 0.1 to 1.2 microns, more preferably 0.3 to 1 micron and even more preferably about 0.8 micron.

As described above, the proximal end of the catheter 20 may be connected to the chemical supply 34. Catheter 20 is formed such that each axial lumen 38 is fluidly independent. In other words, the lumen 38 is not in fluid communication with each other. Catheter 20 is connected to a single chemical liquid supply 34 so that fluid 36 can flow within each lumen 38. Alternatively, catheter 20 may be connected to a plurality of separate chemical supply portions so that several different fluids may independently flow within lumen 38. According to this configuration, each lumen 38 is connected to a separate fluid supply so that the total number of other fluids that can be transported to the anatomical system can be the number of lumens 38. Alternatively, the fluid lumen does not need to be fluidly independent. For example, the membrane 26 may not adhere to the support along the entire length of the support 22, with the chemical liquid 36 moving between the lumens 38.

Catheter 20 delivers the fluid directly to the portion of the anatomy adjacent to infusion 32. Latex 36 from latex source 34 is introduced into axial lumen 38 at the proximal end of catheter 20. Latex 36 initially flows into non-injection 28. When fluid 36 reaches injection portion 32, it permeates into porous membrane 26. As more of the fluid 36 enters the infusion 32, the fluid diffuses longitudinally within the wall of the membrane 26 until the entire membrane 26 and the injection 32 are saturated with the fluid. At this time, the fluid 36 begins to pass through the membrane 26, thereby exiting the catheter 20 and entering the anatomy. Furthermore, due to the nature of porous membrane 26, fluid 36 advantageously passes through the entire surface area of porous membrane 26 at a substantially uniform rate. Thus, the fluid is transported at substantially the same rate throughout the generally linear segment of the wound or site of the anatomy. Furthermore, the above advantages are obtained for low and high pressure emulsion transportation.

5 and 6 illustrate a catheter 50 in accordance with an alternative embodiment of the present invention. According to this embodiment, the catheter 50 comprises an elongated outer tube 52 and an inner elongated tubular porous membrane 54. The tubular membrane 54 is preferably concentrically in the outer tube 52. More preferably, the tube 52 tightly surrounds and supports the tubular membrane 54 such that the inner size of the tube 52 and the outer size of the membrane 54 are relatively tight. A plurality of fluid outlet holes 56 are provided in tube 52, preferably over the entire circumference of the tube. The portion of the tube 52, including the exit hole, defines the injection portion of the catheter 50. The tubular membrane 54 only needs to be provided along the length of the infusion but can be longer. Optionally an axial exit hole may be provided in the distal end 58 of the tube 52. In addition, as will be appreciated by those skilled in the art, guidewires and / or guide wire lumens may be provided to assist in the insertion of the catheter 50 into the anatomy.

Tube 52 can be formed from a variety of suitable materials, such as nylon, polyimide, Teflon, and other materials known to those of skill in the art, with due regard to non-responsiveness, flexibility, light weight, strength, smoothness, and safety to the anatomical system. In a preferred form, tube 52 is preferably a 20 gauge catheter tube with an inner diameter and an outer diameter of 0.019 inches and 0.031 inches, respectively. The exit hole 56 of the tube 52 is preferably about 0.015 inch in diameter and provided to be axially identical along the tube 52. The exit hole 56 is preferably positioned such that all holes have an angle of about 120 degrees with respect to the longitudinal axis of the tube 52 from the angular position of the preceding hole. The longitudinal separation between adjacent exit holes 56 is preferably in the range of about 0.125 to 0.25 inches, more preferably about 3/16 inches. In addition, the injection portion can optionally have a desired length. This shape results in uniform transport of the fluid throughout the generally linear segment of the wound site. Of course, the exit holes 56 can be provided in any number of relative arrangements.

The tubular porous membrane 54 is preferably a sponge or foam material or hollow fiber. Tubular membrane 54 may have an average pore size or pore diameter of 0.23 microns or less to filter bacteria. The pore diameter is preferably in the range of 0.1 to 1.2 microns, more preferably 0.3 to 1 micron, even more preferably about 0.8 micron. The tubular membrane 54 may be formed from any suitable material, taking into account the purpose of non-responsiveness to the anatomical system, maintaining flexibility, fitting well within the size limitations of the tube 52, and all within the tube 52 It has a porosity which results in a substantially uniform distribution of the fluid through the exit hole 56. Suitable materials for membrane 54 are polyethylene, polysulfone, polyethersulfone, polypropylene, polyvinylidenedifluoride, polycarbonate, nylon, or high density polyethylene. Preferred inner and outer diameters of the tubular membrane 54 are 0.010 inches and 0.018 inches, respectively. If guidewire 46 is provided, the guidewire can be stainless steel with a diameter of about 0.005 inches. Tube 52 may be secured to membrane 54 by epoxy or other means known to those skilled in the art. As an alternative, the membrane 54 may be in contact with the tube 52 by an interference fit, and may not use other materials to fix the membrane 54 in the tube 52.

In use, catheter 50 supplies fluid to an area of the anatomical system adjacent to the infusion of catheter 50. While the fluid flows into the injection section, the fluid first permeates into the tubular porous membrane 54. As more fluid enters the infusion, the fluid diffuses longitudinally inside the wall of tubular member 54. Once the member 54 and the tubular space therein are saturated, the fluid passes through the member 54 and leaves the catheter 50 by flow through the outlet hole 56 of the tube 52. Furthermore, advantageously, the emulsion will pass through the membrane substantially uniformly throughout the surface area of the member 54, resulting in a substantially uniform flow through substantially all of the exit holes 56. Thus, the fluid is supplied at substantially the same rate throughout the wounded area of the anatomy. Furthermore, the above advantages are obtained for low and high pressure emulsion feeds.

7 illustrates a catheter 70 according to another embodiment of the invention. The catheter 70 includes a tube 72 having a plurality of outlet holes 76 on the sidewalls of the tube and a tubular porous member 74 concentrically surrounding the tube 72. Catheter 70 acts in a similar manner to catheter 50 described above in connection with FIGS. 5 and 6. In use, the liquid therapeutic agent begins to be absorbed into the porous membrane 74 through the exit hole 76. The emulsion diffuses longitudinally inside the membrane walls until the membrane is saturated. Afterwards, the fluid just leaves the wall and enters the anatomy. Advantageously, the emulsion is distributed to the dissection system at a substantially uniform rate throughout the surface area of the membrane 74. As in the previous embodiment, the high pressure and low pressure fluid feeds benefit from this.

8 illustrates a catheter 60 according to another embodiment of the invention. Catheter 60 is more suitable for supplying fluid at relatively high flow rates to regions of the anatomical system. Catheter 60 includes a tube 62 having a plurality of outlet holes 64 of increasing size. In particular, the more distal exit holes have a larger diameter than the more proximal exit holes. The location of the exit hole 64 on the tube 62 defines the length of the inlet of the catheter 60. The injection portion can optionally have a desired length. The proximal end of the catheter 60 is connected to the fluid supply and a guide wire and / or guide wire lumen may also be provided to assist insertion of the catheter 60 into the anatomy.

As described above, for high or low pressure fluid supply, the exit hole closer to the distal end of the catheter tube generally has increased flow resistance compared to the exit hole closer to the proximal end of the tube. In addition, the fluid flowing through the outlet hole on the far end side experiences a greater pressure drop. As a result, the flow rate of the fluid through the hole in the proximal side is usually higher, resulting in uneven fluid transport. In contrast, catheter 60 advantageously provides a substantially uniform fluid supply through substantially all outlet holes 64 under relatively high flow rate conditions. This is because the larger size of the hole at the distal end compensates for increased flow resistance and pressure drop. In other words, because the more distal holes are larger than the more proximal holes, the flow rate through the more distal holes is larger than when they have the same size as the more proximal holes. Advantageously, the exit hole 64 has a gradually increasing size, resulting in a substantially uniform fluid supply. In addition, the exit holes 64 may be sized such that they combine to form a flow-resistant orifice, as described below in connection with the embodiment of FIG. 12.

Compared with prior art catheter, Catheter 60 advantageously has a simple and easy manufacturing process. It is all necessary to drill a plurality of exit holes 64 in the tube 62. Furthermore, catheter 60 can sustain greater bending compared to prior art catheter while maintaining operability. In contrast to prior art catheters such as the Wang catheter, even if the tube 62 is somewhat bent, it will still supply fluid relatively uniformly. This is because tube 62 has a single lumen with a relatively large cross section. If the tube 62 is somewhat curved, the fluid flow in the lumen is less likely to experience a containment condition and subsequent pressure drop that could result in a non-uniform fluid supply.

Tube 62 of the catheter 60 may be formed from any of a variety of materials, with due regard to nonresponsiveness, flexibility, light weight, strength, smoothness and safety to the anatomical system. Suitable materials include nylon, polyimide, teflon and other materials known to those skilled in the art. The infusion can have any length desired, but preferably has a length of 0.5 to 20 inches, more preferably about 10 inches. The diameter of the exit hole 64 preferably ranges from about 0.0002 inches on the proximal side of the inlet to 0.01 inches on the more distal side of the inlet. The largest, ie most distal, exit hole is preferably about 0.25 inches from the distal end of tube 62. In a more preferred form, the axial separation between adjacent exit holes 64 is in the range of about 0.125 to 0.25 inches, more preferably about 3/16 inches. Optionally, the exit hole 64 may be provided with adjacent holes at an angle of about 120 degrees, as in the embodiment of FIG. 5. Of course, if too many exit holes 64 are provided, the tube 62 may be undesirably weakened.

9, 10A and 10B show a catheter 80 according to another embodiment of the invention. The catheter 80 includes a tube 82, "weeping" tubular coil spring 84 and stop86. The proximal end of the spring 84 is attached to the distal end of the tube 82 so that the tube and the spring each define a portion of the central lumen. A dome-shaped stop 86 is preferably attached to the distal end of the spring 84 to close it. The spring portion 84 at the end of the tube 82 constitutes the inlet of the catheter 80. As shown in Fig. 10A, in the non-stretched state, the spring 84 has adjacent coils in contact with the other, preventing fluid from flowing radially out of the lumen within the spring and under the threshold dispension pressure and leaving the lumen. do. The spring 84, as shown in Fig. 10b, has a particular characteristic of extending longitudinally when the fluid pressure is greater than the threshold distribution pressure of the spring, which causes the fluid to whip from the lumen, i.e. radially outwards between the coils. By leaking, it becomes possible to supply. As an alternative, the spring extends radially without stretching, allowing the fluid to whip through the coil of the spring. Furthermore, as will be appreciated by one of ordinary skill in the art, the spring can extend longitudinally and radially to allow the wetting of the fluid. Advantageously, the fluid between the spring coils is distributed substantially uniformly throughout the length and circumference of the spring portion, ie the infusion portion, which is the end of the tube 82. Catheter 80 can be used for fluid supply at high or low flow rates.

In use, the catheter 80 is inserted into the anatomy and the spring 84 is the area where the liquid therapeutic agent is to be supplied. The spring is initially unextended as shown in FIG. 10A. The fluid is introduced into the proximal end of the tube 82 of the catheter 80 and flows through the spring 84 to reach stop 86. As the fluid is continuously introduced proximally of the tube 82, the fluid accumulates inside the spring 84. When the spring 84 is filled with fluid, the fluid pressure increases faster. Latex imparts a radially outward force on the spring coil. As pressure builds up, the outward force is greater. Once the fluid pressure reaches the threshold distribution pressure, the outward force causes the spring coil to disengage slightly, causing the spring to extend longitudinally, as shown in FIG. 10B. Alternatively, as described above, the coil may be radially separated. The fluid then flows through a separate coil and is dispensed from the catheter 80. Furthermore, the distribution is advantageously uniform throughout the infusion portion of the catheter 80. Since the fluid is continuously introduced into the tube 82, the spring 84 remains in an extended state to continuously distribute the fluid to a desired portion of the human body. If the fluid introduction is temporarily stopped, the fluid pressure in the spring 84 may drop below the threshold distribution pressure. In this case, the spring contracts and the coils once again adjoin so that the fluid is no longer dispensed.

Several spring shapes can achieve the object of the present invention. Suitable spring shapes are readily available 316L or 402L. In a preferred form, spring 84 has 200 coils per inch along its length. In this form, the spring can advantageously withstand a high degree of bending without leaking fluid from the inside, and only extreme bending will separate adjacent coils. Therefore, the spring 84 can be bent considerably in the anatomical portion without allowing the fluid to leak, thus dispensing the fluid only in one part of the human body. The spring 84 may have any length required to determine the length of the infusion portion of the catheter 80. The spring can be formed from various materials with due regard to strength, flexibility and safety. Preferred material is stainless steel. In a preferred form, the inner and outer diameters of the spring are about 0.02 inches and 0.03 inches, respectively, and the spring wire has a diameter of about 0.005 inches. The proximal end of the spring 84 is preferably concentrically enclosed within the distal end of the tube 82. The spring may be attached to the inner wall of the tube 82 using, for example, a UV adhesive, potting material, or other adhesive material. As an alternative, the spring can be soldered into the tube 82 or tightly fitted into the proximal plug and tightly fitted into the tube 82.

Tubes 82 and Stop 86 may be formed from any of a variety of materials, with due regard to flexibility, light weight, strength, smoothness, and safety. Suitable materials include nylon, polyimide, teflon and other materials known to those skilled in the art.

11 shows a catheter 90 in accordance with another embodiment of the present invention. The catheter 90 includes a closed tube 92 and a "weaving" tubular coil spring 94 concentrically enclosed within the tube 92 to define the lumen within the tube and the spring. A plurality of exit holes 96 are provided in the side wall of the tube along the length of the tube 92. The length of the tube 92 including the exit hole 96 defines the inlet of the catheter 90. The exit hole 96 is preferably provided over the wall of the inlet. The infusion can have any length desired. In a preferred form, the axial spacing between adjacent holes 96 is in the range of about 0.125 to 0.25 inches, more preferably about 3/16 inches. Adjacent holes 96 are preferably located at an angle of about 120 degrees apart. Spring 94 is preferably enclosed within the inlet of the catheter and has a form similar to spring 84 of the embodiment of FIGS. 9, 10A and 10B. The spring 94 is preferably longer than the injection portion and all outlet holes 96 are positioned adjacent to the spring 94. In this form, the fluid will not escape the lumen without flow between the spring coils. Preferably a stop is attached to the tube to close the distal end of the tube. As an alternative, tube 92 may have a blocked distal end. Catheter 90 can be used for fluid delivery at high or low flow rates.

In use, the catheter 90 is inserted into the anatomy so that the infusion portion is positioned where the liquid therapeutic agent is desired to be delivered. The fluid enters the proximal end of tube 92 of catheter 90 and flows through a spring 94 to reach the blocked distal end of tube 92. As the fluid is continuously introduced to the proximal end of the tube 92, fluid accumulates in the spring 94. Finally, the spring 94 is filled with the fluid and the fluid pressure is raised causing fluid to leak through the spring coils as described above in connection with the embodiment of FIGS. 9, 10A and 10B. Further, the fluid flows through the spring coil substantially uniformly throughout the length and circumference of the spring 94. The fluid then exits tube 92 by flowing through outlet hole 96 of the inlet. The exit holes are preferably of the same size, allowing the fluid to flow through the exit holes at substantially the same speed, advantageously resulting in a generally uniform distribution of the fluid throughout the required area of the human body. As the fluid is continuously introduced into the catheter 90, the spring 94 remains extended to dispense fluid from the catheter continuously. If the fluid introduction is temporarily stopped, the fluid pressure in the spring 94 may drop below the threshold distribution pressure. In this case, the spring can retract so that the coil is once again adjacent and the fluid is no longer dispensed.

In a preferred embodiment, the spring 94 and the tube 92 are in contact along the entire length of the spring such that the fluid leaking through the spring flows through the hole 96 in the inlet. Preferably one end of the spring 94 is attached to the inner wall of the tube 92 such that the other end of the spring is displaced as the spring is extended. The spring can be attached to tube 92 using, for example, UV adhesive, potting material, or other adhesive material. Alternatively, one end of the spring may solder to the inner wall of the tube 92. Tube 92 can be made from any suitable material. The inner wall of the tube 92 is preferably smooth so that the spring can be freely elongated and retracted.

12 illustrates a catheter 100 according to another embodiment of the invention. The catheter 100 consists of a closed tube 102 having a plurality of exit holes 104 in the inner wall of the tube 102. The portion with the exit hole 104 of the tube 102 defines the inlet of the catheter 100. The exit hole 104 size allows the combined area of the opening to be smaller than the area of the orifice of the catheter or any other flow-limiting cross section. Thus, exit hole 104 is the flow-limiter of catheter 100. In use, the catheter advantageously distributes the fluid through substantially all outlet holes 104. The fluid introduced into the proximal end of tube 102 flows through the tube and reaches the blocked distal end of the tube. At this point, the fluid accumulates in the injection section of the catheter. The fluid does not substantially flow through the exit hole 104 because of the small size of the exit hole 104. Finally, the injection portion of the catheter is filled with fluid. As the fluid is continuously introduced into the proximal end of the tube 102, fluid pressure begins to form. At this point the pressure is high enough to push the fluid through the exit hole 104. Furthermore, the fluid flows through substantially all the exit holes 104.

In this preferred embodiment, the outlet holes are all the same size so that the fluid is dispensed at substantially the same speed through substantially all of the holes. The exit hole 104 is preferably drilled with a laser to achieve a very small pore diameter. The preferred diameter of the exit hole 104 is about 0.0002 inches or about 5 microns. Numerous exit holes 104 are provided in the tube 102. The holes are advantageously supplied throughout the circumference of the injection portion of the catheter 100 to transport the fluid more evenly throughout the anatomy. Preferred axial spacing between adjacent exit holes 104 is in the range of about 0.125 to 0.25 inches, more preferably about 3/16 inches. Catheter 100 can be used for fluid transport at high or low flow rates. Tube 102 is known to those skilled in the art and may be formed from the various materials discussed above.

13 illustrates a catheter 200 in accordance with another embodiment of the present invention. The catheter 200 includes a tube 202 having a plurality of outlet holes 204 in the tube along the inlet of the catheter, as in the embodiment described above. The hole 204 is preferably provided over the circumference of the tube 202. An elongate member 206 made of porous material is surrounded by a tube 202. Preferably, member 206 is generally cylindrical in shape and solid. Preferably member 206 is located within tube 204 such that annular space 208 is formed between the outer surface of member 206 and the inner surface of tube 202. Preferably, member 206 extends backward from distal end 210 of tube 202 to the proximal point of the injection region of the catheter. Alternatively, member 206 may continue only to a portion of the infusion. The member 206 preferably generally shares the center with the tube 202 but can achieve the object of the present invention even in the case of eccentricity. Preferably, member 206 is made of a flexible material to help position the catheter 200 in the patient's body.

In use, the liquid therapeutic agent that flows into the tube 202 saturates the porous member 206 and flows into the annular region 208. Once member 206 is saturated, fluid in member 206 flows to region 208 and out of catheter 200 through outlet hole 204. Advantageously, since the fluid pressure is uniform throughout the annular region 208, the fluid flows substantially uniformly through all the holes 204. The annular region 208 has several advantages. One advantage is that this tends to optimize the uniformity of flow through the exit hole 204. In addition, the member 206 tends to expand when formed from the porous material and saturated with the chemical liquid. In this case, the member 206 is preferably annular to the annular region 208, without pressing the tube 202. This limits the likelihood of the development of high pressure areas on the inner surface of the tube 202, which can cause a non-uniform outlet flow of the therapeutic agent at the wound site. As an alternative, member 206 may expand to contact tube 202 and still achieve the object of the present invention.

Member 206 is preferably formed from a porous material having an average pore size in the range of 0.1-1.50 microns, more preferably of about 0.45 microns. The radial width W of the annular region 208 is preferably in the range of 0 to about 0.005 microns, more preferably about 0.003 microns. Member 206 may be made of a variety of materials with due regard to porosity, flexibility, strength and durability. Preferred material is Mentek.

Member 206 may be secured in tube 202 by the use of an adhesive. In one embodiment, as shown in FIG. 13, the adhesive is applied to the distal end of the member 206 to form a bond to the inner surface of the distal end 202 of the tube. Preferably, the adhesive is applied at or near the proximal end of the infusion of the catheter 200. In addition, the adhesive may be applied to the circumference of the member 206 at any position in the longitudinal direction of the member 206 to form an annular bond with the inner surface of the tube 202. For example, in the embodiment of FIG. 13, annular bond 214 is provided immediately proximal to the infusion of catheter 200. Another form is possible. For example, FIG. 14 shows an embodiment where an adhesive is applied to the distal end of member 206 to make bond 216 and to form a ring-shaped bond 218 in the general center of the infusion. FIG. 15 shows an embodiment of applying an adhesive to the distal end of member 206 to form bond 220. FIG. 16 shows the application of adhesive only at the center of the infusion to form ring-shaped bond 222. Those skilled in the art will understand from the disclosure herein that the adhesive can be applied in various forms. Thus, for example, the adhesive at the distal end of the catheter (ie 212, 216 and 220 in FIGS. 13, 14 and 15) is not necessary.

The present best form of the invention is preferably one in which two bonds are included, one in the most proximal pores and one in the most proximal pores. Each bond is made of an adhesive as described below.

The annular bond 214 can be formed by pouring the liquid adhesive through one of the exit holes 204 when the member 206 is in the tube 202. The adhesive is generally high viscosity and tends to flow along the circumference rather than to the body of the member. The adhesive thus forms a ring-shaped bond with the tube 202, which will be understood by those skilled in the art. The adhesive also fills the exit hole 204 in which it is poured. Various adhesives are acceptable, but the preferred adhesive is Loctite.

As mentioned above, the member 206 preferably shares a center with the tube 202. FIG. 17 shows a cross section of the catheter 200 with the member 206 concentrically enclosed within the tube 202. Alternatively, as shown in FIG. 18, member 206 may be positioned adjacent to tube 202. The form of FIG. 18 is easier to make than that of FIG. 17 since the member 206 does not need to be centered within the tube 202.

One of ordinary skill in the art will understand from the disclosure herein that member 206 may be of any length desired and may extend along any desired length of the infusion portion of the catheter. For example, member 206 need not extend to the distal end of tube 202. Furthermore, the proximal end of member 206 may be distal or proximal to the proximal end of the infusion portion.

If any catheter of this embodiment is used, the catheter first has air inside the catheter tube. For example, the catheter 200 shown in FIG. 13 may have air inside the porous material of member 206. Introduction of the catheter's liquid therapeutic agent causes air to flow out of the exit hole. But this takes several hours. If the catheter is inserted into the patient with air and the liquid medication is introduced into the catheter, the wound site of the patient receives little medication until the air is removed from the catheter tube. Therefore, it is desirable to have a liquid therapeutic agent flow through the catheter prior to inserting the catheter into the patient to ensure that air is removed from the catheter before the catheter is used. Furthermore, as shown in FIG. 19, an air filter 224 having a tubular proximal injection portion 226 of the catheter 200 as known may be inserted into the catheter. Filter 224 prevents undesirable air from entering the inlet of the catheter 200.

 20 and 21 illustrate a catheter with elongated exit holes or slots. The catheter can be used in place of the catheter shown and described above. 20 shows tube 230 with longitudinally long exit holes or slots in tube 230. Slot 232 is provided along the inlet of the catheter, preferably throughout the circumference of tube 230. Compared to the small exit hole, the elongated slot 232 tends to reduce the flow impedance experienced by the fluid, thereby increasing the flow rate of the fluid leaving the catheter. Preferably the slot 232 can be oriented longitudinally on the catheter body so as not to compromise the structural integrity of the catheter 200, which can be readily understood by those skilled in the art.

FIG. 21 shows tube 234 with outlet holes or slots 236 increasing in length along the length of the tube in the distal direction. In the illustrated embodiment, the closer to the proximal end of the infusion of the tube 234, the shorter the length than the slot close to the distal end of the infusion. As shown in the embodiment of FIG. 8, catheter tube 234 advantageously provides a substantially uniform fluid supply through substantially all outlet slots 236 under relatively high flow rate conditions. This is because the more distal slots compensate for the flow resistance and pressure drop that the larger size increases. In other words, because the more distal slot is larger than the proximal slot, the flow rate through the more distal slot is greater than if it were the same size as the proximal slot. Advantageously, slot 236 is provided in progressively increasing length, which results in a substantially uniform fluid supply. Furthermore, long slots generally result in higher escape flow rates as shown in the embodiment of FIG. 20.

In this embodiment of the catheter, an independent guide wire lumen may be provided within or adjacent to the disclosed lumen, as will be appreciated by those skilled in the art.

The catheter of the present invention can be used for various medical purposes. With reference to FIG. 22, in an exemplary application, catheter 20 (reference numeral 20 is used to distinguish the catheter, any of the catheter described above may be used) is inserted into the blood coagulation 240 inside the vein or artery 242. do. Preferably the infusion portion of the catheter is in coagulation 240. Preferably the liquid therapeutic agent is introduced into the proximal end of the catheter tube. Advantageously, the medicament of catheter 20 exits the entire infusion at the same flow rate to dissolve blood coagulation 240.

As will be readily appreciated by those skilled in the art, any catheter embodiments described herein can be used in a variety of applications, which include peripheral nerve block, intrethecal infusion, epidermal injection, and endovascular injection ( intravascular infusion), intravenous and intraarticular injections, as well as pain in wounds.

In addition, all catheters disclosed herein may be integral with the fluid line from the infusion pump as opposed to being an independent catheter designed to be connected to or attached to the infusion pump.

While the present invention has been disclosed in the context of certain preferred embodiments and examples, those skilled in the art will appreciate that other alternative embodiments and / or use of the present invention and obvious improvements and their equivalents may depart from the superficially disclosed embodiments of the present invention. You can understand until it comes to.

Thus, the boundaries of the invention disclosed herein are not limited to the particular embodiments described above, but should be defined by interpreting the claims that follow.

Claims (33)

A catheter comprising an elongated tube and an elongated member, The tube has a closed distal end and an exit hole formed in its sidewall and is sized to be inserted into an anatomical region, the exit hole being provided along the length of the tube to inject a catheter To form an infusion section; And, The elongate member is located in the tube and is sized to form an annular space between the tube and is made of a porous material. At this time, the fluid introduced into the proximal end of the tube is configured to flow through the outlet hole at a constant speed throughout the injection portion, Catheter for the constant delivery of fluid throughout the anatomy. The method of claim 1, The member is characterized in that the central axis and the tube is the same Catheter. The method of claim 1, The member is secured to the tube by an annular bond near the proximal end of the injection section. Catheter. The method of claim 1, The porous material is characterized in that it has an average pore size in the range of 0.1 to 50 microns Catheter. The method of claim 1, The annular space has a radial width in the range of 0.001 to 0.005 microns. Catheter. In a catheter comprising a tubular member, The tubular member is made of a porous membrane and has a size that can be inserted into the anatomical portion, wherein the porous membrane has a constant velocity along the length of the member through the sidewall of the tubular member through which the fluid flowing under pressure into the open end of the tubular member is pressed. Characterized in that flowing to, Catheter for the constant delivery of fluid throughout the anatomy. The method of claim 6, The porous membrane is made of any one of the group consisting of polyethylene, polysulfone, polyethersulfone, polypropylene, polyvinylidene difluoride, polycarbonate, nylon, or high density polyethylene Catheter. The method of claim 6, The porous membrane is characterized in that it has an average pore diameter of 0.1 to 0.23 microns Catheter. The method of claim 6, And further comprising a support forming a lumen and having a flow of fluid exposed to said porous membrane. Catheter. A catheter comprising a support and a porous membrane, The support is composed of a first material; And, The porous membrane consists of a second material having a unique property that allows fluid to flow through the membrane, the membrane surrounding the support, In this case, the support is characterized in that the porous membrane is in contact with the support, the lumen is formed between the support and the membrane, Catheter for the constant delivery of fluid throughout the anatomy. The method of claim 10, The porous membrane is configured such that the fluid flowing in the lumen flows through the portion of the membrane throughout the surface of the portion of the membrane at a constant rate Catheter. The method of claim 10, The surface of the support comprises an interruption so that when the porous membrane is surrounded around the support, the porous membrane forms part of the wall of the lumen. Catheter. The method of claim 12, The obstacle includes a rib that extends radially from the axial center of the support, the rib also extends longitudinally along the length of the support, the porous membrane surrounding the outer rim of the rib. Characterized by Catheter. The method of claim 10, Further comprising a nonporous membrane surrounding a portion of the support adjacent to the portion of the support surrounding the porous membrane and forming a portion of the lumen wall. Catheter. The method of claim 10, The first lumen is separated from the second lumen and the first emulsion flowing through the first lumen and the second emulsion flowing through the second lumen are separated from each other as long as they exist in the catheter. Catheter. The method of claim 15, Each lumen is separated from each other and the first fluid flowing through one lumen and the second fluid flowing through another lumen remain separated from each other as long as they exist in the catheter. Catheter. The method of claim 13, The porous membrane is fixed to an outer rim of the rib Catheter. The method of claim 10, The average pore diameter of the porous membrane is characterized in that 0.1 to 0.23 microns Catheter. A method of producing a catheter for consistently delivering fluid throughout an anatomical site, comprising the following steps: Forming an elongated support; When the sheet is wrapped around the support, configuring the support such that a lumen is formed between the support and the sheet; And, Surrounding the porous membrane around the support such that at least one lumen is formed between the support and the membrane. The method of claim 19, Configuring the porous membrane such that the fluid flowing in the lumen flows through the portion of the membrane over a portion of the surface of the portion of the membrane at a constant rate Way. The method of claim 19, Constructing the support includes providing an obstacle within the surface of the support, such that when the porous film is wrapped around the support, the film forms part of the wall of the lumen. Way. The method of claim 21, The obstacle includes a rib extending radially from the central portion of the support, the rib also extends longitudinally along the length of the support, and the porous membrane surrounds the outer rim of the rib. And further comprising configuring the obstacle. Way. The method of claim 22, And fixing the porous membrane to the outer edge of the rib. Way. A tube including an exit hole along a length; And, A tubular porous membrane concentrically enclosed within the tube, the tubular porous membrane forming a lumen with the tube; Catheter for the constant delivery of fluid throughout the anatomy. The method of claim 24, The tubular porous membrane is characterized in that the fluid flowing through the lumen flows through the wall of the membrane over the surface of the membrane at a constant rate. Catheter. The method of claim 24, The lumen is configured such that the fluid flowing in the lumen passes through the wall of the tubular membrane and leaves the tube by a constant velocity flow through all the exit holes. Catheter. The method of claim 24, The tube surrounds the tubular membrane Catheter. The method of claim 24, The average pore diameter of the tubular membrane is characterized in that 0.1 to 0.23 microns Catheter. A method for producing a catheter for consistently delivering fluid throughout an anatomical site, comprising the following steps: Forming a tube; Providing an outlet hole along the length of the tube; Forming a tubular porous membrane; And, Concentrically surrounding the tubular porous membrane within the tube to form the lumen with the tube. The method of claim 29, And configuring the tubular porous membrane such that the fluid flowing through the lumen flows through the wall of the membrane over the surface of the membrane at a constant rate. Way. The method of claim 29, And configuring said lumen such that fluid flowing in said lumen passes through the wall of said tubular membrane and leaves said tube by a constant velocity flow through all said exit holes. Way The method of claim 29, Further comprising constructing the tube and tubular membrane such that the tube surrounds the membrane. Way. The method of claim 29, The tubular membrane is characterized in that it has an average pore diameter of 0.1 to 0.23 microns. Way.

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