Patent Publication Number: US-2018028741-A1

Title: Recovery Catheter Assembly and Method

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application is a continuation application of U.S. application Ser. No. 13/899,366, filed May 21, 2013, which claims priority benefit under 35 U.S.C. § 119(e) to U.S. Provisional Patent Application No. 61/688,775, filed May 21, 2012, and entitled “Recovery Catheter Assembly and Method”. The disclosures of the aforementioned patent applications U.S. application Ser. No. 13/899,366 and U.S. provisional application No. 61/688,775 are hereby incorporated by reference. 
    
    
     BACKGROUND 
     Field of the Invention 
     The present invention relates to systems and methods of local organ perfusion of tumors or other serious conditions with one or more high dose treatment substances, isolating the venous outflow, collecting it, filtering it, and returning it to the body after removing the high dose treatment substance(s). 
     Background Art 
     There are several methods of treating cancerous tumors including surgery, chemotherapy, focal ablation by delivery of various forms of energy, radiation, amongst others. Often, tumors are not resectable by surgery because they have spread into the surrounding tissues or to distant tissues such as the liver, lung, or brain. The treatment of metastatic disease to these organs is done with chemotherapy, focal surgical resection and focal ablation when there are only a few lesions, and occasionally with radiation. Oftentimes, the metastatic disease is diffuse and not amenable to surgery, radiation or focal ablation. This leaves chemotherapy as the only alternative, and the effectiveness of the chemotherapy is limited by the systemic toxicities cause by the drug including bone marrow suppression, neutropenia, nausea, diarrhea, anorexia, wasting, cachexia, bacterial or viral overgrowth amongst others. 
     A system, process, and method of isolated perfusion of organs with a very high dose of a chemotherapeutic agent, collection of the effluent venous blood from that organ before it enters the systemic circulation, filtering the chemotherapeutic agent from the collected blood, and returning the filtered blood without the chemotherapeutic agent to the systemic circulation has been described by Glickman in U.S. Pat. Nos. 5,817,046, 5,893,841, 5,897,533, 5,919,163, and 7,022,097 and by Bodden in U.S. Pat. No. 5,069,662 and which are incorporated herein by reference. This system is referred to as the Percutaneous Hepatic Perfusion (PHP) apparatus for the purpose of treating metastatic disease and primary tumors of the liver. In essence, a very high dose of a chemotherapeutic agent is infused into the hepatic artery over a period of time, usually from 30 minutes to an hour. The high dose chemotherapeutic agent perfuses the liver and is much more effective than a traditional systemic dose administered intravenously. This drug is taken up by the tumor and the remainder flows into the hepatic veins, which are a series of veins that drain from the liver into the upper inferior vena cava (IVC.) This blood which still contains toxic levels of the chemotherapeutic agent is collected by an isolation device which is part of this special apparatus (PHP). The hepatic venous blood isolation device is a double balloon system that is deployed in the inferior vena cava, the balloons being inflated above and below the hepatic veins, the hepatic venous effluent collected into a catheter and pumped through a filter outside the body that removes the chemotherapeutic agent, and returned to the superior vena cava via another catheter. A through return lumen, also referred to as a return channel, is provided to allow blood in the inferior vena cava from the lower body and kidneys to flow back to the heart while the balloons are occluding the vena cava. 
     While the current prior art apparatus is effective in treating the tumor or tumors of the liver, it is somewhat cumbersome to use, as the double balloons may occlude the renal and/or adrenal veins, and the balloons tend to occupy more space in the inferior vena cava than is desirable. Moreover, the through lumen that transmits blood from the lower inferior vena cava to the heart is not large enough to accommodate the volume of blood returning to the heart. This frequently results in a sudden drop in the patient&#39;s blood pressure, and occasionally a shock like condition. Since it is expected that the patient will need at least some level of resuscitation, an anesthesiologist is in attendance to deal with these problems. Obviously, the risk to the patient and the cost of the procedure increases dramatically because these problems with the prior art technology. This is significant, not only from the risk to the patient, but also because it may prevent interventionalists from pursuing this strategy of treatment for their patients and their referring physicians. There is the risk that these problems with the prior art device and technology may prevent this very effective system of therapy from being fully adopted by the medical community, thereby depriving thousands of patients who would have benefited from the therapy otherwise. There are significant problems that can result from these iatrogenically created complications such as renal and adrenal vein thrombosis, unstable perfusion of the heart, brain, and kidneys, resulting in heart attack, stroke, kidney damage amongst other complications, in a patient who is already compromised because of the underlying malignancy. These complications are the result of the use of the primitive balloon technology and method of occluding, altering, or re-directing blood flow in the human body. 
     The balloons of the prior art device limit the size of the through lumen as the expanded balloons must occupy most of the inferior vena cava to effectively isolate the hepatic veins. This limits the amount of blood that can be returned from the inferior vena cava to the right atrium, resulting in the problems noted in the above paragraph. The footprint of the expanded balloons, especially the caudal balloon, in the inferior vena cava is problematic as the distance between the more caudal hepatic veins and the renal/adrenal veins is frequently less than the footprint of the expanded balloon. 
     In reviewing a series of over 50 CT scans of the abdomen, the inventor has determined from measurements of the cavoatrial junction to the orifice of the left renal vein that the current prior art device of Glickman is likely to partially occlude the left renal vein in greater than ⅓ of the cases. If a 15 mm compensating factor is utilized for curvature and other measurement inaccuracies, then there would likely still be greater than 20% of cases in which the left renal vein would be at least partially covered by the caudal balloon of the current device. 
     Also, different diameter devices may be needed as measurement of the anteroposterior (AP) and transverse dimensions of the IVC revealed a great variation in those measurements. Average AP and transverse dimensions in the upper IVC, mid retrohepatic IVC and immediate supra renal vein IVC were 23.6 mm and 30.4 mm, 20.0 mm and 22.7 mm, and 20.2 mm and 28.3 mm, respectively. A minimal AP dimension of only 8 mm was present in one subject while a maximum AP dimension of 36 mm occurred in another subject. Transverse dimensions varied from 10.2 mm to 40 mm in different subjects. The measurements taken may not apply to populations of different ethnicity and may vary even more in those different populations and age groups. Moreover, within the same patient, the IVC measurements many times revealed a large oblong supradiaphragmatic IVC, a smaller more rounded mid retrohepatic IVC, and a tilted, oblong configuration of the IVC just above the renal veins. In fact, the tilted oblong configuration just above the renal veins was frequently tilted in the opposite direction from the tilted oblong configuration of the supradiaphragmatic IVC. 
     SUMMARY 
     Examples of the present invention will successfully and effectively collect the hepatic venous effluent, isolating it from the systemic circulation without the problems caused by the current double balloon system. According to some examples, isolation will occur without blockage of adrenal or renal veins while providing a large channel for blood to flow unimpeded from the inferior vena cava to the heart without the use of balloons. 
     A first example of recovery catheter assembly comprises an actuator element and a mechanically radially expandable and contractible recovery device operably connected to the actuator element. The recovery device has proximal and distal ends and comprises proximal and distal blocking portions at the proximal and distal ends thereof. The recovery device also has a central portion between the proximal and distal blocking portions. The recovery device is at least partially placeable in a first, radially collapsed configuration and in a second, radially expanded configuration by manipulation of the actuator element. When in the second, radially expanded configuration, the proximal and distal blocking portions have radial dimensions greater than the radial dimension of the central portion thereby at least partially defining a collection chamber at the central portion. In some examples the recovery device is fully placeable in the first, radially collapsed configuration and in the second, radially expanded configuration by manipulation of the actuator element. In some examples the recovery device comprises proximal and distal toroidal blocking balloons at the proximal and distal ends of the recovery device. Some examples include a hollow recovery catheter having a sidewall and defining a recovery lumen. Some examples may further comprise a lateral passageway extending through the central portion of the recovery device and the sidewall of the recovery catheter, the parts of the proximal and distal blocking portions and the central portion at least partially defining the collection chamber being liquid impervious with the exception of the passageway, whereby liquid in the collection chamber can pass through the passageway and into and through the recovery lumen. In some examples the recovery catheter comprises proximal, intermediate and distal portions, the lateral passageway is located along the intermediate portion of the recovery catheter, a blood pump is located along the distal portion of the recovery catheter, and a filter element is located along the distal portion of the recovery catheter for filtering out at least one agent from fluid flow through the recovery catheter lumen. In some examples a first pressure sensor is at the collection chamber, a second pressure sensor is positioned distal of the recovery device, a filter element and a pump are operably coupled to the recovery catheter to pump fluid through the recovery catheter and filter fluid passing through the recovery catheter, and the pump is operably coupled to the first and second pressure sensors to permit control of the pressure within the collection chamber during use. In some examples a filter element and a pump are operably coupled to the recovery catheter to pump fluid through the recovery catheter and filter fluid passing through the recovery catheter, a pressure sensor is located proximal to the pump, and the pump is operably coupled to the pressure sensor to permit control of the pressure within the collection chamber during use. In some examples the actuator element comprises first and second actuator elements, the recovery device comprises a proximal end operably connected to the first actuator element and a distal end operably connected to the second actuator element; the recovery device is at least partially placeable in the first, radially collapsed configuration and in the second, radially expanded configuration by manipulation of the first and second actuator elements. 
     A second example of a recovery catheter assembly, for use within a body passageway at an ostium, includes an outer, actuator sheath having a distal portion and an inner, hollow recovery catheter having a sidewall. The recovery catheter defines a recovery lumen and has a distal end. The recovery catheter is housed within the actuator sheath. An actuator wire extends along the recovery catheter and has a tip positioned distal of the distal end of the recovery catheter. A mechanically radially expandable and contractible recovery device has a proximal end secured to the distal portion of the actuator sheath by a proximal extension element and a distal end secured to the tip of the actuator wire by a distal extension element. The recovery device comprises proximal and distal blocking portions at the proximal and distal ends thereof, a central portion between the proximal and distal blocking portions, and a return lumen extending between the proximal and distal ends thereof. The recovery device is placeable in a first, radially collapsed configuration when the actuator wire is pushed distally to a distal actuator wire position relative to the recovery device and the actuator sheath is pulled proximally to a proximal actuator sheath position relative to the recovery device. The recovery device is placeable in a second, radially expanded configuration when the actuator wire is pulled proximally to a proximal actuator wire position relative to the recovery device and the actuator sheath is pushed distally to a distal actuator sheath position relative to the recovery device. When in the second, radially expanded configuration, the proximal and distal blocking portions have radial dimensions greater than the radial dimension of the central portion thereby defining a collection chamber at the central portion, and the proximal and distal expansion elements have open regions to permit fluid flow through the return lumen of the recovery device. A lateral passageway extends through the central portion of the recovery device and the sidewall of the recovery catheter. The parts of the proximal and distal blocking portions and the central portion defining the collection chamber are liquid impervious with the exception of the passageway, whereby liquid from an ostium of a liquid transporting vessel opening into the collection chamber can pass through the passageway and into and through the recovery lumen. 
     A third example of a recovery catheter assembly, for use within a body passageway at an ostium, comprises an outer, actuator sheath having a distal portion and an inner, hollow recovery catheter having a sidewall. The recovery catheter defines a recovery lumen and a distal end. The recovery catheter is housed within the actuator sheath. The recovery catheter has an actuator wire extending along the recovery catheter and a tip positioned distal of the distal end of the recovery catheter. A mechanically radially expandable and contractible recovery device has a proximal end secured to the distal portion of the actuator sheath by a proximal extension element and a distal end secured to the tip of the actuator wire by a distal extension element. The recovery device comprises proximal and distal toroidal blocking balloons at the proximal and distal ends thereof, a central portion between the proximal and distal blocking portions, and a return lumen extending between the proximal and distal ends. The recovery device is placeable in a first, radially collapsed configuration when (1) the blocking balloons are in deflated states, and (2) the actuator wire is pushed distally to a distal actuator wire position relative to the recovery device and the actuator sheath is pulled proximally to a proximal actuator sheath position relative to the recovery device. The recovery device is placeable in a second, radially expanded configuration when (1) the blocking balloons are in inflated states, and (2) the actuator wire is pulled proximally to a proximal actuator wire position relative to the recovery device and the actuator sheath is pushed distally to a distal actuator sheath position relative to the recovery device. When in the second, radially expanded configuration (1) the proximal and distal blocking balloons have radial dimensions greater than the radial dimension of the central portion thereby defining a collection chamber at the central portion, and (2) the proximal and distal expansion elements have open regions to permit fluid flow through the return lumen of the recovery device. A lateral passageway extends through the central portion of the recovery device and the sidewall of the recovery catheter. The parts of the proximal and distal blocking portions and the central portion defining the collection chamber are liquid impervious with the exception of the passageway. Whereby liquid from an ostium of a liquid transporting vessel opening into the collection chamber can pass through the passageway and into and through the recovery lumen. 
     A fourth example of a recovery catheter assembly, for use within a body passageway at an ostium, comprises an outer, actuator sheath having a distal portion and an inner member connected to a scaffolding which may be mesh braid. The mesh braid is placed adjacent to a recovery lumen but is attached at the distal end of the recovery lumen extrusion. Sliding the actuator sheath over the inner member of the expansile scaffolding will cause the scaffolding to expand and collapse. The recovery catheter also comprises a recovery lumen and a distal end. The recovery catheter has an actuator wire extending along the recovery lumen and a tip attached to the distal end of the recovery lumen and recovery catheter. A mechanically radially expandable and contractible scaffold has a proximal end moveably secured to the recovery lumen extrusion In some embodiments, the recovery device comprises proximal and distal toroidal blocking balloons at the proximal and distal ends thereof, a central portion between the proximal and distal blocking portions, and a return lumen extending between the proximal and distal ends. The balloons are operated independently of the expansile scaffolding. The expansile scaffolding holds the return lumen open when the balloons are expanded, preventing collapse of the return lumen by the pressure of the two balloons. 
     In some embodiments, described herein is a recovery device assembly comprising: a proximal and a distal toroidal balloon blocking elements partially defining a collection chamber, a central tubular section between and encircled by the two blocking elements and attached to their inner balloon walls, a recovery lumen housed within the balloons and tubular section with fenestrations through the wall of the wall of the recovery lumen and the central tubular section communicating with the collection chamber, an expansile structure adjacent to the recovery lumen, the expansile structure also housed within the balloons and central tubular section, actuator elements attached to the expansile structure, wherein the recovery device at least partially placeable in a first, radially collapsed configuration and in a second, radially expanded configuration by manipulation of the the actuator elements and inflation of the balloons so that when in the second, radially expanded configuration the proximal and distal blocking elements have radial dimensions greater than the radial dimension of the central tubular section and the radial dimension of the central tubular section is greater than in the first, radially collapsed configuration. 
     In some embodiments, the central tubular section is expanded and collapsed independently of the inflation or deflation of the toroidal balloons. 
     In some embodiments, the toridal balloons are expanded and collapsed independently of the expansile structure. In some embodiments, the expansile structure is not fixably attached to the central tubular section. In some embodiments, the expansile structure is not fixably attached to the blocking elements. 
     In some embodiments, described herein is a method of recovering blood from an organ comprising inserting a radially collapsed recovery device comprising: proximal and distal toroidal balloon blocking elements partially defining a collection chamber, a central tubular section between and encircled by the blocking elements and attached to their inner balloon walls, a recovery lumen housed within the balloons and tubular section, an expansile structure adjacent to the recovery lumen, the expansile structure also housed within the balloons and central tubular section, actuator elements attached to the expansile structure, and expanding the central tubular section by manipulation of actuator elements to provide a non-compressible bypass lumen for the flow of blood, then inflating the two blocking elements to create a collection chamber and aspirating blood from the collection chamber through fenestrations in the recovery lumen and into the recovery lumen. 
     An example of a method for directing a fluid, which passes through an ostium into a body passageway, to a fluid recovery device is carried out as follows. A radially expandable and contractible recovery device is positioned within a body passageway at an ostium with the recovery device in a first, radially collapsed configuration, the recovery device having a proximal end and a distal end. The recovery device is placed in a second, radially expanded configuration, the placing step carried out at least in part by the mechanical manipulation of at least one mechanical actuator element thereby mechanically expanding the proximal and distal blocking portions so that when the recovery device is in the second, radially expanded configuration. The proximal and distal blocking portions have radial dimensions greater than the radial dimension of the central portion thereby at least partially defining a collection chamber at the central portion. Fluid from the collection chamber is directed into the recovery device. In some examples the radially expanded configuration placing step is carried out using first and second mechanical actuator elements operably coupled to proximal and distal ends of the recovery device. In some examples the radially expanded configuration placing step is carried out completely by the mechanical manipulation of the at least one actuator element. In some examples the radially expanded configuration placing step further comprises inflating proximal and distal toroidal blocking balloons at the proximal and distal ends of the recovery device. 
     An example of a method for recovering venous effluent from an organ, the organ having a distal vein and a draining vein, is carried out as follows. A funnel device of a recovery catheter assembly is placed within a tubular body vessel at a venous ostium of an organ being treated, the funnel device having an open end. The open end of the funnel device is placed within the distal vein of the organ at the ostium. The funnel device is forced against the venous wall to create a seal between the funnel device and the draining vein thereby creating a collection chamber defined between the funnel device and the organ. An agent is infused into the patient. Fluid from the organ is collected in the collection chamber. The collected fluid is filtered. The filtered collected fluid is returned to the patient. 
     An example of a method for determining the effectiveness of a seal at a collection chamber created between a recovery device of a recovery catheter assembly and an organ from which fluid is collected is carried out as follows. An indicator agent and a therapeutic agent are infused into a patient. A fluid, which passes through an ostium of an organ into a body passageway, is collected in a collection chamber defined between a fluid recovery device of a recovery catheter assembly and the organ. The collected fluid is processed. The processing step comprises removing the indicator agent and the therapeutic agent from the collected fluid. The processed fluid is returned to the patient. Systemic fluid is collected from the patient. The collected systemic fluid is tested for the presence of the indicator agent. 
     An example of a method for removing a therapeutic agent from a patient is carried out as follows. A therapeutic is infused agent into a patient. A fluid passing from an organ is collected. A binding material comprising an affinity agent is added into the collected fluid. The therapeutic agent within the collected fluid is bound to the affinity agent. The collected fluid and the binding material are processed. The processing step comprises removing the binding material with the therapeutic agent bound thereto from the collected fluid. The processed fluid is returned to the patient. 
     Other features, aspects and advantages of the present invention can be seen on review the figures, the detailed description, and the claims which follow. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  shows a patient being treated with a prior art isolation apparatus. 
         FIG. 2  shows a prior art isolation apparatus with the balloons in deflated states. 
         FIG. 3  shows the prior art apparatus of  FIG. 2  with the balloons in inflated states. 
         FIGS. 4-8  are illustrated examples of recovery catheter assembly including mechanically assisted expansion mechanisms made according to the present invention 
         FIG. 4  shows a first example of a mechanically assisted expansion apparatus made according to the invention. 
         FIG. 4A  shows the structure of  FIG. 4  in a collapsed state. 
         FIG. 4B  is a cross-sectional perspective view of the structure of  FIG. 4 . 
         FIGS. 5A, 5B and 5C  are cross-sectional views taken along lines  5 A- 5 A,  5 B- 5 B and  5 C- 5 C in  FIG. 4 , respectively. 
         FIG. 6  illustrates an alternative to the example of  FIG. 4  including toroidal balloons used in conjunction with the mechanically assisted expansion mechanism. 
         FIG. 7  illustrates a further alternative similar to that of  FIG. 6  using obliqued toroidal balloons. 
         FIG. 8  shows an alternative example similar to that of  FIG. 6  in which the pump and filter are placed in extended section of recovery catheter. 
         FIGS. 9-16  show other examples of recovery catheter assemblies. 
         FIG. 9  shows a recovery device including a funnel catheter. 
         FIGS. 10A and 10B  show the funnel catheter of  FIG. 9  in more detail. 
         FIGS. 11A, 11B and 11C  show a retrievable temporary balloon expandable strut in three different states. 
         FIG. 12  is a cross-sectional view taken along line  7 - 7  of  FIG. 11C . 
         FIG. 13A  shows a funnel catheter. 
         FIG. 13B  shows a retrievable isolation apparatus including an expandable mesh grade structure. 
         FIG. 13C  shows the structure of  FIG. 13B  in use. 
         FIGS. 14, 15 and 16  show additional examples of retrievable isolation apparatus. 
         FIG. 17  is a longitudinal section of another embodiment of the current invention. 
         FIG. 18  is a horizontal section of the embodiment of  FIG. 17 . 
         FIGS. 19 and 20  show longitudinal sections through a tubular length of elastomeric material. 
     
    
    
     DETAILED DESCRIPTION OF THE EXEMPLARY EMBODIMENTS 
     The following description will typically be with reference to specific structural embodiments and methods. It is to be understood that there is no intention to limit the invention to the specifically disclosed embodiments and methods but that the invention may be practiced using other features, elements, methods and embodiments. Preferred embodiments are described to illustrate the present invention, not to limit its scope, which is defined by the claims. Those of ordinary skill in the art will recognize a variety of equivalent variations on the description that follows Like elements in various embodiments are commonly referred to with like reference numerals. 
       FIG. 1  is a representation of a patient  2  being treated with a prior art apparatus. The drug or substance is injected by a syringe  4  or pump (not shown) into the hepatic artery  5  and perfuses the liver  3 . The hepatic venous effluent is collected by the double balloon catheter  9  in the upper inferior vena cava  7  and directed into the connecting tubing  17  to the pump  21 , then to the filter  43  via the connecting tubing  41  between pump  21  and filter  43 , and then the filtered blood is transported back into the patient&#39;s  2  systemic circulation by connecting tubing  44  returning blood to the internal jugular vein. 
       FIG. 2  is a prior art isolation apparatus  139  demonstrating the uninflated balloons  143 ,  144  and the holes  141  in the external catheter  140  through which the hepatic venous effluent flows into an external situated lumen. The return channel or through lumen (not shown) that transmits the inferior vena caval blood to the right atrium is in a central lumen (not shown) which is necessarily smaller than needed as the catheter  142  must contain the recovery lumen for the hepatic venous effluent, inflation channels for the balloons, and the through return lumen for IVC blood to pass to the right atrium. 
       FIG. 3  is the prior art apparatus  139  with the balloons  143  and  144  expanded so that the section of inferior vena cava (not shown) between the balloons  143  and  144  is isolated. The caudal balloon  143  is placed below the most caudal hepatic veins (not shown) and the cephalic balloon  144  is placed near the juncture of the inferior vena cava (not shown) and the right atrium (not shown). Blood flowing out of the hepatic veins into this section of isolated inferior vena cava is collected through the openings  141  in the wall of the catheter into an external lumen and transported via tubing  17 ,  41 ,  44  to the pump  21  and filter  43  and then back into the body  2  as in  FIG. 1 . There is central channel (not shown) that serves as the return through channel to transport the blood from the IVC to the right atrium. Because of the external collection channel of the isolation apparatus, two balloon inflation channels and the walls of these channels, the central return through channel has an inadequate annular space to transport sufficient blood from the IVC to the right atrium. This constriction is necessary because of the design of the prior art device, and, as mentioned above, is problematic. Moreover, one can easily see that the footprint of the expanded balloons  143 ,  144  is so large that other vital veins may easily be inadvertently occluded. The current invention will obviate these problems in one of several configurations described henceforth. 
     Ideally, the device of the present invention should be relatively small for easy insertion, and then expand in the inferior vena cava to function, then contract to a small size again for removal. In fact, while the above descriptions of the different embodiments have discussed the use of materials that are expansile, expansible, self expanding, balloon expansible, self contracting, and so forth, it is the inventor&#39;s conclusion that after the review of the CT scans on 50 patients that the wide variety of size and shapes of the inferior vena cava, the critical length needed to cover the hepatic venous ostia but not occlude the adrenal and renal veins, the need for a small footprint caudally, and the need for an adequate through return lumen places unusual demands on a device which cannot be met by simply applying prior art techniques (self expanding, balloon expandable, etc.) that may have been used elsewhere in the vascular system to a hepatic venous effluent recovery catheter. Hence, one preferred embodiment as discussed below with reference to  FIGS. 4 and 5A-5C , as well as the other embodiments, will function best with a system of mechanically assisted expansion, which utilizes a mechanism proximally (for example outer actuator sheath  73 ) and a mechanism distally (for example actuator rod  154 ) that will provide additional tension on the proximal and distal flares  131 ,  132  to enhance and assist the expansion and contraction of them. While several of the embodiments utilize balloon expansion and one embodiment utilizes a self expanding braid, a presently preferred configuration is one that uses a non balloon, mechanically assisted expansion, such as recovery device  138  of  FIGS. 4 and 5A-5C . 
     The reasons that mechanically assisted expansion will work better than a self expanding design in the inferior vena cava include the following. 
     1. Foreshortening: With self expansion there will be a significant amount of foreshortening upon expansion of the device, and the amount of foreshortening will depend on the size and shape of the IVC. If the diameter of the IVC is small, there will be less foreshortening than if it is large. There is a need to cover all of the hepatic veins (which typically range from 6.5-7 cm top to bottom), but not to occlude adrenal or renal veins. Therefore the length of the device when deployed is critical. One generally does not have control over the length with a self expanding device and this may result in the occlusion of the renal and adrenal veins. Alternatively, one could control the length with a mechanically assisted expansion, as one could adjust the tension on the flares (flares  131 ,  132  discussed below with reference to  FIG. 4 ) to match the anatomy present in the individual patient. Hence, in a patient with a small IVC, one would increase the tension on the flares creating less length than would be present without this added mechanical assistance, adding an element of control not present with a purely self expanding system. This reason alone provides a strong incentive for not using self expanding only designs and using a mechanical assisted expansion design. 
     2. To be effective at all, a self expanding braid must be oversized and the elastomeric membrane applied in the oversized state, less the membrane will cause the braid to contract. When one attempts to remove the self expanding device (typically approximately 45 mm fully distended in oversized state) through a 15 Fr. (5 mm) catheter, one will have to deal with the extra membrane material which will become irregularly folded and clumped when the braid is contracted. This is especially true when removing the distal annular flare as the center portion of the braid is attached to the recovery tubing and not allowed to contract fully by proximal tension on the braid. In other words, one may be able to remove the proximal annular flare and the center portion by traction on the braid, but one should expect difficulty in removing the distal annular flare which has been oversized purposefully with excess membrane material in a self expanding configuration. Mechanically assisted expansion and contraction would obviate this problem. 
     3. A self expanding tubular mesh braid typically exerts less radial force than a laser cut stent (which would be extremely expensive), therefore one may need a mechanical assisted expansion to create a tight seal, i.e., extra radial tension force not present with self expansion, especially considering the many different shapes and angles in the inferior vena cava. In fact, the acute angle present in the immediate suprarenal inferior vena cava that was frequently demonstrated on the CT study mentioned above would cause particular problems for a self expanding device as there would be inadequate seating of the braid because of the acute angle at this location, and hence inadequate sealing of the device. One would need active expansion, i.e., mechanical assistance, to drive the braid with more force than would be possible with a purely self expanding system. 
     4. Tradeoff in wire sizes and number of wires: The device can be made more compact with fewer and smaller wires, but will have less radial force and lesser chance of creating a tight seal if only self expansion is utilized. A compact device can be constructed if there is mechanical assisted expansion to provide for a secure seal. 
     5. As detailed later, the presence of the recovery catheter attached only to the ventral aspect of the braid in  FIG. 4  will tend to cause the recovery catheter to be centered in the vessel when it is actually eccentrically placed. The use of a self expanding mechanism may cause unequal pressures against the IVC wall by the flares, especially given the varying shapes of the IVC, and hence the potential for a less than secure seal. The use of a mechanical assist mechanism would provide for additional annular tension that would overcome this potential problem. 
     6. Another property of tubular braided structures is that there is a critical braid angle that needs to be achieved to provide radial strength. When this critical angle is achieved the braided tube becomes stronger and the inward force required to collapse the braid dramatically increases. This critical angle of the braid is more readily achievable with an active expansion, or mechanically assisted expansion, that would tend to drive the braid to a larger diameter than would be possible with a purely self expanding system. In fact, the critical angle that does give the braided structure its optimal braid angle and hence optimal radial strength may not be achievable at all with a purely self expanding device. Moreover, even if this critical braid angle were achieved with a purely self expanding system, collapsing the braid for retrieval may be even more problematic. 
     7. A self expanding system needs an outer sheath to constrain the device for insertion and retrieval. With an active system to control the expansion and contraction of the device, this outer sheath may not be needed creating an overall smaller size profile than would be achievable with a purely self expanding system. 
     The reasons a mechanically assisted expansion mechanism as described subsequently in  FIGS. 4-8  will work better than a balloon-only expanded mechanism as demonstrated in some of the current embodiments in prior art devices are: 
     1. Obviating the use of the balloon makes the device simpler. 
     2. The balloon-only assisted expansion may not provide the force needed to create a tight seal or control the length when the balloon is deflated to allow IVC blood to return to the heart. 
     3. In some situations balloon expansion mechanism may be used in conjunction with a mechanical assisted expansion, and some of the current embodiments reflect this. 
     Hence, for the reasons listed above, the novel mechanically assisted expansion of the current invention is superior to previously described stand alone techniques and methods such as balloon-alone expansion and self expansion. As used in this application, mechanically assisted expansion is carried out with mechanical expansion structure with or without the use of a balloon to assist expansion in the preferred embodiments. 
     One preferred embodiment of a recovery catheter assembly  136  is shown in  FIGS. 4-4B and 5A-5C , and includes a recovery device  138  using an expandable or expansible and collapsible mesh braid  130  with an elastomeric covering  97 . Although it may be self expanding, self contracting, it is preferably expansible by mechanical expansion structure which will be described subsequently. 
     The recovery device  138  in this configuration has a “dog bone” configuration with the protruding flares  131 ,  132  on each end creating the blocking element that define the extent of the hepatic venous effluent collection chamber  94  (HVECC) covering the ostia  51  of hepatic veins  52 . Braiding techniques, heat treating of the nitinol (or other material from which the braid  130  is made), the attachment of the braid  130  to the recovery catheter  76 , defining a recovery lumen, and possible lay-ins in the braid will determine the shape of the device  138 . The mesh braid  130  of the device  138  is covered with or coated with an elastomeric substance  97  in all but its proximal and distal ends creating a modified cylindrical channel within the tubular mesh braid  130 . The elastomeric covering, typically of a silicone composition or some other biocompatible material that is resistant to degradation by the chemotherapy, or other, agent, may extend proximal to the proximal flare  131  and distal to the distal flare  132 , but would not cover the ends of the device  138 . This will allow a very generous through return channel  124  for blood to flow from the lower IVC lumen  99  into the right atrium (not shown.) 
     The expanding structure  100  may be made of a mesh braid, laser cut materials, or any other generally tubular, radially expandable mechanical structures that can be expanded into a more or less tubular configuration that would allow an adequate through channel for IVC blood to return to the right atrium without much impendence or obstruction. The present invention is also directed to methods of using generally tubular, radially expandable mechanical structure to convey IVC blood from an area near the renal veins to the supradiaphragmatic IVC or the right atrium while collecting hepatic venous effluent, and all devices which would facilitate such a method with or without the extracorporeal filtration system described above and elsewhere. 
     In the preferred embodiments of  FIGS. 4-8 , the expanding structure  100  is expanded by means of a proximal actuator sheath  73  and a distal actuator wire  154  attached to a proximal wire set  146  and to a distal wire set  147  of the mesh braid  130 , respectively. By exerting forward pressure upon the outer actuator sheath  73  with respect to the recovery lumen  76 , the proximal flare  131  will expand to the wall of the inferior vena cava creating a seal and providing expansion of the proximal portion  124  of the through return channel  124  defined between actuator shaft  73  and the elastomeric coated mesh braid  130 . By exerting a pulling pressure on the actuator wire  154 , the distal flare  132  will expand to the wall of the inferior vena cava creating the distal seal and providing the expansion of the distal portion of the through return channel  124 . The hepatic venous effluent collection chamber  94  is created between these two flared ends of the device. In addition to creating collection chamber  94 , the mechanically expanding structure  100  also creates the return channel  124 , discussed in more detail below. 
     The recovery catheter  76  that collects blood and the chemotherapeutic agent from the HVECC  94  and transfers it to the extracorporeal pump (not shown) is bonded to the ventral surface of the coated expandable mesh braid  130 . At least one hole  95 , and preferably several holes  95 , are placed through the braid  130  and material  97  covering the braid and into the lumen  68  of the recovery catheter  76 . See  FIGS. 5A-5C . This allows communication of the lumen  68  of the recovery catheter  76  with the HVECC  94  and the hepatic venous effluent would flow from the HVECC  94  through the holes  95  and into the recovery catheter  76 , and then be transported extracorporeally to be filtered before being returned to the body. 
     The bonding of the catheter to the braided structure is of special concern as this may be a potential point of failure. A simple circumferential bonding (not shown) around the hole through the wall of the braided device  130  and the holes  95  in the recovery catheter  76  may suffice, but it is anticipated that a broad area bonding (not shown) of the surface of the catheter to the braided structure, as well as a focal circumferential bonding, may be needed and would provide an extra degree of safety. Other members (not shown), such as wires, may be utilized to encircle the recovery catheter  76  and engage the coated mesh braid structure  130  to fix the recovery catheter to the mesh braid structure, in addition to the bonding described above. Prevention of leakage of the toxic hepatic venous effluent into the systemic circulation is a high priority. 
     Since the coated braided structure  130  is bonded to the recovery catheter  76  in the more or less mid portion of the braided structure  130 , collapsing of the braid will be more difficult than if it were not bonded, in that the proximal mechanism will not collapse the distal aspect of the braided structure. Therefore, in this particular embodiment, a second collapsing mechanism is supplied in the form of a stiff push/pull rod or actuator wire  154  that occupies a channel  69 , see  FIGS. 5A-5C , within the wall of the recovery catheter  76 . The distal wire set  147  of the braided structure  130  is attached to this rod or wire  154  by crimping, soldering, or by other appropriate means. Retracting the wire  154  will cause the braided structure  130  to expand against the vessel wall  155  and form a seal  156  about the HVECC  94  that will be created. Advancing the wire/rod  154  will cause the braided structure  130  to collapse for insertion and removal. The proximal portion  131  of the braided structure  130  will be expanded and collapsed by the movement of the actuator sheath  73  with respect to the recovery catheter  76 . 
     Of special note is the eccentric nature of the recovery catheter  76  in  FIGS. 4 and 4A . The braid  130  attached proximally to actuator sheath  73  through proximal wire set  146  will tend to center the recovery catheter  76  in the lumen  99  of the blood vessel IVC. Ideally, the recovery catheter  76  needs to remain eccentrically placed with in the lumen  99  of the vessel to maintain as large as possible return channel  124  for the blood to flow unimpeded. The braid may not provide equal pressure against the vessel wall  155  at the flared ends  131 ,  132  because of the eccentricity and this may contribute to unequal sealing of the HVECC  94 . These negative features may be partially overcome by different braiding techniques, heat set techniques, and additional lay-ins for braid  130  amongst other techniques. Additionally, the members of the braid  130 , that is the proximal wire set  146 , attached to actuator sheath  73  would be shorter on the ventral aspect of the device which may help resolve this difficulty somewhat, and the distal wire set  147  of braid  130  is attached to the distal tensioner wire  154  which is indeed centered within the blood vessel lumen  99 . In other words, the attachment of the proximal braid  146  to the actuator sheath  73  in such a manner that forward pressure on the actuator sheath will provide annular radial force to the proximal flare  131  may be essential to providing a tight seal against the wall of the IVC. Without this added pressure, the eccentric nature of the flare  131  may prevent equal or adequate pressure against the IVC wall  155 , especially since the size and shape of the IVC is so varied from patient to patient and even within the same patient. 
     Even another alternative embodiment as shown in  FIG. 6  utilizes a mechanically assisted expansion device as shown in  FIG. 4 , but the mechanically assistance is utilized only to expand the return channel  124 . The HVECC  94  is defined by balloons  180 ,  181 , which may be toroidal balloons, on the proximal and distal ends of the through return channel  124 . The presence of the mechanically assisted expansion apparatus will overcome many of the problems inherent in a self expanding device that are listed herein and allow easier placement and repositioning, easier deployment and, more importantly, easier recovery of the tubular recovery device  138 . The mechanically assisted expansion will also allow more pressure to be exerted radially and prevent collapse of the return channel  124  when the balloons  180 ,  181  are inflated. The balloons, being more flexible than the braided flares  131 ,  132  of other embodiments, will conform to the acute angles within the inferior vena cava better than the braided wire structures and provide for a more consistent and predictable seal. There has been no problem with leakage of the prior art device that is currently in use which utilizes balloons. The balloons function well to contain the hepatic venous effluent. The problem with the prior art device is that the balloons are too large and occlude the renal and adrenal veins in some cases, and that the through return channel is too small to convey a sufficient volume of blood from the kidneys and lower body via the inferior vena cava to the heart. This latter problem causes the patient to go into shock, as well as a myriad of other problems, enumerated previously. Hence, the balloons are not the problem with the currently used prior art device, it is the size of the balloons and the size of the through return lumen that is problematic. These deficiencies are addressed with various embodiments, including those of  FIGS. 6 and 7 . 
     The braided tubular structure is covered with an impermeable and elastic substance  97  that is resistant to chemotherapeutic compounds as the prior embodiments. It is essentially tubular rather than having the flares  131 ,  132  or expanded ends as present in  FIG. 4 . The tubular structure representing the return lumen  124  is attached to an inner, recovery catheter  76  which communicates with the hepatic venous effluent collection chamber (HVECC)  94  via one or more apertures  95 . An outer actuator sheath  73  is slideable relative to the inner recovery catheter  76  to assist with expansion and collapse of the tubular return channel  124 . The braid  130  is attached to this recovery catheter  76  so that tension can be provided to expand the braid, or to assist with the expansion of the braid, by advancing the outer actuator sheath  73  with respect to the inner, recovery catheter  76 , and tension can be provided to collapse the braid, or assist with collapsing the braid more completely, by withdrawing the outer sheath  73  with respect to the inner catheter  76 . 
     A stiff push wire or actuator wire  154  may be attached to the distal wire set  147  to expand or collapse, or assist the expansion or collapse of the tubular braided structure as previously illustrated in  FIG. 4 . Expansion or assistance with expansion is accomplished by withdrawing the wire  154  with respect to the inner, recovery catheter  76 . Collapse or assistance with collapse of the tubular braided through return channel  124  is accomplished by advancing the wire  154  with respect to the inner catheter  76 . The wire  154  preferably is housed within a lumen  69  of the wall of the inner catheter  76  as per  FIGS. 5A, 5B, and 5C . 
     The proximal balloon and the distal balloons are attached to the outer surface of the tubular braided through return lumen and are inflated via inflation lumens  66 ,  67  as pictured in  FIGS. 5A, 5B, and 5C , although the inflation lumens may be positioned differently within the wall of the inner catheter  76  than shown in these illustrations. These two balloons  180 ,  181  are oriented more or less perpendicular to the expandable through return channel  124  and encircle the expandable through return lumen  124  with a toroidal shape. The most cephalic positioned balloon  181  may be larger than the more caudal balloon  180  as it may be advantageous to seat the cephalic end of the device and the cephalic balloon in the right atrium. The portion of the inferior vena cava between the right atrium and the hepatic veins  52  is typically larger than the suprarenal inferior vena cava (as was determined from the CT study performed by the inventor mentioned above), hence the need to provide a larger balloon or other sealing device cephalically. Since both the proximal and distal balloons are oriented more or less perpendicular to the axis of the through return lumen, the footprint is much smaller than the spherical balloon of the current prior art device, and therefore occlusion of the adrenal and renal veins will not be nearly as problematic as with the current prior art device. 
     Alternatively, the elastomeric covering  97  may cover only a portion of the mesh braid as was will be discussed in  FIG. 14 . If this were the case, a balloon structure (not shown) would essentially encircle or surround the HVECC  94  to define it rather than the two toroidal balloons  180 ,  181  of  FIG. 6 . 
     Moreover, the CT study demonstrated that the left renal vein  182  (in  FIG. 7 , which is a view of the device in the IVC from an anterior or coronal perspective) was always positioned more cephalically than the right renal vein  183 . It also demonstrated that accessory hepatic veins  184  enter the IVC either ventrally or on the right side. Hence, it may be advantageous to position the caudal toroidal balloon  180  at an angle as shown in  FIG. 7  so that the HVECC  94  extends more caudally on the right to avoid occluding the accessory hepatic veins  184  and capture the accessory hepatic venous effluent from HVECC  94 , but more cephalically on the left to provide a safety margin against the inadvertent occlusion of the left renal vein  182  which can be positioned at nearly the same axial level as the most caudal accessory hepatic vein  184 . Additionally, the cavoatrial junction is also frequently asymmetrical, and obliqued balloons may be utilized at both ends to better accommodate the unique anatomy present in the proximal and suprarenal IVC. Using an obliqued toroidal balloon  810  in  FIG. 7  overcomes the need for the proximal and distal occlusion mechanisms, whether expandable braid or spherical balloons, to be symmetric when there is in reality a non symmetric anatomy present. 
     The presence of the pump and filter outside of the body is inconvenient and creates additional steps as well. Placing the pump and filter within the recovery catheter and returning the filtered blood to the systemic circulation without transporting it to an extracorporeal location may be accomplished by miniaturizing the pumping and filtering components.  FIG. 8  shows a simplified view of a recovery catheter  76  similar to  FIG. 6  with the filter  43  and the pump  21  present within an extended section of the catheter  76 . This extended section traverses the right atrium  200  and into the superior vena cava  201 . The presence of the pump  21  in close proximity to the hepatic venous effluent collection area  94  has the added benefit of creating a negative pressure region within the hepatic venous effluent collection area  94 , further guarding against any leak into the systemic circulation, as if there is lower pressure in the hepatic venous effluent collection  94  area than in the IVC  99 , there would be no chance of leakage into the higher pressure of the IVC. The pump  21  may be one of three general types of pumps that are able to propel blood, i.e., roller, centrifugal, and axial pumps. Of these types, a centrifugal pump may likely be best suited for this application as they generally cause less hemolysis than the other types, and can be more easily miniaturized. Centrifugal pumps consist of a nonocclusive pump head and various numbers of impeller blades positioned within a valveless pump housing usually powered electromagnetically. Pump rotation generates a vortex resulting in nonpulsatile unidirectional blood flow and high flow rates can be achieved, although the centrifugal pumps can bridge a limited pressure differential. In the intended use within this invention, there is venous to venous flow which does not demand a significant pressure differential. Several companies currently produce centrifugal pumps including Medtronic, Sarns, and St. Jude Medical, amongst others. Pumps developed for neonatal use may be modified for use in the current application. Axial pumps consist of a rotor type impeller housed in a small casing and mechanical action is powered by an electromagnetically powered rotor system. An example is the Impella pump from Impella Cardiotechnik AG, or even the MicroMed DeBakey VAD. The pump  21  only may be placed in the catheter in another embodiment (not shown) with the filter  43  remaining extracorporeal. 
     The filter  43  for the example of  FIG. 8  may be any one of several types including but not limited to electronic, cartridge, membrane, microtubular, microfluidic, magnetic, chemical, activated carbon, positively or negatively charged filter components, and others. The filter element can be produced from any suitable media such as carbon based or synthetic media which can extract a drug from blood by adsorption or binding drug molecules to porous structures, anion exchange, particulate filtration, aggregate filtration and so forth. Filter structures can be hollow fiber membrane, semi permeable membrane, granular media, woven or non woven filter fabrics or other suitable forms. The filter may be expandable (not shown) after it has been inserted especially if the efficiency of the filter is dependent on the surface area of the filter, preferably in the superior vena cava  201  or right atrium  200  allowing the filtered blood to be returned to the superior vena cava  201  or right atrium  201  without being transported extracorporeally. In the case of an activated carbon filter, the absorption efficacy may be different for several different types, i.e., ROX, UKR, CLA, amongst others, of activated carbon as well as shape and surface morphology. The particles may be coated with a polymethyl methacrylate co-polymer, or some other material, at different thicknesses and with different methods to diminish the effect on red blood cells and other blood components. Frequently there may be a trade off between coating thickness and absorption efficiency. Another type of filter that may be used is one that contains porous hollow fibers which may be coated with affinity agents, or the affinity agents may be either within or outside the hollow fibers. The blood can be pumped either through the porous hollow fibers, and the substance to be removed is selectively transported to the space outside the hollow fibers, or conversely, the blood may be pumped through the spaces outside the fibers and the substance to be removed is selectively transported to the interior of the hollow fibers. 
     Another type of blood filter is a microfluidic blood filter. Used with the current device, the chemotherapeutic agent would be infused and collected as previously described in  FIG. 8 , but upon entering the recovery lumen  76  the blood containing the chemotherapeutic agent would be admixed with coated iron oxide beads that are coated with an affinity agent. The chemotherapeutic agent would adhere to the coated beads and be pumped with the blood through to the filter  43  where an electromagnet (not shown) would separate the beads and chemotherapeutic agent from the blood. Given the space restraints of an in-catheter filter, this system has advantages as it may obviate the bulk required by traditional designs. A hybrid filter may also be used which employs one or more of the different filter types within the same device. 
     The filter  43  may be expanded by the pressure of the pump  21 , or by other means. The blood from the hepatic venous effluent chamber  94  would enter the recovery catheter  76  via apertures  95  as in several other embodiments and proceed cephalically in the extended segment of the recovery lumen  76 , through the pump  21  and the filter  43  and exit into the superior vena cava  201  or right atrium  200  through the distal end of the device. A side hole  203  may be provided in the recovery catheter  76  for the exit of the stiff actuator rod  154 . Alternatively the actuator rod  154  may be attached to a separate actuator sleeve (not shown) located exterior to the recovery catheter  76  that is attached to the tubular braid in this location and would be slideable relative to the recovery catheter  76 , so that retraction of the actuator rod  154  would move the separate actuator sleeve (not shown) to expand the braid and advancement of the actuator rod  154  would move the separate actuator sleeve (not shown) to collapse the braid. 
     Even another embodiment (not shown) utilizes a self expanding return channel  124 , and toroidal shaped balloons  180 ,  181  as in  FIG. 6 , but without the active expansion system as in  FIGS. 6 and 7 . While the active mechanical expansion assistance provides a control not found in purely self expanding systems, the expansion assistance provided by inflating the balloons combined with a self expanding mechanism of the through return lumen may provide enough radial strength to maintain patency of the through return lumen in this embodiment. The sealing function will be provided by the balloons, hence some of the objectionable qualities of a self expanding system listed previously are not as pertinent if the self expanding component is just the through return lumen as is the case in this particular embodiment. The function and components of this embodiment are otherwise essentially the same as in  FIGS. 6 and 7 . 
     Other Recovery Catheter Assemblies 
       FIG. 9  shows another example of a recovery catheter assembly  136  including a recovery device  138 . Recovery device  138  includes a funnel catheter  50  that covers the ostia  51  of the hepatic veins  52 , isolates the hepatic venous effluent and retrieves the hepatic venous blood into the catheter  53  or tubing to be pumped into the filter  43  and returned to the body as in  FIG. 1 . The funnel catheter  50  is held in place by a temporary retrievable balloon expandable strut  54  provided on a separate venous catheter  55  securing it over the hepatic venous ostia  51 . Balloon expandable strut  54  includes a mesh of struts  77  defining an open architecture  79 . The length of temporary retrievable strut  54  is longer than the funnel catheter  50  by design as this will further secure the ends of the funnel catheter to the ventral inferior vena cava  56 . The strut  54  also compresses the periphery of the funnel  50  assuring a tight seal against the ventral aspect of the inferior vena cava  56 . The surface of the strut  54  compressing the funnel  50  may be indented or have a concavity  58  so as to not obstruct the funnel  50 . The open architecture  79  of the strut  54  will not obstruct venous inflow from the renal or adrenal vein even if it covered them. This design solves the two problems of the prior art device mentioned above, the occlusion of renal/adrenal veins and the lack of an adequate through return channel for IVC blood. The temporary strut  54  forces the funnel catheter  50  (which is obliquely shaped) against the ventral aspect of the proximal IVC  56  securing it over the hepatic venous ostia  51  without occluding renal/adrenal veins. The funnel catheter  50  occupies very little annular space in the IVC  56  allowing blood to flow freely from the mid and distal IVC  56  into the right atrium through the spaces or interstices  59  in the temporary strut  54  when the balloon  60  on the temporary strut  54  is deflated. 
       FIGS. 10A and 10B  demonstrates the funnel catheter  50  in more detail. It is composed of two shafts  61 ,  62  and a mesh braid  63  of nitinol (or other appropriate biocompatible material) covered with a silicone elastomer (not shown) or other substance that is expansible and resistant to degradation by the chemotherapeutic agent. Unique to this application, however, the two shafts  61 ,  62  of the funnel catheter  50  are obliquely angled at their distal ends  64  so that the funnel  50  projects to the side of the catheter rather than directed distally in the prior art funnel catheters. In  FIG. 10A , the inner shaft  61  is retracted in respect to the outer shaft  62 . This keeps the mesh braid  63  of the funnel  50  within the lumen of the outer shaft  62 . The mesh braid  63  is bonded to both the inner shaft  61  and to the outer shaft  62 . As the inner shaft  61  is retracted, the mesh braid  63  forms a cylindrical channel parallel and within the channel formed by the outer shaft  62 . As demonstrated in  10 B, when the inner shaft  61  is advanced distally toward the ends of both shafts, the mesh braid  63  is propelled out the distal end of the outer shaft  62  and forms a funnel  50 . Moreover, the shape and the strength of the funnel catheter  50  can be affected by adding longitudinal, horizontal, and oblique lay ins. The shape memory properties of nitinol and the ability to place these lay ins with specific properties at specific locations within the braid allows a braid configured device to be tailored to the specific application. The combination of nitinol combined with brading technology essentially assures that most any shape is possible. In fact the description in this paragraph of forming a shape to cover the hepatic vein orifices is different than previous methods, which are all a funnels projecting distal to the end of the catheter. This construction may be used in other examples discussed herein. 
       FIGS. 11A, 11B, and 11C  represent the retrievable temporary balloon expandable strut (RTBES)  54 . In  FIG. 11A , the strut  54  is expanded over the inflated balloon  71 . The catheter contains two shafts, and outer one  73  and an inner one  76 . The balloon is attached to the inner shaft  76  and the RTBES  54  is attached to the outer shaft  73  via a bond  77 . Distal to the balloon  71  the braid  77  of the strut  72  is bonded  69  to the inner shaft  76  as shown. 
       FIG. 11B  demonstrate the balloon  71  to be deflated while the strut  54  is expanded. Forward force (arrows) on the outer shaft  73  with respect to the inner shaft  76  will assist in keeping the strut  54  expanded against the wall of the IVC (not shown) and the funnel catheter (not shown.) The interstices  79  of the strut  54  provide more than adequate space for blood to flow from the IVC into the right atrium. The pressure from the strut  54  forces the funnel catheter  50  against the ventral IVC and secures it in place over the hepatic venous ostia  51 . The RTBES  54  may be inserted via the internal jugular vein or the femoral vein, as may the funnel catheter, but usually the two would be inserted through separate veins. Moreover, the shaft  76  of the RTBES  54  may be utilized as the return conduit after the hepatic venous blood has passed through the filter, as it would serve no other purpose while the hepatic infusion was being performed. If utilized in this manner, it would be preferentially inserted via the internal jugular vein. Additionally, the shafts  73 ,  76  of the RTBES  54  may have openings (not shown) into the lumen along the shafts  73 ,  76  so some of the returning blood would be directed into the superior vena cava. 
     In  FIG. 11C , the outer shaft  73  is retracted (arrows) with respect to the inner shaft  76  collapsing the strut  54  over the balloon  71 , as the outer shaft  73  is bonded  77  to the strut  54  proximally and the inner shaft  76  is bonded  69  to the strut  54  distally. This will allow insertion and removal of the device  55  in a low profile. 
       FIG. 12  is a cross section of the two shafts  73 ,  76  of the device  55  proximal to the balloon  71  and strut  54 . It demonstrates the inner shaft  76  and outer shaft  73 . The inner shaft  76  comprises a large lumen  68  and at least one smaller lumen  67  for inflation of the balloon. Another lumen  66  may be present for insertion of a guide wire (not shown) or for injection of contrast. Contrast may be injected also through the space  65  between the inner shaft  76  and outer shaft  73 . 
       FIGS. 13B and 13C  discloses a retrievable self expanding or balloon expandable mesh braid structure  80 . It may be delivered and retrieved through a funnel catheter  81 , see  FIG. 13A , which is likely to be dissimilar to the funnel catheter  50  in  FIG. 10 . The funnel catheter  81  may be a simpler design in that occlusion or isolation is not required of the funnel catheter in this configuration and the funnel  82  at the distal end of the catheter is directed along the axis of the shaft of the catheter. The funnel catheter may not be even needed in fact. 
     In  FIG. 13B , the isolation apparatus is a retrievable self expanding or balloon expandable mesh braid structure  80  covered with an elastomeric material (not shown) resistant to the chemical properties of concentrated chemotherapeutic agents, such as, but not limited to silicone. The elastomeric covering (not shown) may cover all of this tubular structure  80 , or, in a preferred embodiment, only the ventral half. This latter configuration would preclude obstruction of renal or adrenal veins. In this particular configuration, the isolation chamber apparatus is a tubular mesh braid structure  80  with a side arm  83  that is inverted into the main lumen  84  of the structure  80 . This inverted side arm  83  is bonded  85  to the recovery tubing  86  that transports the hepatic venous effluent to the exterior of the body where it is pumped through the filter. Alternatively, the recovery tubing  86  may be attached similar to the recovery lumen  76  of  FIG. 4 . Also shown are the tether wires  88  attached to the structure  80  so that it may be withdrawn into the funnel catheter  81  for removal. Instead of the inverted side arm, the mesh braid structure  80  may be alternatively attached to the recovery lumen  83  as demonstrated above in  FIG. 4 . 
     As shown in  FIG. 13C , the ventral aspect of the retrievable tubular structure  80  containing the inverted side arm  83  contains a concavity  87  large enough to cover the ostia  51  of the hepatic veins  52  as well as to serve as a small reservoir to direct the hepatic venous effluent through an orifice  88  into the inverted side arm  83  and the recovery tubing  86  to the exterior. This configuration provides effective hepatic venous isolation as well as a very generous through return channel for IVC blood to pass to the right atrium, solving the major problems of the prior art device. 
       FIG. 14  demonstrates a retrievable isolation apparatus  90  in which the tubing  91  to the exterior is bonded (not shown) directly to the wall of the apparatus  90  vs. the more flexible inverted side arm  83  as in  FIG. 12 . The wall of the retrievable isolation apparatus  90  has a concavity  93  that covers the hepatic venous ostia  5  land serves as a small reservoir  94  to direct blood into the tubing  91  through an orifice  95 . The other properties are similar to those in  FIGS. 8B and 8C . In both inventions of  FIGS. 8B, 8C and 9 , there may be provided additional layer or layers of the elastomeric material  96 , or even a balloon structure (not shown), about the collection chamber to enhance the seal. A special braiding technique of the braid (not shown) may also enhance the seal at these locations. Since the hepatic veins enter the IVC either ventrally or on the right side, the elastomeric coating may be limited to these locations rather than being circumferential. Additionally, in the examples of the devices in  FIGS. 8 and 9  in which the elastomeric material  97  covers only the ventral and right side aspect of the apparatus, the additional sealing method  96  described above may essentially encircle the concavity described above to provide more effective sealing. The tether wires  99  are also shown. 
     Additionally the expandable mesh braid with the elastomeric coating  97  may contain a funnel shaped structure (not shown) on both ends to provide isolation of the hepatic venous blood. The ends may be comprised of a self expanding material (not shown) such as Nitinol that would cause the ends to flare out and contact the IVC wall with an exaggerated amount of force to provide an extra sealing property. 
       FIG. 15  demonstrates another configuration which is similar in construction to  FIGS. 11A, 11B and 11C  in that a retrievable temporary balloon expandable strut (RTBES)  98  is utilized. However the RTBES  98  is not utilized to compress the funnel catheter  50  against the ventral aspect of the IVC in this particular configuration. The RTBES  98  contains the collection chamber  101  which functions as the funnel catheter  50  did in the prior example. This RTBES  98  expands by inflating a balloon  71  and contracts by manipulating the inner shaft  76  and outer shaft  73  as demonstrated in  FIGS. 6A, 6B, and 6C . At least the ventral aspect of the strut  98  is covered with an elastomeric material  97 , although the elastomeric material may cover all of the structure except for the distal and proximal ends, and may have an extra layer  96  of elastomeric material at least partly encircling the collection chamber  94 , as in  FIG. 14 . The shape of this and other configurations can be controlled by braiding technology, the use of lay ins, and so forth. The hepatic venous collection tubing  91  may be directed extracorporeal as in the prior examples, but may alternatively be directed to and bonded to the distal aspect of the inner lumen  76  as is shown. The cross sectional view of  FIG. 12  would apply in this instance and the hepatic venous blood would be directed through the large central lumen  68 . 
       FIG. 16  demonstrates even another configuration in which a retrievable self expanding mesh braid device  110  with an elastomeric covering  113  is utilized. This double funnel  114  configuration in which the ends  114  of the device  110  flare out more than the central section. The central portion of the device  110  would be bonded to the recovery catheter  112  with at least one, but preferably several orifices  111  in the recovery catheter  112 . The added pressure at the ends would create an effective seal, isolating the hepatic venous effluent and directing it into the orifices  111  connecting to the recovery catheter  112 . Tether wires  115  on the proximal end of the device  110  may be attached to the shaft of the recovery catheter  112  or may be bonded together to form a single tether wire (not shown) for removal of the device  110 . In this example, the recovery catheter  112  extends through the entire length of the device  110  to give some rigidity and pushability to the device for placement, manipulation, and removal purposes. It may not extend the entire length of the device  110  however. 
     The braiding technique will typically create more expansile braid at the ends of the structure and less expandability in the central portion. Welds of the filaments in the center of the braid may be utilized to create a center section that is smaller than the distal ends as may the insertion of horizontal lay ins. The bonding of the orifices  114  in the ventral aspect of the device  110  will also help create a small reservoir in the central portion for the hepatic venous effluent. The funnel shaped ends will have a smaller footprint than the expanded balloons in  FIGS. 1, 2 , and  3  prior art devices, and should not occlude the renal veins. However, about the dorsal aspect of the distal end of the device  110 , a section of braid  123  may not be coated with the elastomeric coating  113 . This would allow blood from renal or adrenal veins to flow into the return through channel  124  through the open mesh. 
     There may or may not be radiopaque markers at the end  117  of the recovery catheter  112 , the distal end of the device  118 , and the proximal end  119  of the device  110 . Alternatively markers (not shown) may be on the device  110 . 
     The device  110  will typically be delivered and removed through a funnel catheter  120  which is a mesh braid  122  with an elastomeric coating  113  housed within a outer sheath  121 . In deployment the outer sheath  121  containing all of the components above would be inserted in the femoral or internal jugular vein and, in the case of the internal jugular vein insertion, the tip positioned just below the most caudal hepatic vein. While keeping forward pressure on the recovery catheter  112 , the outer sheath and the funnel catheter  120  would be withdrawn together deploying the device  110  as shown in  FIG. 16 . The proximal end would be cephalic to the most cephalic hepatic veins. The hepatic artery would be infused with a selected agent, and hepatic venous blood collected in the recovery catheter  112  through the orifices  114  and pumped through the filter outside of the body, and returned to the body as in  FIG. 1 . Alternatively, the filtered blood may be returned to the body through the funnel catheter  120 . At the termination of the procedure, the outer sheath  121  would be withdrawn from over the funnel catheter  120  exposing the funnel  120 . The device  110  then would be withdrawn through the funnel catheter  120  by withdrawing the recovery catheter  112 . When the device  110  was within the funnel  120 , the funnel  120  containing the device  110  would be withdrawn into the outer sheath  121 , and the entire apparatus removed. Again a generous through return lumen has been provided, an effective collection chamber is present, and means are provided to prevent occlusion of the renal and adrenal veins. 
     Even another configuration of this apparatus (not shown) utilizes a expandable funnel to occlude the IVC caudal to the most caudal hepatic veins similar to  FIG. 16  and a balloon to occlude the upper IVC just below the right atrium. In other words, the flare  114  of  FIG. 16  may be present on the caudal end, that is to the left, in  FIG. 16 , and a balloon structure (not shown) may be present on the cephalic end. The central lumen which serves as the return through channel to return IVC blood to the right atrium may be a self expanding braided segment with an elastomeric coating that is similar to that of  FIG. 16 . The hepatic venous blood that flows into the hepatic venous collection tubing does not have a separate channel within the isolated segment as in the prior art devices of  FIGS. 1, 2, and 3 . The hepatic venous effluent collects in a space outside of the expandable through return channel and directed into the recovery catheter which is directed through the balloon on the cephalic end in one iteration. The balloon inflation lumen may be contained in the wall of the shaft of the hepatic venous collection tubing as previously discussed. The cephalic end of the central return lumen in the right atrium may have openings to allow the IVC blood to exit this central lumen or may be comprised of the mesh braid without the elastomeric coating, the IVC blood flowing through the interstices of the braid. In this configuration, the funnel distally will provide occlusion of the IVC and effective isolation of the hepatic venous segment of the IVC with a very small footprint, obviating occlusion of the renal and adrenal veins, while the combination of the funnel shape of the caudal orifice of the expandable segment of the through return channel combined with the expanded through return channel will provide a very adequate conduit for blood to flow freely from the IVC to the right atrium. This configuration is a viable alternative to the prior art devices. The use of a balloon recognizes the fact that while the funnel shaped occluders will perform better than balloon occluders in most instances because of several reasons including the instant on/instant off capabilities, the much smaller footprint, larger through lumens, etc., that there may indeed be a need at the junction of the IVC and the right atrium to occlude with a large footprint. 
     The above method also has the benefit of creating a moderate degree of obstruction in the upper IVC, which may create increased pressure in the IVC vs. the hepatic venous effluent collection area. Obviating the obstruction to the returning blood is one of the main goals of the current invention as too much obstruction will cause a drop in blood pressure, etc., as described above. However, creating a controlled moderate amount of obstruction may be desirable to increase the IVC pressure above that in the hepatic venous effluent collection area so as to prevent leakage of the hepatic venous effluent into the IVC. This could be accomplished by a balloon or by other means incorporated into the design of the device, for example a baffle type device that is controlled by the operator. Pressure sensors may be provided within the upper IVC and within the hepatic venous effluent collection chamber to monitor the pressures of the two areas with or without the baffle device. This would be accomplished by providing wires along the catheter shaft(s) or by utilizing wireless pressure sensors. In this particular configuration, it is imperative that the seal about the hepatic venous effluent collection chamber prevent leakage not only from that chamber into the IVC or systemic blood, but also from the IVC into that chamber. 
     It should be noted that the pressure sensors would detect the pressure of the hepatic venous effluent and at least one pressure reading in the IVC or right atrium. By connecting the pressure sensors to a controller and the controller to the extracorporeal pump, the pump could be regulated to always have a lesser pressure in the hepatic venous effluent than in the IVC. If the pressure in the hepatic venous effluent became close to the pressure in the IVC, or even exceeded the pressure in the IVC, then the controller would speed the pump so that more blood was withdrawn from the hepatic venous effluent collection chamber, thereby diminishing the pressure within that collection chamber to a level safely below that in the IVC. This would ensure that there could be no leakage of hepatic venous effluent (lower pressure) into the systemic IVC (higher pressure,) If there was any leakage at all, it would be from the IVC into the hepatic venous effluent collection chamber, and this would not be harmful. The adjustment of the pressure by controlling the speed and output of the pump could be done automatically with the controller, or alternatively with a manual adjustment of the pump speed by the operator or an assistant who is manually monitoring the pressures hepatic venous effluent collection chamber and the IVC and/or right atrium. Alternatively, the pump could be programmed to run at a speed, or regulated by the controller utilizing a single pressure sensor, that would effectively keep the pressure in the HVECC, either by direct measurement or by extrapolated measurement, less than 1-2 mm Hg (the normal pressure in the right atrium) or thereabouts. This would insure that the pressure in the HVECC was less than the pressure in the IVC/RA, and hence there could be no leakage from a lower pressure system into a higher pressure system. In some examples the pressure in the IVC is taken manually before the procedure so that there would be needed only one pressure sensor proximal to the pump to control the pump speed and keep the pressure at this sensor less than the IVC pressure determined at the beginning of the procedure. 
     Still another alternative method (not shown) utilizes two balloons as the occlusion elements, both caudally and cephalically, but the through return channel is expansile by means of a catheter as in  FIGS. 11A , B, and C. This would take advantage of the proven occlusion features of the balloons, but the expansile through return channel would provide a channel large enough to return the IVC blood to the right atrium without the rather meager lumen of the current device. The struts on the catheter of  FIGS. 11A , B, and C would compress the inner circumference and inner wall of the balloon outward creating more annular space and lumen within the central open area of the balloon. The hepatic venous effluent is collected in the space isolated by the two balloon occlusion elements, and then transported to the exterior of the body. This may be done by a separate catheter lumen or through the main lumen of the catheter of  FIGS. 11A , B, and C. 
     A modified version of the embodiment described in the above paragraph would utilize an expanding apparatus to create the expansile through return channel within the center or “donut hole” of the balloons. It would be similar to the embodiment of the above paragraph, but the struts would expand without the use of a third balloon. The occluding balloons would be compressed from their inner circumference, enlarging it so as to provide an adequate through channel. A balloon configuration with an enlarged central channel has been termed a toroidal balloon. A toroidal balloon structure on each end of the device to define the limits of the hepatic venous effluent collection chamber (HVECC) may be combined with a self expandable structure such as a mesh braid or other self expandable structure and mounted on a catheter  73  as shown in  FIG. 4  and FIG. 6 . The balloons (not shown) would either augment or replace the flares  131 ,  132  in  FIG. 4  or be placed as in  FIG. 6  or  FIG. 7 . Otherwise this modified version would be generally similar to  FIG. 6 . This modified version of the embodiment is shown in  FIGS. 17 and 18 .  FIG. 17  is a longitudinal section of this modified version of this embodiment which demonstrates the expansile braid  54  within the center of the toroidal balloons  180  expanding the through return channel or by pass lumen  110 . The braid  54  can be placed adjacent to the recovery lumen  68 , but both are surrounded by the toroidal balloons  180 . The recovery lumen shaft  76  can contain inflation lumens  66  for the balloons  180  which can be placed at any one of a number of locations within the recovery lumen shaft  76 . Fenestrations  95  from the hepatic venous effluent collection chamber connect the hepatic venous effluent collection chamber and the recovery lumen  68 . The fenestrations  95  can be placed at any one of several locations about the recovery lumen  68 . The expansile braid or member  54  can be activated by an outer sheath member (not shown) and an inner sheath member (not shown) similar to the prior descriptions. It can be fixably attached to the distal end of the recovery lumen shaft  132  so one member can be moved longitudinally with reference to the other to compress or expand the braid  54  and to elongate or collapse it. The presence of this scaffolding  54  will support the through channel or bypass lumen  110  from being collapsed by the balloons  180  when they expand. 
     In  FIG. 18 , a cross section of the device at level X of  FIG. 17  is shown. The balloons  180  and the scaffolding  54  are collapsed in this example and the two balloon  180  walls abut each other. The recovery lumen  68  and balloon inflation lumens  66  are shown. The balloon inflation lumens  66  may be at other locations in the wall of the recovery lumen shaft  76 . Also shown is the collapsed scaffold or braid  54  directly beneath the recovery lumen  68 . The inner sheath  76  of the scaffold activating mechanism also houses a guide wire  154  which is directed out of the tip of the catheter assembly  132  in  FIG. 17 . The inferior wall of the recovery lumen shaft  76  is concave to accommodate the scaffold  54  when it is expanded as in  FIG. 17 . In practice the two balloon walls  180  at the lower portion of this figure would not be supported and would collapse into the space  199  beneath the recovery lumen  68  not occupied by the collapsed scaffold  54  and guide wire  154 . 
     The configuration described in  FIGS. 17 and 18  relates to embodiments where the braid is placed adjacent to, but not surrounding, the recovery lumen, and provides flexibility in changing the crossing angle such that the expansile and contractile range is extended over embodiments where the braid surrounds the lumen. This is especially useful in embodiments in which toroidal balloons serve as the blocking portion and the braid serves only to support the central bypass lumen and provides for the means to establish an adequate central bypass lumen in cases where the vessel is smaller than usual or in those cases in which the inflation of the balloons actually compress the central bypass lumen. Hence, the configuration in  FIGS. 17 and 18  with the braid adjacent to, but not surrounding, the recovery lumen can be used to enable proper expansion and contraction of the braid scaffolding so that a proper diameter of the central bypass lumen is maintained and blood flow return to the heart can be maintained. Maintenance of proper, or sufficient, diameter of the central bypass lumen provided by these embodiments provides for blood flow return to the heart such that patients&#39; cardiac output can be maintained and blood pressure does not drop to dangerous levels. The freely expandable and contractable braid scaffolding of these embodiments provides for support of the central bypass lumen such that the critical diameter or dimension of the central bypass lumen can be maintained and an adequate blood flow return to the heart can be maintained preventing the drop in blood pressure that could lead to patients needing resuscitation. 
     The embodiments described in  FIGS. 17 and 18  also provide for the braid scaffold that supports the central bypass lumen to act independently of the remainder of the device in this configuration. This allows flexibility in addressing the variations in sizes of blood vessels within the same individual and also the variation in sizes between different individuals that was recognized in the 50 patient CT study previously mentioned. For example, if the inferior vena cava is rather large in an individual, then the braid scaffolding supporting the central bypass lumen may expanded a bit more than usual and the toroidal balloons expanded a bit more than usual to create the seal needed against the vessel wall. The ability of the braided scaffolding to expand independently can prevent an over expanded balloon from compressing the central by pass lumen in this example as the toroidal balloon will expand outward to the vessel wall, but also will tend to expand inward and compress the central bypass lumen. If, however, the inferior vena cava is smaller than average, the braid scaffolding supporting the central bypass lumen can be expanded to a minimal critical diameter and the toroidal balloons inflated a lesser amount than usual. Since the inner radius of the toroidal balloons cannot compress the central bypass lumen because of the independent support by the braid scaffolding, the balloon expands only in an outward direction toward the vessel wall establishing a critical seal with less volume than otherwise would be necessary. This allows for flexibility with variable expansion of the central bypass lumen and the balloons. Another advantage of the embodiments described in  FIGS. 17 and 18  is that they is that the overall diameter of the recovery device in the collapsed configuration can be arranged to be smaller when the braid is not affixed to the recovery lumen and is able to expand and contract freely so that inserting and removing the entire recovery device will become less problematic and avoids the necessity of using a larger introducer sheath to place the device within the vessel. When the braid is attached to the recovery lumen, there is limited contraction of it as well as limited expansion. These embodiments provide for a device that is as small as reasonably possible for introduction into the blood vessel and that can then be expanded to a size as large as is reasonably possible to create the critical sealing and provide for an adequate central bypass lumen to avoid problems associated with restricted blood flow past the occlusion. The device in embodiments described in  FIGS. 17 and 18  will provide for easier insertion and removal. 
     The shape of the recovery lumen in  FIGS. 17 and 18  also provides significant advantages as the concavity in the surface adjacent to the braid scaffolding serves to nest the braid scaffold when expanded and collapsed. This shape also utilizes more of the available space within inner radiuses of the toroidal balloons and allows a smaller profile of the overall device than a typical rounded cross sectional shapes that are usually employed. 
     In embodiments described in  FIGS. 17 and 18 , the proximal actuator elements that expand and contract the braid are independent of the recovery lumen and not coaxially placed over the recovery lumen as in prior embodiments. The distal actuator element may be attached to or traverse the recovery lumen structure distally, but does not longitudinally traverse the sidewall of the recovery lumen as in prior embodiments. The braid scaffold acts independently of the recovery lumen and is not attached to it except at the distal end of the recovery lumen where the distal extension of the braid scaffold is anchored to the distal recovery lumen. 
       FIGS. 19 and 20  are longitudinal sections through a tubular length of elastomeric material that may be used for the through lumen or by pass lumen  110  and for the balloons  180 .  FIG. 19  demonstrates the material with ends AB and CD. To form the balloons  180  and the through or by pass lumen  110 , ends AB and CD are rolled onto the tubular portion of the material and bonded as demonstrated in  FIG. 20 . This is only one of a number of methods of forming the balloons and through/bypass lumen. The bonding may be end to side or side to side. 
     Sometimes two or more layers of various materials are laminated together to achieve desired characteristics. A generic adhesive used for all purpose applications may fail especially when temperature changes occur or the material experiences significant elongation as is the case with balloon expansion. Again, these conventional adhesives hold their substrates together by mechanical means. In addition, failure of the bond will occur during temperature fluctuations due to differences in coefficients of thermal expansion. The optimal adhesives use difunctional monomers and attach themselves to the substrates by a helical bond. This helix allows the resultant bond to move with the differences in the expansion and contraction rates of the substrates. Even substrates that are typically difficult to bond are activated and attached by this means. Of course, other methods known and described may be used to bond the materials. 
     Substrate activators have the unique capacity of removing active hydrogens from substrates and initiating the growth of polymer chains at that site. The following represents the four step reaction of a chemical grafting process using polypropylene as an example: 
     1) Activation: free radical formation 
     
       
         
         
             
             
         
       
     
     2) Chemical Bonding of monomers: 
     
       
         
         
             
             
         
       
     
     3) Formation of small polymer side chains: n=controlled chain length of monomers (same or varied) 
     4) The reaction is then terminated with a special formulation ingredient so that all reactive components are exhausted. 
     In this configuration, the apparatus would be positioned appropriately with the distal most balloon at the cavoatrial junction and the scaffolding expanded to form the through return or by pass lumen to allow blood from the IVC to flow unimpeded into the right atrium. The balloons would then be subsequently expanded in most cases to create the hepatic venous effluent collection chamber from which the hepatic venous effluent would flow through the fenestrations, into the recovery lumen and then out the recovery lumen shaft to an extracorporeal location where the blood would be pumped through a filter and then returned to the systemic venous circulation via the internal jugular or some other vein. 
     Another completely separate method of performing perfusion of an organ with a toxic substance and collecting the venous effluent, while providing for blood flow would be to utilize the prior art device or one similar that does not have an adequate through return lumen, but to add a second additional catheter system and, if necessary, a pump to transport blood from the lower IVC, or some other region, extracorporeally and then return it to the systemic circulation beyond the point of collecting the venous effluent, usually the superior vena cava. This would essentially create an extracorporeal bypass circuit and likely be functional, although problematic because of the added catheters, punctures, pump, equipment and so on. A special return catheter (not shown) may have two return lumens: one for the hepatic venous effluent which has been filtered and another for the systemic IVC blood which has been routed extracorporeally around the obstruction created by the use of the prior art type devices. This would obviate the need for two return catheters. The current inventions solve the problem of lack of an adequate through return channel without resorting to this relatively cumbersome method. 
     To prevent movement or migration of the device during infusion, an attachment mechanism (not shown) at or near the skin insertion site may be provided. It may vary in configuration from a suture attached to the tissues, to a clip at the skin level, to an anchoring device, or any other means of preventing movement of the catheter. 
     The methods of utilizing all of the above examples are quite similar. Imaging studies such as CT scans, MRI, or others are utilized to measure the distance between the most cepahalad placement of the flared blocking element, whether it be the cavoatrial junction or the supradiaphramatic IVC, and a point just above the renal veins. Measurements are also taken of the dimensions of the IVC. An appropriately sized recovery device, such as the device  138  of  FIGS. 4-8  of the current invention is chosen. Typically, a catheter is placed in the hepatic proper artery from a femoral puncture for subsequent perfusion of the liver by a concentrated high dose substance. The device of the current invention, in one configuration or the other, is placed in the IVC and deployed so that the isolation apparatus covers the hepatic venous ostia. The more cephalic end of the device may be placed in the right atrium or in the supradiaphragmatic IVC which is normally 1-3 cm. in length. In the case of the flared configurations of some of the embodiments, the distal flares may abut more force radially against the wall of the supradiaphragmatic IVC and the sealing annular force directed toward the wall of the IVC than if the device were placed in the right atrium and traction on the device at the cavoatrial junction utilized to produce a seal. Testing is done to determine if the placement is appropriate by injection of contrast in a retrograde manner through the recovery catheter and into the HVECC, and demonstrating that there is no leakage from the isolated segment. Contrast is injected into the distal IVC to determine that there is good return through flow to the right atrium. Testing will also evaluate the status of the renal veins and adrenal veins, and the device adjusted to provide for flow from these veins. Hepatic venous effluent will be collected, and the hepatic arterial infusion will begin. The venous effluent will be pumped and filtered extracorporeally and returned to the body as in the prior art devices for a period of time. After the arterial infusion is complete the venous effluent collection and treatment will continue for a prescribed period to prevent any delayed washout of the concentrated high dose substance from the liver into the systemic circulation. After a period of time, the chosen device will then be collapsed, retracted, and removed from the body. 
     In the cases where the approach is done preferably from the internal jugular vein, it anticipated that flush injections of contrast through the filtered blood return catheter that would be present in the femoral vein would be done to roadmap the anatomy, and could be done simultaneously with the placement of the apparatus as the blood would flow centrally toward the heart. A side arm on this catheter would provide a means of injecting contrast while the filtered blood return flow is maintained. This would be valuable to monitor the placement of the apparatus during the procedure and is not feasible with the current prior art devices. 
     It should be noted that features of the particular configurations listed above may be used with other configurations interchangeably to provide a smaller footprint of the isolation chamber in the IVC and to provide for an adequate return through lumen for IVC blood to return to the right atrium. While the devices described here have particular use in the inferior vena cava, use elsewhere in the body is also anticipated. Moreover, while the recovery of hepatic venous effluent has been described, reversing the flow through the recovery catheter apparatus may be done to deliver a drug or drugs or other substances in a retrograde manner to the liver via the hepatic veins or other tissues. 
     While the above descriptions of the funnel catheter and the isolation apparatus and the through return lumen describe the use of mesh braid as the supporting and expandable component of the particular configuration, other options are to be covered by this patent application, such as cross linking, spiral support configurations, strut like configurations, more or less parallel wires or support members, non-parallel wires or support structures, folded configurations, circumferential balloons, partially circumferential balloons, spiral balloons, abutting structures, and others. 
     In the case of treatment of cancers, tumors, infections, or conditions involving other organs which may have only one or two or a few veins draining that organ, there may be no need to occlude the vena cava. The simple insertion of a funnel catheter directly into the ostium of the vein(s) of that particular organ would serve to collect and isolate the venous blood from that organ. The funnel catheter, whether constructed of mesh braid or other materials, is a simpler, easier, safer, more stable and quicker method of isolating and collecting the venous effluent than balloon based catheters, and occlusion of a vein for the collection and isolation of venous effluent by any funnel catheter is expressly covered in this patent application. 
     In fact, the perfusion of a focal anatomic area whether it be an extremity, abdominal, thoracic, cervical, or cranial area, or other soft tissue or bone area with any substance in a concentration that would cause toxic effects in other areas of the body, and collection of the substance with a system that either does not use a balloon or provides for a expandable through channel is part of this application. For example the substance could be an antibiotic to treat a focal infection, an anti-tumor drug, a thrombolytic agent to dissolve clot, a substance that converts vulnerable plaque to stable plaque, or dissolve plaque, stimulates cellular growth, retards cellular growth, relieves pain, causes tissue atrophy or cellular apoptosis, causes lipolysis, causes hair growth or loss, improves or alters hearing, vision, taste, smell, and touch senses and the like. For example, the focal area or organ could be the brain, salivary gland, thyroid gland, lymph nodes, soft tissue, lungs, heart, spine, bone, kidney, ovary uterus, breast, extremities, digestive tract, nasal area and sinuses, eyes, ears, ant throat. 
     The local perfusion of an area of tumor with a highly concentrated substance may indeed be the first line of treatment in the future for the treatment focal malignancies to shrink if not obliterate the tumor. Surgery could then be done on the much smaller tumor, if indeed there were any tumor left. 
     In the case of organs that have only one or two veins, or organs where the venous drainage may be approached by several catheters that are placed directly in the ostium or ostia, the funnel catheter  113  design shown in  FIG. 16  may be utilized. Another design for a funnel catheter is shown in  FIG. 13A . The highly concentrated substance would be perfused into the artery of the organ, and the funnel catheter used for recovery of the venous effluent. The venous effluent would be pumped through the filter and returned to the systemic circulation as previously discussed. The action of the funnel in this particular embodiment may be controlled by moving inner and outer actuator sheaths  61  and  62  as in  FIGS. 10A and 10B . The ends of the two actuator sheaths  61 ,  62  are angled in  FIGS. 10A and 10B  causing the funnel in that illustration to project to one side. With actuator sheaths having ends that are not angled, the funnel will project straight ahead from the ends of the two actuator sheaths with a shape demonstrated in  FIGS. 13A and 16 . This will allow the funnel catheter to be placed within the ostium of the organ being treated. Because of the mechanical action of the funnel caused by the two actuator sheaths as in  FIGS. 10A and 10B , the funnel will exert radial force against the wall of the vein just inside the ostium and the braid will further anchor the funnel within the vein. 
     Organs that would be amenable to this approach include the kidneys, pelvic organs, extremity, brain, lung, breast, and various abdominal organs by placing the funnel catheter in the portal vein, amongst others. The artery serving that organ would be catheterized and the substance infused. A catheter for collection of venous blood using a balloon on the end to occlude or block the vein in question works fairly well, although is not as stable as desired, mainly because of its spherical shape. Balloons tend to slide within the vessel, and there is a much greater probability of a balloon occlusion collection catheter to slide out of the venous ostium that there is of the funnel catheter described above. The mesh braid creates a slightly irregular surface on the funnel which resists slippage along the venous wall without damaging the intima. 
     Moreover, the shape of the funnel is advantageous for another reason. Typical balloon catheters have an opening at the end of the straight cylindrical catheter just distal to the balloon. The venous effluent must be withdrawn through this end hole, and since it is desirable to keep the pressure in the draining vein less than the vein it is draining into, suction will be applied by the pump creating suction within this recovery catheter. With a single end hole, there is the possibility of the suction not only creating turbulence and resulting hemolysis, but also the possibility of causing the vein wall to occlude the single end hole because of the suction. The funnel catheter overcomes these problems by providing a smooth transition from a large diameter vein into the much smaller catheter, minimizing turbulence and hemolysis, and obviating obstruction of the catheter by the suction. Additionally, in recovering venous effluent from these single vein organs, it is imperative that any drainage through collateral veins be minimized or completely eliminated. Many venous collaterals exist, but only flow when there is increased venous pressure within the organ for some reason or another. Hence, having a catheter that can maintain a good deal of suction to keep the venous pressure low in the effluent vein and the organ is important in preventing collateral flow around the recovery system and leakage into the systemic circulation. 
     Certainly, the effectiveness of the seal about the recovery device acting as an isolation apparatus is paramount to prevent high concentrations of a deleterious substance from entering the systemic circulation. Since the free hepatic venous pressure is only 1-5 mm Hg. greater than the pressure in the upper IVC or right atrium, the seal does not have to be the same as that which might occlude arterial flow with pressure differentials of 100-200 mm Hg. However, it is imperative that no leakage occurs from the hepatic venous effluent chamber into the IVC. Testing the effectiveness of the seal may require frequent injection of contrast agent which is time consuming and not very accurate. An alternative method of detecting any leakage of the toxic substance would be to develop a real time assay of the toxic substance, and test systemic blood periodically. Alternatively, a substance that is easily assayed could be injected with the toxic substance into the hepatic artery. It would then be collected with the hepatic venous effluent along with the toxic substance and transported externally, where a separate filter (in line with the filter that filters the toxic substance) or the same filter would filter the easily assayed substance out of the blood to be returned to the body. Therefore, assays of systemic blood of the easily assayed substance would determine if the seal about the isolation apparatus was functioning properly. The easily assayed substance is filtered out of the returning blood, so if there was any activity in the systemic circulation, then it would alert the attending physicians that there was a high probability of a leak of the toxic substances into the systemic circulation. The easily assayed substance may be have the properties of methemoglobin or carbon monoxide, or any other substance for which there is a simple, quick, and easy assay, and also be a substance that is easily filtered. 
     It is apparent that the materials comprising the device must possess flexible, expandable, contractible, amongst other, characteristics including the ability to conform to different shapes and sizes within the same patient with enough annular force to effect a complete seal. The variety of shapes encountered in the IVC are much more varied than in the typical artery which has a more or less round shape and usually consistent, although occasionally minimal tapering, diameter throughout the area being treated or manipulated. While the pressures needed to seal the HVECC are less than the arterial system certainly, the need for the device to conform to different sizes and shapes in the same patient is of great importance in constructing a device for use in the retrohepatic IVC. The construction of the different embodiments of the current invention will utilize designs, materials and techniques specifically adopted to venous use and different than those devices typically utilized in arteries. 
     Another embodiment is described in  FIGS. 17 and 18 . 
     Compared to prior art isolation apparatus, recovery device  138  can achieve a smaller footprint as well as a larger through return lumen. Some examples of recovery device  138  can be made with either an adjustable length or different length devices may be used. 
     Any and all patents, patent applications and printed publications referred to above are incorporated by reference. 
     Modifications and variations can be made to the disclosed embodiments and examples without departing from the subject of the invention as defined in the following claims. For example, while the above examples and embodiments use separate mechanical actuators to expand the proximal and distal blocking elements, in some cases a single mechanical actuator could be used to the same effect; one such mechanical actuator could be a balloon housed within the recovery device having enlarged proximal and distal ends when expanded.