NZ786486A - Devices and methods for vascular hyperperfusion of the extravascular space - Google Patents

Abstract

external arterio venous fistula connection arranged to connect and provide circulation between an arterial cannula and a venous cannula to allow repeated sterile access to the arterial and venous side of the circulation without interruption of the flow of blood comprising: an arterial connection means arranged to sealingly connect to the arterial cannula; a venous connection means arranged to sealingly connect to the venous cannula to create a sealed passageway; and at least one reusable access portal; wherein the access portal is arranged to receive an endovascular device for insertion either into the vein connected to the venous cannula or into the artery connected to the arterial cannula.

Description

S AND METHODS FOR VASCULAR HYPERPERFUSION OF THE EXTRAVASCULAR SPACE Field of the Invention The present invention relates to improvements in vascular isolation of organs and ts thereof and, in particular, to ed devices and methods for vascular isolation of human extravascular spaces in organs and segments thereof, so as to enhance delivery and ty of therapeutic agents, such as chemotherapeutic agents and stem cells, to those extravascular spaces. The t invention additionally s to devices for engaging with vascular spaces and segments thereof. ound of the Invention Arterial or venous engagement and access for extended periods is required in many circumstances for a y of medical therapies and ents. This typically involves cannulation into an artery or vein. The interface n the vein or artery and cannula requires pressure to deliver materials or receive blood and minimise the ability for blood to stagnate around the interface thereby leading to thrombosis.

When blood is not being taken or substances are not being delivered into the vein or artery the lumen between the cannula and the vein or artery must be plugged to stop blood escaping. Typically, the end of the cannula and/or plug includes edges or protrusions or recesses that extend into the vein or artery or that result in an area of dead space in the cannula. Protrusions and recesses present a formation that potentially allows blood to pool and stagnate giving rise to the conditions where thrombosis can occur. Dead space also gives rise to an area where blood can pool and stagnate also ting a situation where thrombosis can occur. The dead space may also present an area where gas collects giving rise to the risk of a gas embolism forming.

The access devices used in such treatments or therapies typically comprise a cannula with one end connected to the circulatory system of a patient, and adaptor ports on the other end connected to a blood flow pump or other injection device. When not in use, the isolation system has relied on a plunger that is slidable within the cavity of the cannula to close access to the cavity and so to prevent fluid communication between the atory system and any of the ports of the access . Such access devices may be referred to as single lumen access devices.

US Patent No. 853 and US Patent No. 8,419,672 be such access devices for remote access isolation systems. Related access devices and systems are described in US Patent No. 9,078,982. Each of these three patents, also by the present inventor, are incorporated, in their entirety, herein by reference.

When a venous or arterial access, such as a cannula, is connected to a patient’s blood vessel at a perpendicular angle, the tip of a plunger can be slid through the cavity or lumen of the cannula until it reaches the location where the proximal end of the cannula is connected to the wall of the vessel. The plunger can thus, after use of the cannula, completely prevent the filling of the patient’s blood into the lumen of the a, thereby ng fluid stasis which may otherwise cause thrombosis.

However, when a cannula is connected to the patient’s blood vessel at a non-perpendicular angle, the conventional cylindrical shape of the tip of the plunger is not capable of ting the filling of a small amount of blood into a lower part (called "thedead space") of the lumen of the cannula unless the tip is slid further through the lumen of the cannula and a leading part of the tip protrudes into the lumen of the vessel.

Such a dead space within the lower part of the cannula’s lumen or, if the dead space is occupied by the plunger tip, such a protrusion of the leading part of the tip into the vessel’s lumen, can be responsible for haemodynamic disturbances, including fluid stasis, within the patient’s circulatory system that could result in thrombotic events.

When a single lumen access device of the kind bed in these patents, such as a cannula, is connected to a patient’s blood vessel at a perpendicular angle, the tip of a plunger can be slid through the cavity or lumen of the cannula until it reaches the location where the proximal end of the a is connected to the wall of the vessel.

The plunger can thus, after use of the cannula, completely t the filling of the patient’s blood into the lumen of the cannula, thereby avoiding fluid stasis which may otherwise cause thrombosis. However, when a cannula with an appropriately chamfered proximal end is connected to the patient’s blood vessel at a non-perpendicular angle, the conventional cylindrical shape of the tip of the r is not capable of preventing the filling of a small amount of blood into a lower part (called "thedead space") of the lumen of the cannula unless the tip is slid further through the lumen of the cannula and a leading part of the tip des into the lumen of the vessel.

Such a dead space within the lower part of the cannula’s lumen or, if the dead space is occupied by the plunger tip, such a protrusion of the leading part of the tip into the vessel’s lumen, can be responsible for haemodynamic disturbances, ing fluid stasis, within the patient’s circulatory system that could result in otic events.

Furthermore, access devices with multi-access ent caps are known, as shown in Figure 51 of US Patent No. 982 by the present or. However, those access devices with multi-access treatment caps have access ports which are such that only a single catheter may be received through a selected access port and then through the lumen of the access device, and therefore each such device can only facilitate either an outflow from the circulatory system to a blood flow pump or an inflow from a blood flow pump in the circulatory system, but not both. That is, those access devices with multi-access treatment caps cannot facilitate two or more inflow and outflow catheters at any one time because the lumen of those devices is unable to receive two or more catheters. Additionally, those multi-access treatment caps do not enable a catheter to be ed into specific positions with use of the multi-access treatment cap.

Arterial or venous infusions of pharmaceutical or other therapeutic agents are rd practice for chemotherapy in treating neoplasia, for gene therapy, and for stem cell therapy. The effect on the targeted tissue is diminished as a result of the on of the therapeutic agent by the normal flow of blood and/or the detoxification of the eutic agent by blood. To counter these effects, "stop flow" ques have been developed, usually by obstructing the inflow and outflow from the targeted tissue.

Standard techniques exist, for example, for the chemotherapeutic ent of neoplasia in the pelvis, in which the aorta and inferior vena cava are obstructed, tourniquets are applied to the legs and the isolated segment is then infused with a chemotherapeutic agent for a short period of time within the ischemic time of the pelvis.

An alternative approach is to remove the blood containing the chemotherapeutic agent and use various extracorporeal filters to neutralize the agent before systemic recirculation. The aim in that situation is to minimise the toxic side effects when the blood containing the chemotherapeutic agent is released into the systemic circulation.

This type of approach may be done operatively in the liver by cannulating the portal vein and the hepatic artery of the liver, using pumps to recirculate the agent and using an extracorporeal filter to minimise the systemic effects. This is called "isolated hepatic Remote access isolation s have been described for regional hyperperfusion to increase the blood flow to an intravascular space (see US Patent No. 9,078,982). Generally, hyperperfusion occurs when an above normal amount of fluid or cells passes through a space. Such isolation systems require an inflow port, an outflow port, an isolation balloon, and a pump to control the blood flow to the targeted organ. The pressures created are up to 4 times the normal arterial mean pressures with an increase of up to 8 times the normal flow. An aim of the hyperperfusion in US Patent No. 9,078,982 is to remove symptoms of an ischemic limb, in the short term to prevent tion, and in the longer term to e an increase in the shear stress to grow new blood vessels.

The inevitable effect of hyperperfusing therapeutic agents regionally to a desired intravascular space is that the agents will then move into the interstitial space from where they can enter not only the target area but also the draining lymphatic channels and lymph nodes. The approach has important ramifications in the treatment of neoplasia, as many malignant cells invade the lymphatic channels, migrate into the lymph nodes, multiply and then embolise via the thoracic duct before they move into the vascular system from where they spread systemically. Lymph nodes that are ed are notoriously difficult to treat because of their small size. Tumour ence often arises from residual tumours in lymph nodes and among lymph cells. Other problems relating to treatment of neoplasia arise from malignant cells ng in small numbers in relatively ischemic tissue, such that systemic treatment will have diminished effect.

Some tumours are also known to induce a higher interstitial pressure partly due to a surrounding pseudo-capsule related to ssion of normal structure and or secondary inflammatory s. There are also some malignant cells that do not multiply and so those therapeutic agents which mainly affect cell on will have little or no effect on such cells.

The access devices used in such remote access isolation systems for regional hyperperfusion to a target area and for ies or treatments where arterial or venous engagement for extended periods is required include cannulas, catheters (and especially balloon catheter systems), ns, plungers, adaptor ports and other devices required for these therapies or treatments.

Remote access isolation systems in the past have been able to e intermittent or acute access to a patient’s circulatory system for the purpose of hyperperfusion to ischemic limbs. The access devices used in such systems typically comprise a cannula with one end connected to the circulatory system of a patient, and adaptor ports on the other end ted to a blood flow pump. When not in use, the isolation system has relied on a plunger that is slidable within the cavity of the cannula to close access to the cavity and so to prevent fluid communication between the circulatory system and any of the ports of the access device. Such access devices may be referred to as single lumen access s.

US Patent No. 7,766,853 and US Patent No. 8,419,672 describe such access devices for remote access ion systems. d access devices and systems are described in US Patent No. 9,078,982. Each of these three patents, also by the present inventor, are incorporated, in their entirety, herein by reference.

When a single lumen access device of the kind described in these patents, such as a cannula, is connected to a patient’s blood vessel at a perpendicular angle, the tip of a plunger can be slid through the cavity or lumen of the cannula until it reaches the location where the proximal end of the cannula is connected to the wall of the .

The plunger can thus, after use of the cannula, completely prevent the filling of the patient’s blood into the lumen of the cannula, thereby avoiding fluid stasis which may otherwise cause thrombosis. However, when a cannula with an appropriately chamfered al end is connected to the patient’s blood vessel at a non-perpendicular angle, the conventional cylindrical shape of the tip of the plunger is not capable of preventing the filling of a small amount of blood into a lower part (called "thedead space") of the lumen of the cannula unless the tip is slid further through the lumen of the cannula and a leading part of the tip protrudes into the lumen of the vessel.

Such a dead space within the lower part of the a’s lumen or, if the dead space is ed by the plunger tip, such a sion of the leading part of the tip into the vessel’s lumen, can be responsible for haemodynamic disturbances, including fluid stasis, within the patient’s circulatory system that could result in thrombotic events.

Furthermore, access devices with multi-access treatment caps are known, as shown in Figure 51 of US Patent No. 9,078,982 by the present inventor. However, those access devices with multi-access treatment caps have access ports which are such that only a single catheter may be received h a selected access port and then through the lumen of the access device, and therefore each such device can only facilitate either an outflow from the circulatory system to a blood flow pump or an inflow from a blood flow pump in the atory system, but not both. That is, those access devices with multi-access treatment caps cannot facilitate two or more inflow and outflow catheters at any one time because the lumen of those devices is unable to receive two or more catheters.

It has been found by the present inventor that there are several ways in which ar isolation can enhance delivery of therapeutic agents to human organs and segments thereof, such as tumours, and thereby enhance therapeutic activity.

Firstly, an enhancing mass effect can be produced by the delivery of the agent to a specifically isolated target area to se the concentration of the agent in a confined mass of tissue in that area. This effect is based on relative tumour mass, and is called "mass targeting". The degree of enhancement depends upon the mass of the targeted tissue compared to the total mass of the body. For example, a pancreatic head cancer typically may weigh 35g on clinical tation. In a 70kg man, the therapeutic advantage of mass targeting approximates 2000x that of systemic intravenous delivery.

A second enhancing effect of vascular ion is called "exposure time prolongation" and involves the avoidance of washout or dilution of the agent by controlling the inflow and w for a period of time specifically within the ischemic time of the relevant organ. This is a time effect which multiplies the first mentioned mass effect. In pharmacokinetic language this is known as the "area under the curve", which is derived from a graph where agent concentration is plotted against time.

A third enhancing effect of ar isolation is the capacity to neutralize the agent, such as by administering an antidote before the isolation is reversed. This is called "neutralization of residual active chemotherapy". In order to avoid any systemic s, it is possible to reverse the flow through the isolated organ or segment thereof and t the residual agent and discard it before it has left the organ. This is called the al tration of the agent and can be measured by assessing the concentration of agent in the discarded volume.

A fourth enhancing effect of vascular isolation is by control of the osmolar pressure gradient into the isolated target area, uently controlling he oncotic pressure. Although access devices allow for control of the arterial inflow and venous outflow, even more targeted therapy may result from substitution of the intravascular plasma ns with hypo-osmolar solutions ning the therapeutic agents. A hypo-osmolar on creates an r pressure nt which controls movement of the therapeutic agents from the intravascular space to the extravascular space, and especially to the interstitial space surrounding the tumour cells. The interstitial space contains the metabolic substrates required by the tumour cells, and is drained by the lymphatic system. So, not only can tumour cells be specifically targeted in this way, but the lymphatic channels and lymph nodes draining from the tumour cells can also be targeted.

The control of the osmolar pressure nt can include controlling the oncotic pressure. The control of oncotic re enables the removal or l removal of the intravascular protein.

A further way in which ar isolation can enhance eutic ty is to selectively control the venous outflow of an organ, whilst simultaneously controlling the arterial inflow.

Again, with respect to the present invention, yet still a further way in which vascular isolation can enhance therapeutic activity is to increase the venous outflow pressure above the typical mean arterial pressure (MAP) and mean capillary pressure(MCP) as much as possible allowing an increased hydraulic force for injection up to and including the vascular pressure so that this hydraulic force can be directed laterally. This can be measured with instruments attached to the infusion system.

In the past there have been a variety of external fistulae usually for ialysis procedures. The original shunts were described by Quentin er, Allen Brown and Thomas Shunts. There may be direct anastomoses to the donor input artery and to the receiving vein (Thomas and Allen Brown). In some cases endoluminal connections were used without anastomosis and with the ligation of the distal vessels (Quentin Scribner). To access the systemic circulation the arterio and venous sides were temporarily clamped and the interconnecting device removed. This device was ly a simple endoluminal connecting tube with a possibility of easy disconnection. There are clear safety issues. This system was being connected to the therapeutic or diagnostic system. The prime example is renal haemodialysis.

Where external fistulae have been used high flow rates are . The high flow rates can contribute to congestive cardiac failure due to the high flow rates that manifests itself as peripheral , lethargy, ess of breath and chest pain. It can also cause peripheral "Steal" me where the high flow rate causes ischemia in the regions distal the fistula. High flow can also cause venous hypertension.

Summary of Invention In a first embodiment, the present ion seeks to provide an al arteriovenous fistula connection arranged to connect and provide circulation between an arterial cannula and a venous cannula to allow ed sterile access to the arterial and venous side of the circulation without interruption of the flow of blood comprising: an arterial connection means arranged to sealingly connect to the arterial cannula; a venous connection means ed to sealingly connect to the venous cannula to create a sealed passageway; and at least one reusable access portal; wherein the access portal is arranged to receive an endovascular device for insertion either into the vein connected to the venous cannula or into the artery connected to the arterial cannula.

Preferably, the external arterio venous fistula connection comprises a reusable arterial access portal arranged to receive an scular device for insertion into the arterial cannula and a venous access portal arranged to receive an endovascular device for insertion into the venous cannula.

Preferably, the external arterio venous fistula connection is configured to e sampling of blood without separate venous puncture.

Preferably, the external arterio venous fistula connection is configured to allow catheter insertion for continuous remote intra arterial or intravenous infusion of a therapeutic treatment. ably, the external o venous fistula tion further comprises a catheter loop for real time recognition of cell type.

Preferably, the catheter loop comprises a catheter inserted into the arterial side of the fistula connection; a device for recognising the cell type and to deliver blood back to the venous system without interrupting the blood flow in the fistula connection.

Preferably, the external arterio venous fistula connection further comprises a plunger configured to engage either the venous connection or the arterial connection to seal the respective tion or connections.

Preferably, the external arterio venous fistula connection further comprises a bridging device to connect the venous cannula and the arterial cannula.

Preferably, the bridging device comprises a passageway between the arterial cannula and venous a 305 to allow blood to flow through.

Preferably, the passageway sealingly s with the passageways of the arterial and venous cannulas.

Preferably, the bridging device ses engagement means to fix the ng device to the arterial and venous cannulas at an engagement point.

Preferably, the engagement point includes a seal to stop leakage of blood passing into or from the bridging device.

Preferably, the external arterio venous a connection further comprises an access portal located on the bridging device to provide access to the arterial and venous as.

Preferably, the access portal feeds directly into the passageway allowing catheters to be fed into either or both of the arterial side or venous side of the fistula connection.

Preferably, the external o venous fistula connection further comprises connection devices configured for sealingly fix the bridging device th the arterial and the venous cannulas.

Preferably, the bridging device further comprises an al-side access portal and a venous-side access portal.

Preferably, the external arterio venous fistula connection further comprises seals configured to engage the arterial access portal and the venous access portal. ably, the arterial and venous access portals comprise a pierceable membrane.

Preferably, the fistula connection is flexible.

Preferably, the external arterio venous fistula connection comprises an internal tube.

Preferably, the external o venous fistula connection ses: an outer housing; a first constriction device ured to engage the outer housing; and a constriction control element configured to pass into the fistula connection and engage the internal tube.

Preferably, the constriction control element is configured to apply force to the internal tube to constrict a d diameter portion of the internal tube.

Preferably, the external arterio venous fistula connection comprises a second constriction device around the outer housing.

Preferably, the second constriction device is ured to constrict both the outer housing and the internal tube.

In a second embodiment, the t invention seeks to provide a method of ring a eutic substance for treatment to a region of the body through vascular isolation and manipulation of fluid flux into and from the region of the body including the steps of: restricting vascular inflow to the region of the body; washing out oncotically active plasma proteins from the region of the body by increasing the outward oncotic pressure gradient from the region of the body; inducing ischemia in the region of the body; controlling the pressure and fluid flow of the main blood s to and from the region of the body; ing the therapeutic substance to the region of the body when the fluid flow to the region of the body is controlled.

In controlling the pressure and fluid flow of the main blood vessels to wash out proteins and enable therapeutic treatment, the present invention seeks to avoid the need for drug usage to expel albumens and allow therapeutic substances to cross extravascular space barriers.

Preferably, the region of the body is an organ.

Preferably, re h the vascular inflow is controlled to be less than or equal to 20mmHg.

Preferably, the pressure through the ar inflow is controlled to induce critical capillary closure.

Preferably, the oncotically active plasma ns are washed out at between 28mmHg to 35mmHg.

Preferably, outflow of the therapeutic substance from the region of the body is occluded using positive end expiratory pressure (PEEP).

By using PEEP, the need for mechanical occlusion of outflow ports to restrict the escape of therapeutic substances through the outflow is avoided.

Preferably, outflow of the eutic substance from the region of the body is controlled using relative movement of limbs of the body.

Preferably, the therapeutic substance is hyperperfused into the region of the body.

Hyperperfusion avoids the use of drugs to assist with substance transfer into extravascular spaces.

Preferably, the hyperperfusion is provided at less than or equal to 35mmHg.

Preferably, the occlusion of ar flow is achieved with multi balloon catheter line insertion to at least one of the blood vessels surrounding the target area.

Preferably, the therapeutic treatment includes at least one of herapy, supply of nanoparticles, stem cells, immunotherapy and or gene therapy.

Preferably, the manipulation of fluid flux includes at least one of occlusion of flow, partial occlusion of flow, isoperfusion or hyperperfusion of the main axial vessels to the target area.

Preferably, the manipulation of fluid flux is achieved with at least one of endovascular or extravascular devices.

Preferably, the method includes assessing and modulation of the fluid pressure of fluid within the blood vessels according to infusion.

Preferably, the method includes the steps of: delivering the therapeutic treatment to an interstitial space where tumour cells , or to the necrotic centers of tumours along an oncotic gradient penetrating pseudocapsule following an oncotic gradient; providing fluid that traverses the lymphatics and delivers ent to lymph nodes; and repeating delivery of therapeutic treatment over time may target cells that are not dividing at one ular treatment cycle.

By using the c nt to target tumour cells, the cells can be better targeted without collateral damage.

In a third embodiment, the present invention seeks to provide an ly for delivering a therapeutic treatment to a region of the body through vascular isolation and manipulation of fluid flux into and from the region of the body including: a first occlusion device adapted to restrict vascular inflow to the region of the body; a second ion arrangement to restrict vascular outflow from the region of the body; n the first occlusion device is adapted to increase the outward oncotic pressure gradient from the region of the body to wash out oncotically active plasma proteins from the region of the body so as to leave the region of the body in a state of ischemia; an injection device arranged to provide a therapeutic substance for the therapeutic treatment when the region is in ischemia; and a l device arranged to remove the therapeutic substance from the region of the body.

Preferably, the region of the body is an organ.

Preferably, the first occlusion device is arranged to control pressure through the vascular inflow to be less than or equal to 20mmHg.

Preferably, the pressure through the vascular inflow is lled to induce critical capillary closure.

Preferably, the oncotically active plasma proteins are washed out at between 28mmHg to 35mmHg.

Preferably, outflow of the therapeutic substance from the region of the body is occluded using positive end tory pressure.

Preferably, outflow of the therapeutic substance from the region of the body is controlled using relative nt of limbs of the body.

Preferably, the eutic substance is adapted to be hyperperfused into the region of the body through a catheter.

Preferably, the erfusion is provided at a pressure below the venous outflow pressure from the region of the body.

Preferably, the hyperperfusion is provided at less than or equal to 35mmHg.

In a fourth embodiment, the present invention seeks to provide a vascular access device for prolonged use including: a chamfered a ing a chamfered cannula end arranged to engage with a blood vessel at an angle; and a removable plunger arranged to block and seal a lumen of the cannula; wherein the ble plunger includes a chamfered end arranged to eliminate dead space within the cannula when the plunger is fully inserted in the cannula to block the lumen of the cannula.

The ation of deadspace minimises the risk of thrombosis.

Preferably, the chamfered end of the ble plunger is arranged so that it does not protrude into the blood vessel when the plunger is fully inserted into the cannula to block the cannula.

Preferably, the chamfered cannula end and the chamfered end of the plunger have the same chamfered angle.

Preferably, the cannula includes an inner wall profiled to mateably correspond to outer stem wall of the plunger.

Preferably, the inner wall of the cannula is ed so that the plunger cannot rotate due to the mateable correspondence with the outer stem wall of the plunger.The vascular access device as claimed in Claim 33 or Claim 34, n projections of the outer stem wall of the plunger are arranged to be received in recesses in the inner wall of the cannula.

Preferably, the mating correspondence of the cannula inner wall and the plunger outer wall are arranged so that the chamfered cannula end is parallel with and aligned with the chamfered end of the r when the plunger is fully inserted in the cannula.

Preferably, the cannula includes a graft end arranged to engage with a blood vessel and a body portion, wherein the graft end is arranged to connect with the body portion.

Preferably, the cannula includes a connector ly distal to the graft end ed to connect to a medical supply device.

Preferably, the connector assembly is arranged to connect with the body portion.

In a fifth ment, the present invention seeks to provide, a multiport adaptor for a cannula system including: a plurality of tubes g into a central lumen; wherein the central lumen is arranged to connect to a main cannula line that is arranged to connect to the vasculature.

Preferably, the plurality of tubes can be used to provide a plurality of cannulas into the vasculature via the central lumen.

Preferably, the plurality of cannulas is used to create a mosis in the vasculature.

Preferably, each of the plurality of tubes is arranged to receive and feed a guide wire into the central lumen.

Preferably, the plurality of tubes are flexible and ed so that lumens in each of the tubes do not intersect.

Preferably, the guide wires are arranged to be fed into the vasculature individually or together.

Preferably, the guide wires are arranged to include balloons.

Preferably, the guide wires are arranged to be directed to inflow and outflow vasculature bodies of a particular region so that the particular region can be isolated with medical devices associated with the guide wires.

Preferably, each of the ity of tubes is arranged to connect an external medical device.

] Preferably, the plurality of tubes are arranged to connect to the external medical device with a luer lock.

] Preferably, the plurality of tubes are arranged to e a plurality of endovascular devices into the vasculature simultaneously.

In a sixth embodiment, the present invention seeks to provide an external arterio-venous fistula connection arranged to connect between an arterial a and a venous cannula including an al connection means arranged to sealingly connect to the arterial cannula, a venous connection means arranged to sealingly connect to the venous cannula to create a sealed passageway and at least one reusable access portal; wherein the access portal is arranged to receive a catheter for insertion into the vein connected to the venous cannula or artery ted to the arterial a.

Preferably, he external arterio-venous a tion includes a reusable arterial access portal arranged to receive a catheter for insertion into the arterial cannula and a venous access portal arranged to receive a catheter for insertion into the venous cannula.

Brief ption of the Drawings Notwithstanding any other embodiments that may fall within the scope of the present invention, an embodiment of the present invention will now be described, by way of example only, with reference to the accompanying s, in which: Figure 1 is a schematic representation of an arterial occlusion balloon positioning arrangement for control of arterial flow in the pelvis region according to an embodiment of the present invention; Figure 2 is a schematic representation of a vascular occlusion balloon positioning arrangement for control of vascular flow according to an embodiment of the present ion; Figure 3 is a schematic entation of a vascular occlusion balloon oning arrangement of a single balloon catheter system which provides control of collateral vascular blood flow for use in vascular isolation of the right breast according to an embodiment of the present invention; Figure 4 is a schematic representation of an arterial ion n positioning arrangement of a multi balloon catheter system which provides control of collateral arterial blood flow for use in vascular isolation of the right breast according to an embodiment of the present invention with super selection of al inflow; Figure 5 is a schematic representation of an arterial occlusion balloon positioning arrangement of balloon catheter systems for control of vascular flow to the liver according to an embodiment of the present ion; Figure 6 is a schematic representation of an arterial occlusion balloon positioning arrangement of balloon er systems which provides control of collateral arterial blood flow for use in hyperperfusion of the liver according to an embodiment of the present invention; Figure 7 is a schematic representation of vascular occlusion balloon positioning arrangement according to an embodiment of the present invention for treatment of the cranial region; Figure 8 is a tic representation of an arterial occlusion balloon positioning arrangement for control of vascular flow to the lower limbs according to an embodiment of the present invention; Figure 9 is a tic representation of an arterial occlusion balloon positioning arrangement for control of vascular flow to the lower limbs according to an ment of the present invention; Figure 10 is a schematic representation of an arterial occlusion balloon oning arrangement of three separate ns in catheter systems which e control of vascular flow to the pancreas according to an embodiment of the present invention; Figure 11 is a schematic entation of a pressure lled intraluminal balloon and a connecting distal end of a multi-channel catheter shaft system according to another embodiment of the present invention, for use in the duodenum for vascular isolation of a tumour in the pancreas according to an embodiment of the present invention; Figure 11A is a side view of the ssive balloon of Figure 11; Figure 12 is a schematic representation of an arterial occlusion balloon oning arrangement of a three separate balloon catheter system, and which provides control of collateral arterial blood flow for use in hyperperfusion of the liver Figure 13 is a schematic representation of vascular isolation of the upper lobe of the lung; Figure 14 is a sectional side view of a single lumen access device of the prior Figure 15 is a sectional side view of a cannula of another single lumen access device of the prior art, showing the tip of a plunger stem of the device protruding from the cannula into the lumen of a blood vessel of a patient; Figure 16 is a sectional side view similar to that of Figure 15, but showing the tip of the plunger stem of the device no longer protruding into the vessel lumen but retracted into the lumen of the cannula so as to create a dead space within the lumen of the cannula; Figure 17 is a side view of a cannula of a single lumen access device according to an embodiment of the present ion; Figure 18 is a sectional end view through B-B of the cannula of Figure 17; Figure 19 is a side view of a plunger stem having a red tip for use with the a shown in Figures 17 and 18 of the single lumen access device; Figure 20 is a sectional end view through A-A of the plunger stem of Figure 19; Figure 21 is a side view of the single lumen access device formed of the cannula of Figures 17 and 18 and the plunger stem of Figures 19 and 20, with the single lumen access device being connected to a patient’s blood vessel and not g any resulting protrusion or dead space; Figure 21A is a side view of an alternative cannula to the cannula of Figure 17; Figure 22 is a sectional side view tudinally) of the cannula of Figure 17; Figure 23 is an ed view of the ned part B of the cannula as shown in Figure 22 Figure 24 is an enlarged view of the sectioned part C of the cannula as shown in Figure 22; Figure 25 is a perspective view of a multiport adaptor according to an embodiment of the present invention connected, for use, with a cannula of a single lumen access device; Figure 25A is a perspective view of a multiport adaptor according to an embodiment of the present invention; Figure 26 is an exploded view of the multiport r shown in Figure 25 alongside the cannula; Figure 27 is a side view of the interconnected multiport adaptor and cannula of Figure 25 shown connected to a patient’s circulatory system and showing an occlusion balloon oning arrangement of three separate balloon catheter systems which all pass h the lumen of the cannula into the circulatory system to control vascular flow to or from an organ; Figure 28 is a perspective view of a multiport adaptor according to another embodiment of the second invention connected, for use, with an implantable cannula of a single lumen access device; Figure 29 is an exploded view of the multiport adaptor shown in Figure 28 alongside a distal end of the implantable cannula; Figure 30 is a side view of the interconnected multiport adaptor and cannula of Figure 28 shown connected to a patient’s circulatory system and showing an occlusion balloon positioning arrangement of three separate n catheter systems which all pass h the lumen of the a into the circulatory system to provide vascular isolation of an organ; Figure 31 is a side view of an external fistula device according to an embodiment of the t invention; Figure 32 is a side view of an external fistula device according to an embodiment of the t invention; Figure 33 is a side view of a port used in the external fistula device of Figure 32; Figure 34 is a side view of an external fistula tor device ing to an embodiment of the t invention; Figure 35 is a side view of the external a connector device of Figure 34 cannulated; Figure 36 is a side view of a multiport catheter connection and plunger according to an embodiment of the present invention; Figure 37 is a side view of an external fistula device according to the present invention; and Figure 38 is a side view of an external fistula device according to the present invention.

Detailed ption of the Invention Broadly, with reference to s 1 to 13 an embodiment of the present invention s to a system and devices for improving the delivery of therapeutic substances for therapeutic treatment into the extra vascular, i.e. interstitial space, where the targeted cells or lesions are situated, specifically hyperperfusing the ischemic interstitial space. Hyperperfusion is defined as to cause an above normal amount of fluid (or cells) to pass through a space. The inevitable effect of hyperperfusing therapeutic agents into the interstitial space is to hyperperfuse the target as well as the draining lymphatic channels and lymph nodes. The concept has important ramifications in the treatment of neoplasia as many of the malignant cells invade tics, migrate into the lymphatic nodes, multiply, then embolise via the thoracic duct and then into the venous system and hence is spread systemically. Lymph node involvement is notoriously difficult to treat related to the small size of lymph nodes. Tumour recurrence often s to residual tumour in lymph nodes and lymph cells. Other problems relating to treatment of neoplasia relate to malignant cells residing in small numbers in [Link] https://en.wikipedia.org/wiki/Hydrostatic_pressure [Link] https://en.wikipedia.org/wiki/Oncotic_pressure [Link] https://en.wikipedia.org/wiki/Capillary relatively ischemic tissue so that systemic treatment has y diminished penetration capacity and hence . Some tumours are also known to have a higher interstitial pressure induced partly due to a surrounding pseudocapsule d to compression of normal structure and or secondary inflammatory effects. There are also some malignant cells that are not lying and as many therapeutic agents have its main effect on cell division. The physiological laws governing fluid fluxes across capillary ne is described in Starlings equation.

The Starling equation reads as follows: where: is the net trans vascular fluid flow in cubic centimetres per second; is the net driving force; Pc is the capillary hydrostatic pressure; Pi is the interstitial tissue hydrostatic pressure; πc is the capillary d oncotic pressure; πi is the interstitial tissue colloid oncotic re; Kf is the capillary filtration coefficient⎯a proportionality constant; and σ is the capillary protein reflection coefficient.

The reflection co-efficient is a correction co-efficient that reflects the variability of the oncotic pressure gradient. Typically the reflection co-efficient is less than 1.

Following are approximated values for the variables in the equation for both arterioles and venules in the body: Pc Pi σπc σπi Location (mmHg) (mmHg) (mmHg) (mmHg) arteriolar end of capillary +35 −2 +28 +0.1 [Link] //en.wikipedia.org/wiki/Venule venular end of capillary +15 −2 +28 +3 ng that the net driving force declines linearly, then there is a mean net driving force outwards from the capillary as a whole, which also results in more fluid exiting a capillary than re-entering it. The lymphatic system drains this excess.

In the methods of treating a region of the body with a eutic substance as disclosed herein, the methods provide pressurised on of the therapeutic substance with ar isolation to induce hyperperfusion of interstitial tissue in the region of the body and its draining lymphatic channels and lymph nodes. In this way, the therapeutic substance can pass from the region of the body via the lymphatic system. As such, use of a l device or extraction device may not be required for removal of the therapeutic substance from the region of the body. s in the Variables with Hyperperfusion of the Interstitial Space ] The following embodiments of the t devices and methods reduce the capillary pressure below the "critical closing pressure". When infusion begins the capillaries reopen and receive the infused substrate. They close again when the infusion is stopped minimising dilution by red cells and plasma. Typically, the critical closing pressure is 20mmHg.

Embodiments of the present invention allowing improved pressure driven washout and hyperperfusion of the interstitial space affects the following variables: (a) Reduction of the Pc as the pressure gradient from the arteriolar to the venules is normally high and the venous capacitance is several times the arteriolar capacitance; reduction of the perfusion pressure is essential to avoid rapid washout of the therapeutic substance. (b) se the oncotic nt to drive wash out of red blood cells, plasma and protein from the titial space. (c) Elevation of the therapeutic perfusion pressure (Pp) by the infusion catheter. Often the Pp is greater than the original Pc and optimally the Pp is greater than the Pc so that maximum therapeutic agent traverses the basement membrane into the interstitial space. (d) Reduction of πc as intravascular albumen is important for the oncotic nt diluting this with saline causes a net outward flux from the ascular to the ascular space. This is augmented by the lower molecular weight of many therapeutic agents which passively cross from the ascular to the extravascular space and therefore aid therapy. Many active therapeutic agents are bound by albumen decreasing their efficiency. For example Oxalyplatin is 70% rapidly and irreversibly bound to Albumen. The described devices are capable of diluting the albumen with the reduction of the oncotic pressure and therefore improving interstitial hyperperfusion. (e) The devices also allow increasing the filtration coefficient (Kf) by inducing ischemia. Decreased red blood cells intravascular leads to a decrease in oxygen delivery to the capillary endothelium resulting in increased capillary permeability and net increased outward flux. The local ia induced vaso dilatation which ses local cross sectional area and therefore increases total outward flux and facilitates extra vascular flow.

] Embodiments of the devices of the present invention, at least in part, seek to: 1. reduce, se or reverse the Pc, Pv gradient; 2. increase the outward oncotic gradient by diluting or removing intravascular albumen and plasma proteins; 3. optimise therapeutic activity by minimising covalent binding; 4. creating ischemia sing outward flux across endothelial membranes; . increasing the cross sectional area by vaso dilatation induced by ischemia; 6. induce critical closing of capillaries; 7. increase the venous w pressure as much as possible; and 8. infuse therapeutic agent up to but not exceeding the key little v so there is no escape of therapy into the systemic circulation.

On the venous side, the devices allow varying degrees of ction and depending on the treatment site can be endovascular balloons occluding outflow, positive end expiratory pressure (PEEP) or ascular in a occlusion device which can transcutaneously be inflated or deflated to control d flow.

The effects of controlling the intravascular to extravascular flux: (a) Deliver therapeutic agents to interstitial space where tumour cells reside in small numbers; or to the necrotic centers of s along an oncotic (b) Have increased capacity to penetrate pseudocapsule following an oncotic gradient. (c) The fluid traverses the lymphatics and delivers treatment to lymph nodes. (d) Repeat delivery of agents over time may target cells that are not dividing at one particular treatment cycle.

The critical closing pressure can be used as a valve; normally at 20mmHg.

With an inflow port to an extravascular space occluded the al closing re can be relied on to operate as a valve. After washout of the extra vascular space has occurred and the delivery of the eutic agent is complete the capillary system s closed, then minimal dilution of the area by normal blood can be expected.

The pressure difference between hyperperfusion and the intravascular and extravascular space are extreme. The ascular erfusion requires greater than normally produced pressures by the heart. There is associated with dilatation of the distal vessels increased sheer stress and decreased venous flow. The Gaseous flux from red cells to and from the cells is immediate, i.e. extremely small diffusion time and ndent of osmotic pressure and plasma.

In many tumours, the vascular inflow is tortuous, of irregular diameter and may end blindly. There is a reduced flow, pressure and higher resistance which results in reduced chemotherapy delivery. The capillary inflow pressure can drop to 5mmHg. In these circumstances, hyperperfusion leads to a greater net inflow pressure and se to the MAP and MCP thereby creating a r net inflow pressure and greater therapeutic substance delivery. Hyperperfusion also applies to the lymphatic system, creating greater increase in lymphatic flow related to high interstitial pressures.

The increase flow containing eutic substances is delivered to both lymphatic vessels and nodes.

Possible treatment involving the vascular isolation of organs or anatomical regions of the human body includes but is not limited to the liver, pancreas, pelvic organs, lower limbs, cranial region etc. In various embodiments of the present invention, multiple ation systems employing balloons 24 and catheters 22 are inserted into the patient’s vasculature using cannulation techniques and subsequently positioned in the arteries and/or veins supplying blood to the target area. The balloons of these balloon catheter systems are then inflated, cutting off or occluding the arterial or venous inflow to the target area and ishing an isolated zone of significantly reduced blood inflow. This ed zone allows for infusion of therapeutic agents into the target area whilst minimizing systemic exposure. Vascular isolation may be further ed by using a separate access device to locate additional n catheter systems in the veins so as to occlude venous outflow from the target area or lesion, or by using positive end expiratory pressure (PEEP).

With the isolation zone established, it is within the scope of the t invention to provide infusion to the target area with the flow of blood within the blood vessel or against the flow of blood.

Broadly, the t invention provides a blood vessel occlusion balloon positioning assembly 20 for isolating a region within the body. The blood vessel occlusion balloon positioning arrangement includes an access device 41 arranged to engage, pierce and provide access into a blood vessel, a ity of catheter lines 22 and catheter balloons 24 located around the catheter lines 22 that are arranged to be inflated within a blood vessel to control the flow of blood. The er lines 22 and balloons 24 are arranged around the region within the body to isolate it from blood flow.

Embodiments of the present invention envisage measuring the pressure within blood vessels 23 and controlling the flow and pressure in sections of the blood vessel Figure 1 rates a blood vessel occlusion balloon positioning arrangement 20 according to an embodiment of the present ion used in the pelvis area from the aorta 81. This can include, but is not limited to, targeting bladder, recto sigmoid, prostate, anal canal, vagina, cervix, uterus, ovary, lymphoma cytoma and sacral tumours. Typically this region includes a number of blood vessels 23. In the arrangement of Figure 1, the balloon positioning ement 20 es an access device 41 for piercing and providing access to the blood vessels 23, a plurality of catheter lines 22 and er balloons 24 around the catheter lines 22 that are arranged to be inflated within a blood vessel to control the flow of blood to a target site.

In the embodiment of Figure 1 the target site is a tumour 11. The catheter lines 22 and balloons 24 are inserted into blood vessels via access device 41 and arranged in blood vessels 23 around the tumour 11 to isolate it from blood flow.

Typically, the targeted organ/region in the pelvis area has a ral blood supply requiring control of the blood flow through both supplying blood vessels. This may require a l system with two er lines 22 with separate balloons 24. This allows the two catheter lines 22 to place balloons 24 in both blood supply vessels. For example, when the tumour 11 is prostatic carcinoma, a balloon at the origin of the internal iliac system including both the anterior and posterior divisions with a super selective catheter going into the inferior vesical artery which is the desired optimal artery to infuse is used.

Figure 2 illustrates the use of the balloon positioning arrangement 20 according to an embodiment of the present invention used in blood vessels 23 from the inferior vena cava 46. The blood vessel occlusion balloon positioning arrangement 20 includes an access device 41 for piercing and providing access to the blood vessels 23, a plurality of catheter lines 22 and catheter balloons 24 around the catheter lines 22 that are arranged to be inflated within a vein to control the flow of blood to a target site. In the embodiment of Figure 2 the target site is a tumour 11. The catheter lines 22 and balloons 24 are arranged in blood vessels 23 around the tumour 11 within the body to isolate it from blood flow.

With t to Figures 1 and 2, where bilateral infusions are ed access device 41 can be used from the lateral side or teral individually.

Figure 3 shows an example of a blood flow control balloon 24 to minimise eral venous flow and optimise infusion of chemotherapeutic agents in the right breast.

Figure 4 shows an example of a plurality of blood flow balloons 24 being used to ze collateral arterial flow and further optimise infusion of chemotherapeutic agents in the right .

] The balloons 24 co-operate to allow selective arterial infusion of chemotherapeutic or other therapeutic agents into a target area via an infusion channel 116 through catheter 22 and balloon 24 in the lateral thoracic artery 118. Collateral blood flow control balloon 114 minimizes arterial collateral flow to the target area by obstruction of the vessels distal to innominate artery 120, the internal ic artery 124, the superior thoracic artery 126 and the thyrocervical trunk 128. The common carotid artery 122 feeds into the innominate artery 120.

In one embodiment of the present invention irradiated particles can be injected to the isolated region of the body at the time of arterial infusion or at a later time.

With specific reference to Figure 3, collateral blood flow control balloon 24 minimizes venous collateral flow from the target area by obstruction of vessels proximal the innominate vein 130, the internal thoracic vein 134, the pectoral vein 136 and the lateral thoracic vein 138. In this way, there is obstruction of the ry and subclavian arterial system to the right breast (as shown in Figure 4), and there is obstruction of the axillary and subclavian venous system from the right breast (as shown in Figure 3). The internal jugular vein 132 joins into the right subclavian vein 141. The obstruction of the main venous outflow from the right breast increases the venous pressure in the target area, thereby optimizing the effect of the chemotherapeutic agents on the lesion.

Figure 3 also shows a shaft 140 that containing separate guidewire and inflation channels (not shown) leading to the balloon 24 via the basilic vein and then the right subclavian vein 141, and an end 142 of the shaft 140.

Figure 4 also shows a shaft 143 that contains separate guidewire and ion channels (not shown) leading to the balloon 24 via the brachial artery or alternative access points as understood by the skilled addressee, and then the ry . Also shown is a shaft 145 containing te ire and inflation channels leading to the balloon 24, also via the brachia, artery and then the axillary artery 144, and an end 146 of the shaft 145.

With reference to Figure 4, it is within the scope of the present invention that other arteries, for example the internal thoracic artery to be infused.

Figure 5 shows an arterial occlusion balloon positioning arrangement 20 of a balloon catheter system for vascular isolation of the liver 21. Three catheter balloons 24 on catheter lines 22 are inserted into the blood vessels 23 supplying blood to and from the liver 21. Balloons 24 are placed in a number of the or eric artery 25, the gastroduodenal artery 43, the common or proper hepatic artery 23, and the splenic artery 42. 46 is the inferior vena cava and 44 is the coeliac axis.

Figure 6 shows an e of ar isolation of the liver 21 to treat a tumour 11 by the positioning of an inflated occlusion balloon 24 in the hepatic artery 23 and by a atheter 3 that is located through a central guidewire channel of the occlusion balloon 24 and extends to an opening inside the hepatic artery 23. The microcatheter 3 is so formed that it wedges inside the s supplying the tumour 11 and, by the forcing of the walls of the microcatheter 3 against the walls of the vessels supplying the tumour, it obstructs flow through the arterial collaterals. The umbra or flow shadow is dense due to the double obstruction minimising the flow to the tumour 11. The portal collaterals are also obstructed by balloons 24 which are either intravascular or exovascular nding the celiac axis 44, superior mesenteric artery 25 and inferior mesenteric vessels, tively. The result is a low arterial flow in the intestines 35 with secondary low flow through the portal vein 69 which further decreases the flow to the tumour 11. In one embodiment, this flow can be further decreased by inflating an implantable cuff 26 around the portal vein 69. This method of vascular isolation also increases the ischemic effect, thereby inducing central necrosis in the tumour 11, which has a growing edge 5. The interstitial fluid flow in the tics 4 from the tumour 11 is sed by sing the pressure in the hepatic veins 73 and inferior vena cava (IVC) 46 through controlling the positive end expiratory pressures (PEEP). The outward flow from the tumour 11 can be controlled by varying the PEEP. Alternatively, three separate balloon 24 catheters 22 can be positioned to occlude the three c veins 73, respectively.

] It is within the scope of the present invention for alternative forms of restriction than an inflatable cuff for flow ction, such as a tourniquet or otherwise.

Figure 7 shows an embodiment of the present invention applied to the vascular and arterial isolation of the cranial region 39. This may include tumours 37 of the brain or carcinoma of the tongue, larynx, pharynx, l skin and submandibular .

In one embodiment, the site of origin of the y is an access device 41 at the origin of the external carotid artery 74 or it can be from either or both groins or arms.

The access device can be implanted unilaterally or bilaterally. Access device 41 is implanted bilaterally for structures receiving close to midline blood supply. For inflow, the main axis is super selected to the target area and controlled with endovascular or extravascular balloon 24 occlusion systems on catheters 22 as described above. In some situations the ion system is d to the excellent collateral flow of a proximal and distal balloon 24 systems (co-rail systems are required to reduce res that correspond to the critical g pressures which are 20mmHg at a pre ary .

For collateral control, other branches of the external carotid 74 may need to be cannulated depending on the radiological ance and the pressures obtained after occluding the main axis. Other neighbouring branches of the external carotid may be required to be controlled including the branches of the subclavian vessels such as the costocervical and thyrocervical trunks.

Outflow control is achieved by postural manoeuvres (such as moving into the Trendelenburg position), positive and expiratory pressures and occlusive catheters in the al jugular vein 75, common facial or anterior jugular vein which may involve endovascular or external vessel occluding systems.

Internal occlusion of the internal jugular vein is achieved with a balloon 24 catheter 22 as described above. External occlusion is achieved with an extravascular ion device 78 that applied pressure to the outside of a vein via an inflation line 79.

The external occlusion with extravascular occlusion device 78 is applied to the same blood vessel that the access device is applied to, on the same side. That the occlusion device 78 is illustrated on the contralateral side in Figure 7 indicates that bilateral use.

The venous pressures are continuously monitored. Once l of the vessels is contained, the plasma proteins and blood are washed out from the targeted t and ed with the saline containing therapeutic agents. With reestablishment of flow the collateral and main axis arterial inflow may be ed first and the venous outflow control ues for 5-20 minutes to minimise systemic recirculation. With the plasma proteins washed out the action of the patient’s antibodies is greatly reduced or eliminated. With the action of the patient’s antibodies in the target segment being eliminated or reduced the chances of an immune response in the target segment is greatly reduced or removed.

There are several constraints in the ent of delivery of eutic agents into the parenchyma of the brain. The blood brain barrier (BBB) prevents more than 95% of eutic substances traversing the elium. Molecules less than 500 Daltons are usually able to cross. The problem is the tight junctions between endothelial cells do not allow free movement across this barrier. The next problem related to the tumours themselves as they tend to be diffuse rather than being focused in a specific mass. In regard to the fluid flux this is associated with an increase in intracranial re which may induce symptoms associated with the syndrome of intracranial hypertension. The next m relates to the relative brain ischemia, particularly with focal infusions. The isolation treatment would best be done under local anaesthetic to modulate the on time. The last problem is the good collateral flow in some parts of the brain which is difficult to e oncotic gradients as there is difficulty in washing out the oncotically active plasma proteins in the infused segments.

The last problem relates to the difficulty of increasing the outflow pressure so that there is net movement from the ascular to the extravascular space.

For segmental brain isolation, establishment of inflow control is via arterial access via the groins external carotid artery 74 or the arm arteries. eral flow is minimised by the use of a collateral, so a co-rail system where one balloon is proximal in the larger vessel and the second one closer to the lesion usually in the same vessel, and infusion proceeds down the central or guidewire channel. Outflow cerebral hypertension can be improved by Trendelenburg or specific obstruction to the internal jugular vein either endovascularly, with occlusive balloon systems, or extravascular occluding system implanted around the internal jugular vein in the neck. This system can be activated and de-activated transcutaneously.

] The plasma proteins and blood are washed out from the segment and replaced by the active y. This may be aided by using hypertonic carrier solution to shrink the elial cells therefore increase the endothelial pore size. Another possibility is to use other carrier substance particularly if a lipophilic agents which traverse the blood brain barrier easier.

Figures 8 and 9 illustrate the s and devices for ar isolation of the present invention applied to the lower limbs 82. Figure 8 illustrates arterial isolation and Figure 9 illustrates venous ion. The site of origin of endoluminal catheters may be on the contralateral limb in the common femoral or auxiliary or even brachial vessels or via an arteriovenous fistula. If the lymphatic systems cause occasion to be treated then controlling systems may position proximal to the lymphatic nodes i.e. the iliac systems.

In some situations implantable extra vascular occlusive s can be used.

The skilled addressee will readily recognise that the methods and devices for vascular isolation illustrated in Figures 8 and 9 are readily applied to the upper limbs.

The skilled addressee will understand that the site of origin of the therapy is an access device 41 at the origin of the common femoral artery 81 or it can be from either or both groins or arms.

Individual control of the profunda vessels or al iliacs or co-rail systems is achieved via use of balloons 24 over a catheter line 22 as described above to isolate the tumour 11. In the embodiment of Figure 8 a balloon 24 is placed in the superficial femoral artery 83. In one embodiment, this is monitored by the appropriate pressure transduction. In the ment of Figure 9 a balloon 24 is placed in the icial femoral vein. Outflow control can be aided by reverse Trendelenberg positioning.

Endovascular balloons either teral or contralateral or quets 42 may be appropriate in some cases and also positive and expiratory pressure can be added.

Any or all of the above mechanisms may be used to control outflow. Plasma and blood removal of oncoticly active material and replacement by therapeutic substances in biocompatible solution, resumption of the normal circulation may be delayed by removing the outflow ction several minutes after the inflow control system.

Control of the profunda vessels can be achieved ipsilaterally or contralaterally.

Figure 10 shows an arterial occlusion balloon positioning arrangement of three te balloon 24 positions of the balloon positioning arrangement 20 for ar isolation of the pancreas 53 through the anterior superior pancreaticoduodenal artery 193, is the anterior inferior pancreaticoduodenal artery 191 and the posterior superior pancreaticoduodenal artery 95. Also shown are the posterior inferior pancreaticoduodenal artery 97, the superior mesenteric artery 194 the gastroduodenal artery 192, the proper hepatic artery 94 and the coeliac axis 44.

Figure 11 shows an example of an inflated mucosal compressive balloon 230 positioned in the um 231 used in an embodiment of the balloon positioning ement 20 of the present invention. Also shown is the or pancreatic duodenal artery 232, its posterior branch 234, and its anterior branch 236. Also shown are the duodenal arteries 238 and the pancreatic branches 240 from the anterior branch 236 of the superior pancreatic duodenal artery 232.

Both the posterior branch 234 and the anterior branch 236 communicate with the posterior and inferior pancreatic duodenal branches 242 which usually arise from the superior mesenteric vessel 244. Balloons 24 are positioned in the splenic origin 252, the superior pancreatic duodenal artery 232 and the superior eric vessel 244, respectively. A pancreatic tumour 254 is shown in the head of the as 256.

The inflated mucosal compressive balloon 230 traverses all four ns of the um 231.

As the pancreas 256 is now isolated, infusion of a herapeutic agent to treat the targeted area (or ) can occur.

] The outer infusion balloon of the mucosaI balloon 230 may be filled with ice water. Ice water has the effect of compressing of the blood vessels of the duodenum and has a secondary effect of prolonging ischemic time by minimising the effects of hypoxia, i.e. "cold ischemic time" is longer than "warm lschernic time". Cold temperature also produces vasoconstriction of the small blood vessels of the duodenum and this also protects against infusion of cytotoxic drugs. The blood vessels in the tumour 254, however, have little or no vasomotive tone owing to the absence of smooth muscle and nerves within the vessel walls. As there is a continuous heating effect from nding structure (albeit minimised due to the decreased blood supply), to maintain the required cold temperature of the balloon 230, a continuous infusion of temperature lled fluid is required to allow constancy of the ambient duodenal temperature.

Varying the PEEP can increase the venous pressure in the liver and portal system so as to minimise leakage of the chemotherapeutic agent into the ic circulation.

Similarly, direct balloon obstruction of the hepatic veins can increase venous pressure.

As tumour vessels do not react to cold in the way that other tissue does, the use of ice water allows targeting of tumour whilst avoiding delivery of therapeutic substances to the duodenum due to the mucosal tissues response to the ice water.

] Figure 11A illustrates the mucosaI balloon 230 in further detail. A multi-channel catheter 192 passes through the mucosaI balloon 230. The mucosaI balloon 230 includes an inner ion balloon 194, adapted to be pressurised, and an outer infusion balloon 196 d to contain or transfer vasoconstrictive agents or cold fluid to surrounding tissue through elution ports 198. Temperature controlled fluid is ed into the inner balloon 194 h aperture 214 in a channel of er 192 and inflation fluid (such as air) is injected into inner n 194 through aperture 216 in a second channel of catheter 192 to inflate and maintain pressure in the inner balloon 194. Therapeutic substances are injected into the space between inner inflation balloon 194 and outer infusion balloon 196 through aperture 224 in a third channel of multi-catheter 192. The therapeutic substances are transferred through elution ports 198 into the nding tissue and the cold temperature assists the targeting of tissue such as tumour tissue.

Figure 12 shows an arterial occlusion balloon positioning arrangement of three separate balloon catheter systems 75, 76, 77 to minimise collateral blood flow and optimise hyperperfusion in the liver. The balloon 78 of the system 75, which is a soft and malleable balloon, has a lumen 79. The balloon 78 s longitudinally beyond the coeliac axis 80 into the aorta 81 and also stretches into the opening of the left gastric artery 82, the splenic artery 83 and the other collateral vessels of the common hepatic artery 84, such as the right gastric artery 85 and right gastroepiploic artery 86 and many small vessels. The n 87 of the system 76 is positioned in the left c artery 88 and the balloon 89 of the system 77 is positioned in the right hepatic artery 90. The two separate catheters 91, 92 for each balloon 87, 89 are capable of being passed through the internal diameter of the lumen 79 provided by the wider catheter 93 for the balloon 78.

The balloon positioning arrangement shown in Figure 12 allows for optimal delivery of therapeutic agents by control of inflow from the common hepatic artery 84 and from collateral vessels. The balloon 78, when inflated, is at least 5 cm long but may be up to 40 cm long to occlude as many collateral vessels as possible. It is malleable to conform to the native vessel (i.e. the common hepatic artery 84) and to protrude partly into the openings of collateral vessels. The lumen 79, which also defines the central guidewire channel, has a larger diameter than guidewire channels of the prior art. As a result, the lumen 79 can act like a stabilising sheath. This will allow the balloon 78 and other such balloons to be used for isolation and occlusion of vessels which branch off very acutely from main vessels.

] A common method for inserting balloon catheter systems into acutely angled vessels involves a guidewire being initially ed into the vessel and then a balloon er system being inserted over the guidewire to the desired position. However, when the guidewire is removed in order to allow for ion of the balloon and uent infusion of therapeutic agents, the uninflated balloon may slip out of the vessel. This problem may be avoided by use of the long collateral balloon 78 shown in Figure 12 in which the lumen 79 acts like a ising sheath, even when the n is uninflated. The guidewire can then be removed, and additional collateral balloon systems can then be inserted through the lumen of the long eral balloon.

Alternatively, the guidewire may be removed after the long collateral balloon is inflated.

In that case, because the balloon 78 is quite malleable and protrudes partly into the gs of collateral vessels, it produces greater frictional resistance forces so that, when the guidewire is removed, the inflated balloon does not slip out of the vessel.

The lumen or central guidewire l of most prior art balloon catheter systems are 0.035 inches or 0.038 inches in diameter. However, the n catheter system 75 ing the balloon 78 is capable of allowing two separate balloon infusion catheter systems to be passed through its lumen which each have a minimum diameter of 0.039 inches.

The balloon oning arrangement shown in Figure 13 illustrates a mechanism of isolation and infusion of the right upper lobe of the lungs 100. The main bronch 101 and the ary vein 102 are shown. The skilled addressee will readily ise that any part or the whole of either lung can be isolated in a similar manner.

Non ventilation of a lung or segment leads to atelectasis or collapse of that lung or segment. Vasoconstriction of the pulmonary arteries follows physiologically in order to shunt blood to aerated segments. The blood flow of tumours are not as responsive to vasoconstriction related to their primitive nature hence the degree of vascular cell activity compared to normal tissue for selective infusion purposes. Some of the blood supply may come from brachial arteries which are less affected. d to the atelectasis the pulmonary venous re increases which may be aided by PEEP.

Consequently the treatment for primary or secondary lung sia in the right upper lung 100 according to the present invention is: (a) induction of atelectasis via non-ventilation by balloon occlusion of bronchus; (b) introduction of super selection catheters 624 with balloon 24 occlusion of the pulmonary artery 103 at the apical segment 104, and the anterior segment 106 from peripheral venous access; (c) t of oncologically active material from the supplying s to the isolated lung lobe or segment; (d) application of PEEP; and (e) infuse active therapy up to a ted pulmonary venous pressure.

The lungs are approximately 450g ) and 400g (left); the right has 3 lobes.

Projected mass ratio advantage in a 75kg patient who is approximately 600 times to a lobe. Collapse of the whole lung can be performed whilst infusion only of an affected segmental part as required by the anatomical distribution of the tumours.

In on to the above discussed applications the balloon positioning arrangement of the present invention can also be used in the following applications.

Head and Neck s This may include tumours of the nasal, pharynx and , the , floor of mouth, sinuses, submandibular glands and malignant areas of the skin and mucous membrane. The usual site of origin of the therapy is a multi-access port at the origin of the external carotid or it can be from either or both groins or arms. Access device is implanted bilaterally for structures receiving close to midline blood supply. Inflow, the main axis is superselected to the target area and controlled with endovascular or extravascular balloon ion systems and in some situations related to the excellent collateral flow a proximal and distal balloon systems (co-rail systems are required to reduce pressures that correspond to the critical closing pressures which are 20mmHg at a pre capillary level).

Other branches of the external d may need to be cannulated depending on the radiological appearance and the pressures obtained after occluding the main axis. Other neighbouring branches of the external carotid may be required to be lled ing the branches of the subclavian vessels such as the costocervical and thyrocervical trunks.

The Outflow Control ] This is achieved by postural vres such as Trendelenberg, positive and expiratory res and occlusive catheters in the internal jugular vein, common facial or anterior jugular vein which may e endovascular or al vessel occluding systems. The venous res are continuously red. Once control of the vessels is contained, the plasma proteins and blood are washed out from the ed t and replaced with the saline containing therapeutic agents. With reestablishment of flow the collateral and main axis arterial inflow may be deflated first and the venous outflow control continues for 5 - 20 minutes to minimise systemic recirculation.

Vascular Isolation and Onconic Manipulation of Lesions in the Pelvis This may include lesions in the bladder, rectum, vagina, anal canal, prostate, uterus, cervix, lymphatics and other primary or secondary lesions. The site of origin of the ers are the vascular access systems located in one or other or both groins may include the common l, superficial femoral systems and similarly the venous access system located in the common femoral, superficial femoral, external and iliac vein. Occasionally control of the great saphenous vein is required. The actual inflow may be controlled at two levels with superselection of the target organ e.g. the inferior vesical artery for prostate lesions with another balloon which controls the origin of the internal iliac system. As these organs receive blood flow bilaterally, synchronous control of the contralateral main axis with election can be achieved by guiding catheters placed rade over the bifurcation of the aorta. The pressures monitored are the superselected end pressures transduced on both sides individually and then er and similarly the collateral res again measured unilaterally then bilaterally. These measurements determined the need for simultaneous contralateral flow control. In some cases embolisation of significant collateral s may be required to obtain adequate inflow pressure reductions.

Outflow l Outflow control is achieved by simultaneous occlusion of the internal, external or selected pelvic vein, iliac vein or veins. Elevation of the venous outflow pressure may be achieved by both postural manoeuvres (head up) and in addition to the positive and expiratory pressure (PEEP).

Oncotic Manipulation The blood is removed from the isolated organ to be treated and replaced with the appropriate chemotherapeutic or other form of treatment in hypo-oncotic solution.

To maximise retention the venous res remain elevated by all means for 5-20 minutes after the resumption of normal arterial flow.

Methods of Isolation and Fluid Flux Control to the Pancreas The main axis arterial inflow is controlled by catheters and balloons in the common hepatic with superselection of the gastroduodenal or superior pancreaticoduodenal. Other lesions in the pancreas may require the splenic vessels or pancreatic magna to be the main axis control system and occasional superselection of the or pancreaticoduodenal is ed. The collateral control is via balloon systems controlling the gastric the gastroepiploic, hepatic vessels and the splenic artery depending on the site of target tumour.

Venous Obstruction This is obtained by positive and expiratory re (PEEP) as well as an extra ar occlusive device nding the portal vein or in some cases the splenic vein.

The hepatic veins may also require control via balloons. This degree of occlusion controlled transcutaneously, radiologically. After vascular isolation the plasma proteins and blood are washed out from the isolated segment and replaced with saline ning the chemotherapeutic agent. Monitoring of the eral as well as the main axial pressures and radiologically the placement of the appropriate catheters is mandatory. Offline measurement of chemotherapeutic activity and levels is also helpful with management and in some cases a method shielding of the surrounding mucosa can be obviated by the use of cold infusions in the stomach and duodenum and first part of the duodenum g reactive vasoconstriction and minimal blood flow.

In Vascular Isolation and Manipulation of Flux of Lesions in the Breast Inflow Control The access system is implanted in either arm in the brachial vessels or the groin. For medial lesions, the internal mammary is superselected and occluded and prepared for infusion. In lateral lesions the lateral ic vessel is superselected. In some rare cases the medial and l pectals can be isolated with 2 balloons proximal and distal to their origins. Collateral vessels, the other vessels that are not superselected i.e. the internal mammary, medial and lateral pectoral, thyrocervical trunk, costocervical trunk, and lateral thoracic vessels have occluded as required depending on the site of lesion. One single or two balloons are often sufficient to occlude all collateral inflow with riate re reduction.

Outflow The w cannula’s originate from the brachial and occlude all of the tributaries of the subclavian and axiliary vessels. Therefore the l thoracic vein, the medial and lateral pectoral veins, the veins from the thyrocervical and costcervical trunks and internal mammary vein are all occluded simultaneously. Any venous and arterial pressures are monitored both in the main axis and collateral res. The arterial systems are then occluded, the plasma proteins are then washed out and then the outflow balloons are inflated and the closed segment is replaced by saline containing the therapeutic agents.

Reconstitution Is release of the collateral balloons first the main axial balloon and then followed by the venous outflow occlusive systems which are deflated 5–20 minutes after an arterial titution to minimise therapy entering the systemic circulation.

Upper Limb Site of origin of the catheters/balloons access system depends upon the site of the original lesion and associated lymphatic drainage and in some cases may originate in the groins. In proximal the inflow l system is placed on the al side i.e. the c side of the lesion. This may include a double inclusion of the main axis or the use of a fistula to control inflow to the lesion.

Collateral Flow Control This may involve proximal and distal ns in the main axis selective occlusion of radial, ulnar interrosseousor circumflex humeral vessels ing on the site of the lesion and the result of the pressure transduction recordings. w Control Positive and expiratory pressure, posture and balloons placed on the cardiac side of the lesion as well as l of the appropriate tributaries to the main venous return axis. These vessels may be the brachial auxiliary or subclavian s.

Replacement of the blood with biocompatible solutions containing the appropriate therapy. Resumption of circulation, venous outflow may be deflated several minutes after the inflow control system to minimise re-circulation of active therapeutic agents into unwanted areas.

Broadly, with reference to Figures 17 to 24 an embodiment of the present invention relates to a blood vessel access device with a chamfered end to eliminate the on of dead space when the cannula is inserted into a blood vessel.

Figures 14, 15 and 16 show prior art single lumen access devices. The access device 410 shown in Figure 14 has a cannula 411 with adaptor ports 412, and the a 411 is connected to a patient’s blood vessel 413 at a perpendicular angle (90°).

In this way, a tip 414 of a stem of a plunger 415 within the cannula 411 can be slid far enough towards a proximal end of the cannula so that the tip 414 reaches a point where the proximal end of the cannula is level with the wall of the blood vessel, thereby preventing the g of the patient’s blood into the cavity or lumen 416 of the cannula.

As a uence, there is no dead space between the plunger tip 414 and the blood vessel 413 when the cannula 411 is connected to the patient’s vessel at a perpendicular angle.

However, as shown in Figures 15 and 16, when a cannula 417 with an is ted to the patient’s vessel at a non-perpendicular angle (say 30°), the regular cylindrical shape of the tip 414 of the plunger may create a protrusion 418 into the lumen of the vessel (see Figure 15) or, if the tip 414 is retracted into the cannula to eliminate the protrusion, a dead space 419 is then created within the lumen of the cannula which will be filled with a small amount of blood (see Figure 16). Both the protrusion 418 and the dead space 419 can cause or contribute to haemodynamic bances or ence within the patient’s circulatory system that may result in thrombotic events. The amount of dead space or protrusion, when present, will vary according to the site of remote , e.g. axillary, femoral, iliac, or jugular vessels.

The plunger 420 shown in s 19 and 20, which is for use with the cannula 421 of the present invention shown in Figures 17 and 18 to form the single lumen access device, avoids this problem by having a chamfered tip 422 or proximal end configured such that the angle made between the plane of the chamfer of the tip 422 and the longitudinal axis of the r 420 is identical to the angle made between the longitudinal axis of the cannula 421, through which the plunger stem travels, and the wall of the patient’s vessel connected by the cannula 421. The plunger 420 acts to stop the flow of blood up the cannula 421. Blood flow up the cannula 421 can cause a thrombosis.

In one embodiment, the plunger 420 can include an internal lumen (not shown) running its entire length. The internal lumen can be plugged by a second plunger. The second plunger can removed to allow the provision of material through the internal lumen As shown in Figures 17 and 21, the a 421 has a proximal graft end 423 which has the same chamfered angle as that of the r tip 422 and a body portion 432 within which the plunger stem 424 sits. When the plunger stem 424 is slid down the body portion 432 of the cannula 421, the plane of the chamfer of the plunger tip 422 will be parallel with the patient’s vessel wall 428, preventing dead space and thus reducing the likelihood of thrombotic events.

As shown in the sectional end views of Figure 18 and Figure 20, the inner walls 425 of the body portion 432 of the cannula 421 are so contoured as to mateably correspond with the contour of the outer walls 426 of the plunger stem 420, thereby enabling the plunger stem 424 to, during its passage through the cannula 421, be guided in such a way that the chamfered es of the proximal ends or tips 122, 123 of the plunger stem and cannula are correctly aligned. When the a 421 is connected to a patient’s blood vessel at a non-perpendicular angle, and the plunger stem 424 is slid down the cavity 427 of the cannula 421, the ent provided by the corresponding contoured walls 425, 426 mentioned above ensures that the chamfered surface of the plunger tip 422 will be parallel and in line with the vessel wall 428 so as to prevent any dead space within the lumen 427 of the cannula 421 or any sion into the vessel lumen. ynamic disturbances that could result in thrombotic events will be prevented by this feature, and this will allow the access device to be used for a longer implant period without reducing its safety.

Figure 22 shows a sectional view longitudinally of the cannula 421; whilst Figure 23 shows in sectional detail how a connector assembly 429 interconnects a proximal graft end portion 430 of the a 421 to an nt end portion 431 of a main body 432 of the cannula 421. Figure 24 shows in sectional detail how a connector assembly 433 is connected to a distal end portion 434 of the main body 432 of the cannula 421. The connector assembly 433 enables connection to a medical supply device such as a multiport adaptor, a pump, a drug supply, a radiation supply or otherwise.

With reference to Figure 21A, an ative to the use of cannula 421 with a plunger stem 424 is shown. Instead second plunger stem 420A is used to stop the flow of blood up the lumen of the cannula 421 is used. The second plunger stem 420A includes passageway 422A along its length. The passageway 422A includes a one way valve 423A to allow injection of material into the a 421 whilst stopping fluid and particulates flowing into the passageway 422A from the cannula 421.

The blood vessel access device with a chamfered end of Figures 14 to 24 provides an access device for the catheters 22 and balloons 24 for the ion and therapeutic treatment of a region of the body or organ ad sed above.

Broadly, with reference to Figures 25 to 30 an embodiment of the present ion relates to a multiport adaptor device for facilitating the insertion of multiple catheters into a single cannula lumen.

The multiport adapter 235 shown in s 25 to 27 has a unitary end port 236 that is adapted to be connected onto the tor assembly 233 at the distal end portion 234 of the cannula 421 of Figures 17 to 24. The r 235 has a branched portion 237 which diverges into three tubes, to each of which is releasably connected an item of external tubing 238, 239, 240 having respective outer ports 241, 242, 243 that are designed to fit other medical devices with a male luer lock medical fitting of the type described in US 5,047,021. The skilled addressee will recognise that alternative connection means may be used to be used to connect the outer ports 241,242, 243 to other medical devices. Such medical devices may be haemostasis valves (see US 5,195,980; EP 0875262; US 6,22,1057), medical three-way stopcocks (see US 7,914,495), and syringes (see US 109). The adapter 235 can also receive catheters 44 and balloons 45 of three balloon catheter s which all pass through the lumen of the cannula 421 and which are used in vascular ion systems and to allow improved and enhanced communication with the patient’s circulatory system.

As shown in the embodiment of Figure 25A a multiport adaptor 225 is shown.

The ort adaptor 225 includes four tubes 541, 542, 543, 543 that are flexible and serve to act as a guide for the placement of catheters placed through the different tubes. The flexible tubes 541, 542, 543, 544 allow independent steerage for the placement of the catheters h feeder connection port 545 where moving one flexible tube only affects one catheter without impacting other catheters. The tubes 541, 542, 543, 544 have their distal ends connected to outer ports 546, 547, 548, 549.

In an alternative embodiment multiport adaptor es more than three tubes.

In yet a further alternative embodiment, the plurality of tubes of the ort adaptor are located within a unitary body to fix the location of the tubes with respect to each other.

The skilled addressee will recognise that alternative tion mechanism to a male luer lock can be used and still fall within the scope of the present invention.

The vascular isolation systems introduced into the patient’s circulatory system are then used to control or even occlude the blood flow through the vessels 246 to and/or from an organ or a segment thereon. The adaptor 235 serves as an extracorporeal component of the access device. Where a ity of smaller cannulas 44 are fed through the ort adaptor 235 into the cannula 221 each of the r cannulas 44 can be directed to different positions to occlude or control the blood flow.

Figures 28 to 30 show the implantable cannula 421 of Figures 17 to 24 connected at its distal end to the unitary end port 236 of a multiport adaptor 247 which is similar in structure and function to that shown in Figures 25 to 27. Figure 30 shows the cannula 421 connected directly to the wall 228 of a patient’s artery or vein. The ort adaptor 247 also diverges to form a plurality of outer ports provided with ISO standard fluid/gas tight tions suitable for vascular ations. Three catheters 244 and ns 245 all pass through the lumen of the implantable cannula 421 via the outer ports of the multiport adaptor 247, and the balloons 245 occlude blood flow through the vessels 246.

The function of the multiport adaptor 235, 247 in facilitating the insertion of onal devices through the lumen of the implantable cannula 421 allows for multiple endovascular devices, such as catheters and balloons (hereinafter referred to as "ballooncatheters", to be introduced simultaneously into the patient’s ature via the implantable cannula. These endovascular devices can then be used simultaneously to administer treatments in a variety of ways.

An e of a possible treatment involves the vascular isolation of organs or anatomical s of the human body, including but not limited to the liver, pancreas or pelvic organs. In this example, multiple cannulation systems ing balloons and catheters are inserted into the patient’s vasculature using the implantable cannula 421 and multiport adaptor 235, 247 and subsequently positioned in the es supplying blood to the target area or lesion. The balloons of these balloon catheter systems are then ed, cutting off or occluding the arterial inflow to the target area and establishing an isolated zone of significantly reduced blood inflow. This ed zone allows for infusion of therapeutic agents into the target area whilst minimizing systemic re. Vascular isolation may be further enhanced by using a separate access device to locate additional balloon catheter systems in the veins so as to occlude venous outflow from the target area or lesion, or by using ve end expiratory re (PEEP).

With reference to Figures 31 to 35, external vascular fistula devices 300, 315, 320 according to an embodiment of the present invention are shown. These fistula devices 300, 315, 320 allow ed sterile access to the arterial and venous side of the circulation without interruption of the flow of blood through the fistula devices 300, 315, 320. In addition , the connector can be removed and replaced ing arterial and venous control. The device allows ng of blood without separate venous re.

This capability improves the quality of life of cancer patients on chemotherapy who require a great deal of testing to particularly look at the haematological effects of the chemotherapy. The device allows catheter insertion for continuous remote intra-arterial or intravenous infusion for delivery of chemotherapy, stem cells or nano particles or antibiotics. The system may also have a catheter loop within itself for example for real time recognition of cell type. A catheter is inserted into the arterial side of the fistula devices 300, 315, 320 and this traverses a device which immediately recognises cell type in real time and then delivers the blood back into the venous system without interruption of fistula flow. A r system is extraction via the venous part of the a devices 300, 315, 320 and re-insertion via a pump into the arterial system; this is known as remote closed loop recirculation. This is appropriate in some forms of chemotherapy, particularly if detoxification is required. The device is also appropriate for repetitive diagnostic angiography by insertion of a catheter into the arterial venous side as required. The device construction addresses safety issues with ially minimal chance of spontaneous dislocation and tampering.

In fistulae, in the past the venous system may o intimal hyperplasia with the gradual reduction of flow and eventual inclusion. This may or may not be treatable with appropriate angioplasty or ion. Under these circumstances the fistula device 300, 315, 320 is compatible with both of the arterial and venous ar tube and therefore allows the access to be continued by plugging the tube with a plunger i.e. if necessary the access device can be removed and replaced by plungers in either or both access tubes.

Alternatively, a previous single intra-arterial device can be converted into a fistula device 300, 315, 320 if the access to the other side of the circulation is required.

Referring to Figure 31, an external fistula device 300 is shown. The external fistula device 301 includes a bridging device 307 designed to connect to arterial cannula 303 and venous cannula 305. The bridging device 307 acts to provide a passageway 310 n the arterial cannula 303 and venous cannula 305 to allow blood to flow through. The bridging device 307 includes engagement means 309 to fix the bridging device 307 to the arterial and venous cannulas 303, 305. The engagement means 309 can be in the form of a screw thread, a clip, a snap fit or otherwise and understood by the skilled addressee. The passageway 210 of the bridging device 307 sealingly engages with the passageways of the arterial and venous cannulas 303, 305 at ment point 311. Engagement point 311 includes a seal to stop e of blood passing into or from the bridging device.

An access portal 301 is located on the bridging device 307 to provide access to the arterial and venous cannulas 303, 305. The access portal 301 feeds directly into the passageway 210 allowing catheters to be fed into either or both of the arterial side or venous side of the fistula connection. This ement allows for repeated catheterisation through access portal without needing to compromise the connection between the arterial and venous cannulas. ing to Figure 32, an alternative external fistula device 315 is shown connected to arterial cannula 303 and venous cannula 305. As with the embodiment of Figure 31, a bridging device 313 with eway 310 is used to connect the arterial and venous cannulas 303,305 er. Connection devices 319 sealingly fix the bridging device 313 to the arterial and venous as 303, 305. The bridging device includes both arterial side access portal 317 and a venous side access portal 318.

Arterial access portal 317 is used to insert catheters through the arterial cannula 303 into an artery. Venous access portal 318 is used to insert a catheter through the venous a 305 into a vein. Seals at the top of arterial access portal 317 and venous access portal 318 allow repeated catheterisation through the bridging device without needing to puncture es or veins.

] Figure 33 illustrates the al access portal 317 of Figure 32. A catheter is inserted through seal 323 h passageway 321 into arterial cannula 303.

Figure 34 illustrates an alternative external fistula device 320. As with the previous embodiments tion means 327 fix the external fistula device 320 to the arterial and venous cannulas 303, 305. Arterial access portal 322 includes a seal and is arranged to receive a catheter for insertion to an artery. Venous access portal 324 includes a seal and is arranged to e a catheter for insertion to a vein. The connection means can be in the form of a threaded screw mean, a clip, a clamp or otherwise as tood by the skilled addressee. The arterial and venous access portals 322, 324 are arranged for repeated use so that ers can be easily inserted and removed. In one embodiment the T arterial and venous access portals 322, 324 include a pierceable membrane.

In one embodiment the external fistula device is le.

With reference to Figure 35, the ative external fistula device 320 of Figure 34 is shown with catheters inserted into an artery and vein via the arterial and venous access portals 322, 324.

Figure 36 illustrates a scenario where the alternative external fistula device 320 has been removed from the connection between arterial and venous cannulas 303, 305 g into artery 333 and vein 335. A plunger 337 is placed h connection means 327 into venous cannula 305 to plug the venous blood. Multiport adaptor 35 is connected to al cannula 303 to allow insertion of ers 44 and ns 45.

This allows for the occlusion of arteries and the isolation of organs to use the method discussed above for therapeutic treatment.

With reference to Figure 37 and 38, an al fistula device 350 is illustrated.

The external fistula device includes an internal tube 351.

In the embodiment of Figure 37, a first constriction device 353 engages the outer housing 354 of the external fistula device 350. A constriction control element 355 passes into the external fistula device and engages the internal tube 351. The constriction device applies force to the inner tube and constricts a reduced diameter portion 356 of the internal tube 351. The constriction device 353 can apply side to side constriction of the internal tube 351. Alternatively, the constriction device 353 can apply circumferential constriction to the internal tube. The constriction device 353 can apply with a screw, hydraulic, pneumatic means or otherwise as understood by the skilled addressee.

In the embodiment of Figure 38 similar elements as present in Figure 38 have been given the same numbering. A second constriction device 357 is placed around the outer housing 354 of the external fistula device 350. The second constriction device 357 icts both the outer housing 354 and the internal tube 351 at constricted region 359 of the external fistula device 350. The constriction can be either side to side or circumferential and is lled by control element 361 which is a screw, hydraulic, tic means or otherwise as understood by the skilled addressee.

] For both the ments of Figures 38 and 39, the constricted internal tube 351 allows control of the flow rate of fluid h the fistula.

The following n comprises numbered s which are not claims, but are additional statements describing particular embodiments of the invention: Clause 1. A device comprising: a method of delivering a therapeutic substance for treatment to a region of the body through vascular ion and manipulation of fluid flux into and from the region of the body including the steps of: restricting vascular inflow to the region of the body; washing out oncotically active plasma proteins from the region of the body by increasing the outward oncotic pressure gradient from the region of the body; inducing ischemia in the region of the body; controlling the pressure and fluid flow of the main blood vessels to and from the region of the body; providing the therapeutic substance to the region of the body when the fluid flow to the region of the body is controlled.

Clause 2. The method of Clause 1, wherein the region of the body is an organ.

Clause 3. The method of Clause 1 or 2, wherein pressure through the vascular inflow is controlled to be less than or equal to 20mmHg.

Clause 4. The method of Clause 3, wherein the pressure h the vascular inflow is controlled to induce critical capillary closure.

Clause 5. The method of any one of the ing clauses, wherein the oncotically active plasma proteins are washed out at between 28mmHg to 35mmHg.

Clause 6. The method of any one of the preceding clauses, wherein outflow of the therapeutic substance from the region of the body is occluded using positive end expiratory pressure.

Clause 7. The method of any one of the preceding clauses, wherein outflow of the therapeutic substance from the region of the body is controlled using relative movement of limbs of the body.

Clause 8. The method of Clause 7, wherein w of the therapeutic substance from the region of the body is controlled using Trendelenburg or anti lenburg movements.

Clause 9. The method of any one of the preceding clauses, wherein the therapeutic substance is erfused into the region of the body.

Clause 10. The method of Clause 9, wherein the hyperperfusion is provided at less than or equal to 35mmHg.

Clause 11. The method of any one of the ing s, wherein the occlusion of vascular flow is achieved with multi balloon catheter line insertion to at least one of the blood vessels surrounding the target area.

Clause 12. The method of any one of the preceding s, wherein the therapeutic treatment includes at least one of chemotherapy, supply of nanoparticles, stem cells, immunotherapy and or gene therapy.

Clause 13. The method of any one of the preceding clauses, wherein the manipulation of fluid flux includes at least one of occlusion of flow, partial occlusion of flow, isoperfusion or hyperperfusion of the main axial vessels to the target area.

Clause 14. The method of any one of the preceding clauses, wherein the manipulation of fluid flux is achieved with at least one of scular or extravascular devices.

Clause 15. The method of any one of the preceding clauses, ing assessing and modulation of the fluid pressure of fluid within the blood vessels according to infusion.

Clause 16. An assembly for delivering a therapeutic treatment to a region of the body through vascular isolation and manipulation of fluid flux into and from the region of the body ing: a first occlusion device adapted to restrict vascular inflow to the region of the body; a second occlusion arrangement to restrict vascular outflow from the region of the body; wherein the first occlusion device is adapted to increase the outward oncotic pressure gradient from the region of the body to wash out oncotically active plasma proteins from the region of the body so as to leave the region of the body in a state of ischemia an injection device arranged to e a therapeutic substance for the therapeutic treatment when the region is in ia; and a removal device arranged to remove the therapeutic substance from the region of the body.

Clause 17. The assembly of Clause 16, wherein the region of the body is an organ.

Clause 18. The assembly of Clause 16 or 17, wherein the first occlusion device is arranged to control pressure through the ar inflow to be less than or equal to 20mmHg.

Clause 19. The assembly of Clause 18, wherein the re through the vascular inflow is controlled to induce critical capillary closure.

Clause 20. The ly of any one of Clauses 16 to 19, wherein the oncotically active plasma proteins are washed out at between 28mmHg to .

Clause 21. The assembly of any one of Clauses 16 to 20, wherein outflow of the therapeutic substance from the region of the body is occluded using positive end expiratory pressure.

Clause 22. The assembly of any one of the preceding clauses, wherein outflow of the therapeutic nce from the region of the body is controlled using ve movement of limbs of the body.

Clause 23. The assembly of Clause 22, wherein outflow of the therapeutic substance from the region of the body is controlled using Trendelenburg or anti Trendelenburg.

Clause 24. The assembly of any one of Clauses 16 to 23, wherein the eutic substance is adapted to be hyperperfused into the region of the body through a catheter.

Clause 25. The method of Clause 24, wherein the hyperperfusion is provided at a pressure below the venous outflow pressure from the region of the body.

Clause 26. The method of Clause 25, wherein the hyperperfusion is provided at less than or equal to 35mmHg.

Clause 27. The method of any one of Clauses 1 to 15, including the steps of: delivering the therapeutic treatment to an interstitial space where tumour cells reside, or to the necrotic centers of tumours along an oncotic gradient penetrating capsule following an oncotic gradient; providing fluid that traverses the lymphatics and delivers treatment to lymph nodes; and repeating delivery of therapeutic treatment over time may target cells that are not dividing at one particular ent cycle.

Clause 28. A method of venous and lymphatic w control of a region within the body wherein the outflow control is achieved with an endovascular occlusive balloon or partial occlusive balloon and external utaneous extravascular occluder, positive end expiratory pressure ational forces.

Clause 29. The method of Clause 28, wherein the positive end pressure gravitational forces are lenberg or anti lenberg postural manoeuvres.

Clause 30. A vascular access device for ged use including: a chamfered cannula including a chamfered cannula end arranged to engage with a blood vessel at an angle; and a removable plunger arranged to block and seal a lumen of the cannula; n the removable plunger includes a chamfered end arranged to eliminate dead space within the cannula when the plunger is fully inserted in the cannula to block the lumen of the cannula.

Clause 31. The vascular access device of Clause 30, wherein the red end of the removable plunger is arranged so that it does not protrude into the blood vessel when the plunger is fully inserted into the cannula to block the cannula.

Clause 32. The vascular access device of Clause 30 or Clause 31, wherein the chamfered cannula end and the chamfered end of the plunger have the same chamfered angle.

Clause 33. The vascular access device of any one of Clauses 30 to 32, wherein the cannula includes an inner wall profiled to mateably correspond to outer stem wall of the plunger.

Clause 34. The vascular access device of Clause 33, wherein the inner wall of the cannula is profiled so that the plunger cannot rotate due to the mateable correspondence with the outer stem wall of the plunger.

Clause 35. The vascular access device of Clause 33 or Clause 34, wherein projections of the outer stem wall of the plunger are ed to be received in recesses in the inner wall of the cannula.

Clause 36. The ar access device of any one of Clauses 33, 34 or 35, wherein the mating correspondence of the cannula inner wall and the plunger outer wall are arranged so that the chamfered cannula end is parallel with and aligned with the chamfered end of the plunger when the plunger is fully inserted in the cannula.

Clause 37. The ar access device of any one of Clauses 30 to 36, wherein the cannula includes a graft end arranged to engage with a blood vessel and a body n, wherein the graft end is arranged to connect with the body portion.

Clause 38. The vascular access device of Clause 37, wherein the cannula includes a connector assembly distal to the graft end arranged to connect to a medical supply device.

Clause 39. The vascular access device of Clause 37 or Clause 38, wherein the connector assembly is arranged to connect with the body portion.

Clause 40. A multiport adaptor for a cannula system including: a plurality of tubes feeding into a central lumen; wherein the central lumen is arranged to connect to a main cannula line that is arranged to connect to the vasculature.

Clause 41. The ort adaptor of Clause 40, wherein the plurality of tubes can be used to provide a ity of as into the vasculature via the central lumen.

Clause 42. The multiport adaptor of Clause 41 n the plurality of cannulas is used to create a anastomosis in the vasculature.

Clause 43. The multiport adaptor for a cannula system of any one of Clauses 40, 41, or 42, n each of the plurality of tubes is arranged to e and feed a guide wire into the central lumen.

Clause 44. The multiport catheter of any one of Clauses 40 to 43, wherein the plurality of tubes are flexible and arranged so that lumens in each of the tubes do not intersect.

Clause 45. The multiport r for a cannula system of Clause 43, wherein the guide wires are arranged to be fed into the vasculature individually or together.

Clause 46. The multiport adaptor for a a system of Clause 43 or Clause 45, wherein the guide wires are arranged to include balloons.

Clause 47. The multiport adaptor for a cannula system of any one of Clauses 43, 45 or 46, wherein the guide wires are arranged to be directed to inflow and outflow vasculature bodies of a particular region so that the particular region can be ed with medical devices associated with the guide wires.

Clause 48. The multiport adaptor for a cannula system of any one of Clauses 40 to 48, n each of the plurality of tubes is arranged to t an external medical device.

Clause 49. The multiport adaptor for a cannula system of Clause 48, wherein the plurality of tubes are arranged to connect to the external medical device with a luer lock.

Clause 50. The multiport r for a cannula system of in Clause 48, wherein the ity of tubes are arranged to provide a plurality of endovascular devices into the ature simultaneously.

Clause 51. An external arterio venous fistula connection arranged to connect between an arterial cannula and a venous cannula including an arterial connection means arranged to sealingly connect to the arterial a venous connection means arranged to sealingly connect to the venous cannula to create a sealed passageway and at least one reusable access portal; wherein the access portal is arranged to receive a catheter for insertion into the vein connected to the venous cannula or artery connected to the arterial cannula.

The external o venous fistula connection of Clause 51, including a reusable arterial access portal arranged to receive a catheter for insertion into the arterial cannula and a venous access portal arranged to receive a catheter for insertion into the venous cannula.

Alterations and cations to the Embodiments Various additions, cations and substitutions regarding design and construction can be made without departing from the spirit and scope of the invention.

Modifications and variations such as would be apparent to the skilled addressee are considered to fall within the scope of the present invention. The present invention is not to be limited in scope by any of the specific embodiments bed herein. These embodiments are intended for the purpose of exemplification only. Functionally equivalent products, formulations and methods are clearly within the scope of the invention as described herein.

Reference to positional descriptions, such as lower and upper, are to be taken in context of the embodiments depicted in the figures, and are not to be taken as limiting the invention to the literal interpretation of the term but rather as would be understood by the skilled see.

] Throughout this ication, unless the context requires otherwise, the word "comprise" or ions such as "comprises" or "comprising", will be understood to imply the inclusion of a stated integer or group of integers but not the exclusion of any other integer or group of integers.

Claims (24)

CLAIMS :

1. An external arterio-venous fistula connection arranged to connect and provide ation between an arterial cannula and a venous cannula to allow repeated sterile access to the arterial and venous side of the ation without interruption of the flow of blood sing: an arterial connection means arranged to sealingly connect to the arterial cannula; a venous connection means arranged to gly connect to the venous cannula to create a sealed passageway; and at least one reusable access ; wherein the access portal is arranged to receive an endovascular device for insertion either into the vein connected to the venous cannula or into the artery connected to the arterial cannula.

2. The al arterio-venous fistula connection of claim 1 comprising a reusable arterial access portal arranged to receive an endovascular device for insertion into the arterial cannula and a venous access portal arranged to receive an endovascular device for ion into the venous cannula.

3. The external arterio-venous fistula tion of either claim 1 or claim 2 ured to provide sampling of blood without separate venous puncture.

4. The external arterio-venous fistula connection of any one of the preceding claims configured to allow catheter insertion for continuous remote intra-arterial or intravenous infusion of a therapeutic treatment.

5. The external arterio-venous fistula connection of any one of the preceding claims further comprising a catheter loop for real time recognition of cell type.

6. The external arterio-venous fistula connection of claim 5 wherein the catheter loop comprises a er inserted into the arterial side of the fistula connection; a device for recognising the cell type and to deliver blood back to the venous system without interrupting the blood flow in the fistula connection.

7. The external arterio-venous fistula connection of any one of the preceding claims further comprising a plunger configured to engage either the venous connection or the arterial connection to seal the respective tion or connections.

8. The external arterio-venous fistula connection of any one of the preceding claims r comprising a bridging device to connect the venous a and the arterial cannula.

9. The external arterio-venous fistula connection of claim 8 wherein the bridging device comprises a passageway between the arterial cannula and venous cannula 305 to allow blood to flow through.

10. The external arterio-venous a connection of either claim 8 or claim 9 wherein the passageway sealingly engages with the passageways of the arterial and venous cannulas.

11. The external arterio-venous fistula connection of any one of claims 8 to 10 wherein the bridging device comprises engagement means to fix the bridging device to the arterial and venous cannulas at an engagement point.

12. The external arterio-venous a connection of any one of claims 8 to 11 n the engagement point includes a seal to stop leakage of blood passing into or from the bridging device.

13. The external arterio-venous fistula connection of any one of claims 8 to 12 further comprising an access portal located on the bridging device to provide access to the arterial and venous as.

14. The external arterio-venous fistula connection of any one of claims 8 to 13 wherein the access portal feeds directly into the passageway ng ers to be fed into either or both of the arterial side or venous side of the fistula connection.

15. The external arterio-venous a connection of any one of claims 8 to 13 further comprising connection devices configured for gly fix the bridging device th the arterial and the venous as.

16. The external arterio-venous fistula connection of any one of claims 8 to 13 wherein the bridging device further comprises an arterial-side access portal and a venous-side access portal.

17. The external arterio-venous fistula connection of claim 16 further comprising seals configured to engage the arterial access portal and the venous access portal.

18. The external arterio-venous fistula connection of claim 17 wherein the arterial and venous access s comprise a pierceable membrane.

19. The external arterio-venous fistula connection of any one of the preceding claims wherein the fistula connection is le.

20. The external arterio-venous fistula tion of any one of the preceding claims comprising an internal tube.

21. The external arterio-venous fistula connection of claim 20 comprising: an outer housing; a first constriction device configured to engage the outer housing; and a constriction control element configured to pass into the fistula connection and engage the internal tube.

22. The external arterio-venous fistula connection of claim 21 wherein the iction control element is configured to apply force to the internal tube to constrict a d diameter portion of the internal tube.

23. The external arterio-venous fistula connection of either claim 21 or claim 22 comprising a second constriction device around the outer housing.

24. The al arterio-venous fistula connection of claim 23 wherein the second constriction device is configured to constrict both the outer housing and the internal tube.