US20040249335A1

US20040249335A1 - Implantable arteriovenous shunt device

Info

Publication number: US20040249335A1
Application number: US10/820,169
Authority: US
Inventors: John Faul; Toshihiko Nishimura; Peter Kao; Ronald Pearl
Original assignee: Leland Stanford Junior University
Current assignee: Leland Stanford Junior University
Priority date: 2003-04-08
Filing date: 2004-04-06
Publication date: 2004-12-09
Also published as: EP1613373A1; US20050107733A1; WO2006041824A3; US7628768B2; US20090156978A1; WO2006041824A2; EP1613373A4; US20120010556A1; US8048016B2; WO2004091696A1

Abstract

A long-term implantable arteriovenous shunt device is provided that can be used as a therapeutic method. The shunt device is implanted between an artery and a vein, preferably between the aorta and the inferior vena cava. The shunt device decreases the systemic vascular resistance and allows a blood flow rate through the shunt device of at least 5 ml/min after the implantation. The blood flow rate could be controlled either via an open loop or a closed loop control means. The shunt device could also be a self-adjustable shunt device to self-adjust its structure to control the blood flow rate through its lumen. Based on the effects of the shunt device to the respiratory, cardiac and circulatory system, the implantable shunt device could be beneficial as a therapy to patients with problems or conditions related to these systems.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is cross-referenced to and claims priority from U.S. Provisional Application 60/461,467 filed Apr. 8, 2003, which is hereby incorporated by reference.[0001]

FIELD OF THE INVENTION

The present invention relates generally to medical devices and methods. More particularly, the present invention relates to non-cardiac devices and methods that provide a fistula or lumen between the arterial system and venous system.

BACKGROUND

Chronic obstructive pulmonary disease affects millions of patients in the United States alone. The present standard of care is oxygen therapy, which requires a patient to remain near a stationary oxygen source or carry a bulky portable oxygen source when away from home or a treatment facility. It is easy to appreciate that such oxygen therapy has many disadvantages.

Lung reduction surgery has recently been proposed for treating patients with chronic obstructive pulmonary disease. Such surgery, however, is not a panacea. It can be used on only a small percentage of the total patient population, requires long recovery times, and does not always provide a clear patient benefit. Even when successful, patients often continue to require supplemental oxygen therapy.

For these reasons, it would be desirable to provide improved approaches, including both devices and methods, for treating patients suffering from chronic obstructive pulmonary disease. It would be desirable if such devices and methods were also useful for treating patients with other conditions, such as congestive heart failure, hypertension, hypotension, respiratory failure, pulmonary arterial hypertension, lung fibrosis, adult respiratory distress syndrome, and the like. Such devices and methods should provide for effective therapy, preferably eliminating the need for supplemental oxygen therapy in the treatment of chronic obstructive pulmonary disease. After the procedures, such devices and methods should optionally be adjustable so that the degree of therapy is responsive to the patient's needs at any particular time. At least some of these objectives will be met by the invention described hereinafter.

SUMMARY OF THE INVENTION

The present invention is a long-term implantable arteriovenous shunt device that can be used as a therapeutic method. The shunt device is implanted between an artery and a vein, preferably between the aorta and the inferior vena cava. The shunt device is implanted for a long-term period of at least 6 weeks and the implantation could be established via an open surgical procedure, a minimally invasive surgical procedure, or an intravascular procedure.

The objective of the shunt device is to decrease the systemic vascular resistance and allow a blood flow rate through the lumen of the shunt device of at least 5 ml/min after the implantation. The cross sectional area (or radius) and the length of the lumen of the shunt device are selected to having such a blood flow rate, with the cross sectional area in the range of about 19 mm ²to about 750 mm², the length in the range of about 2.5 mm to about 15 mm, and the radius in the range of about 2.5 mm to about 15 mm. In one embodiment, the inner wall of the shunt device has a coating to prevent clot formation or atheroma formation.

In some situations it might be desirable to control the blood flow rate. Therefore, the present invention includes a control means to control the blood flow rate through the shunt at a desirable blood flow rate level or range. The control means could be as simple as an on/off mechanism (or switch), or could be more sophisticated by regulating the rate of flow ranging from either an open loop control or a closed loop control with feedback provided by physiological parameters. For each level of sophistication, the control means could include a controller (ranging from a switch to a decision algorithm), one or more flow control elements that control the rate of flow through the lumen, and/or one or more sensors to provide feedback to a controller. Examples of physiological parameters that could be sensed or measure are blood pressure, heart rate, cardiac output, paO ₂, O₂saturation, O₂saturation, mean systemic arterial pressure or mean systemic venous pressure.

In an alternate embodiment, the shunt device could a self-adjustable shunt device to self-adjust its cross sectional area or its length, or both, as a function of the pressure difference across the shunt device. The self-adjustable shunt could then automatically control the blood flow rate through the shunt at a predetermined blood flow rate level or range. The material of such a self-adjustable shunt device would then have expansion and contraction features to change the cross sectional area or the length, or both.

The reduction of systemic vascular resistance and (controlled) blood flow through the shunt device from the arterial system to the venous system has some important consequences that could benefit various kinds of patients. These consequences are related to respiratory, cardiac and circulatory effects. For example, the method could be a respiratory or cardio-respiratory therapy based on an increase of the partial pressure of O ₂dissolved in the arterial blood plasma, an increase of the hemoglobin O₂saturation in arterial or venous blood, or an increase of the O₂concentration in arterial or venous blood. Accordingly, patients with respiratory problems could benefit from the consequences as a respiratory or cardio-respiratory therapy. In another example, the method could be is a cardiac therapy based on an increase of the cardiac output. Accordingly, patients with cardiac problems could benefit from the consequences as a cardiac therapy. In yet another example, the method could be a circulatory therapy based on a decrease of the pulmonary arterial blood pressure, a decrease of the systemic arterial blood pressure, a decrease of the systemic systolic pressure or a decrease of the systemic diastolic pressure. Accordingly, patients with circulatory problems could benefit from the consequences as a circulatory therapy.

BRIEF DESCRIPTION OF THE FIGURES

The objectives and advantages of the present invention will be understood by reading the following detailed description in conjunction with the drawings, in which: [0011]
FIG. 1 shows the concept of decreasing systemic vascular resistance according to the present invention; [0012]
FIG. 2 shows an example blood flowing, with or without a shunt device of the present invention, from a high resistance arterial system with a high oxygen concentration to the low resistance venous system with a low oxygen concentration; [0013]
FIG. 3 shows an example of shunt device positioned between the aorta and inferior vena cava according to the present invention; [0014]
FIG. 4 shows examples of shunt devices according to the present invention; [0015]
FIG. 5 shows an example of shunt device with a control means according to the present invention; [0016]
FIG. 6 shows an example of shunt device with a controllable or self-adjustable mechanism according to the present invention; [0017]
FIG. 7 shows an example of shunt device with a controllable mechanism based on a smart material according to the present invention; [0018]
FIG. 8 shows an example of a self-adjustable shunt device according to the present invention; [0019]
FIG. 9 shows an example of shunt device with a means to increase resistance to blood flow according to the present invention; and [0020]
FIGS. 10-12 show additional information regarding some physiological effects of an aorto-caval fistula in rats according to the present invention.[0021]

DETAILED DESCRIPTION OF THE INVENTION

Blood flows from the heart via the arterial system AS to the vasculature of the tissues from which it returns back to the heart via the venous system VS as shown by [0022] system 110 in FIG. 1. Blood returning to the right side of the heart is pumped to the lungs where it binds oxygen (becomes oxygenated, or re-oxygenated) before returning to the left side of the heart to be pumped to the body's tissues via the arterial system. Blood flow experiences a resistance from all of the systemic vasculature, which is referred to as the systemic vascular resistance (SVR). SVR excludes the pulmonary vasculature but when these two are combined it is sometimes referred as total peripheral resistance (TPR). SVR is determined by factors that influence vascular resistance in individual vascular beds. Mechanisms that cause vasoconstriction (reducing the caliber of a vessel) will increase SVR, and those that cause vasodilation (increasing the caliber of a vessel) will decrease SVR. The actual change in SVR in response to neurohumoral activation, for example, will depend upon the degree of activation and vasoconstriction, the number of vascular beds involved, and the relative in-series and parallel arrangements of these vascular beds to each other. Although SVR is primarily determined by changes in blood vessel diameters, changes in blood viscosity will also affect SVR.
The present invention decreases the SVR by having an [0023] arteriovenous shunt device 130 implanted to shunt and re-circulate blood from the arterial system AS to the venous system VS in system 120 as shown in FIG. 1. The re-circulated blood through shunt device 130 bypasses the peripheral microcirculation and decreases the SVR when one would compare system 110 with SVR₀to system 120 with SVR₁; i.e. SVR₁is lower than SVR₀. A desired decrease of the SVR would be at least 5% after the implantation of shunt device 130.
In general, [0024] shunt device 110 could be implanted between a large (proximal) artery and a large (proximal) vein. The location is selected to shunt and (quickly) re-circulate blood from the high resistance arterial system with a high oxygen concentration to the low resistance venous system with a low oxygen concentration as shown by system 120 in FIG. 2. In a preferred embodiment, implantation of shunt device 130 is between the aorta 310 and the inferior vena cava 320, either proximal of the renal arteries, or more preferably distal of the renal arteries, as shown in FIG. 3.
Blood flow through a [0025] lumen 230 of the shunt device 130 typically results from a pressure gradient between the blood in the arterial system and the blood in the venous system, indicated by the large P and small p in FIG. 2 (note different font sizes). The blood flow rate through shunt device 130 after implantation should be at least (about) 5 ml/min. While the pressure gradient between the arterial and venous sides of the vasculature will generally be sufficient to achieve and control the target volume of blood flow, in some instances it may be desirable to utilize a control means or self-adjustable mechanism to either maintain a level/range or increase/decrease the blood flow rate (see also infra).
The reduction of SVR and (controlled) blood flowing through [0026] shunt device 130 from the arterial system to the venous system has some important consequences when system 110 (pre-implantation) and is compared with system 120 (post-implantation). These consequences are related to cardiac, circulatory and respiratory effects.
With respect to the cardiac effects, an important consequence of decreasing the SVR is that the cardiac output increases according to: [0027] $CO = \frac{MAP - CVP}{SVR}$
whereby CO is cardiac output, MAP is mean arterial pressure, and CVP is central venous pressure. Since CVP is normally near 0 mmHg, the calculation is often simplified to: [0028] $CO = \frac{MAP}{SVR}$
Cardiac output is equivalent to the blood flow rate according to: [0029]
CO=SV*HR
whereby SV is stroke volume and HR is heart rate. [0030]
When SVR decreases, MAP decreases to a smaller degree. The decrease in MAP is due to a small drop in systolic pressure (P[0031] _systolic) and a larger drop in diastolic pressure (P_diastolic). P_diastolicis dependent on the SVR whereby a drop in SVR results in a drop in P_diastolic. The pulse pressure (P_systolic−P_diastolic) is then increased. For instance, before implantation MAP could be 90 mmHg and SVR could be 18 dynes, which results in a CO of 5 liters per minute. SVR of 18 dynes is determined by dividing an SVR of 1440 dynes by a conversion factor of 80. MAP of 90 mmHg is determined by using: $MAP ≅ P_{diastolic} + \frac{1}{3} (P_{systolic} - P_{diastolic})$
with an exemplary PP of 30 mmHg given a P[0032] _systolicof 110 mmHg and P_diastolicof 80 mmHg.
After implantation, SVR could for instance drop from 1440 dynes to 1000 dynes and with the conversing factor of 80 drop from 18 to 12.5. If blood pressure has a P[0033] _systolicof 100 mmHg over a P_diastolicof 55 mmHg, then MAP is 70 mmHg; i.e. in this example the P_systoliccould have dropped by 10 mmHg, but the P_diastoliccould have dropped by 25 mmHg. Combining these exemplary numbers would result in a cardiac output of 5.6 liters per minute; i.e. 70 mmHg divided by 12.5.
With respect to the respiratory effects, an important consequence of shunting arterial blood to the venous circulation (such as the aorta to the inferior vena cava) is that blood with high O[0034] ₂content circulates to the venous blood system without having the O₂extracted in tissue capillaries. The O₂“rich” arterial blood re-circulates to, and mixes with, the low O₂concentration of the venous system. As a result, the blood flowing through shunt device 130 increases the O₂concentration in the venous blood, which is illustrated by the different (font) sizes of O₂in FIG. 2. The increase of O₂concentration in the venous blood system leads to an increase in the O₂concentration in the arterial blood in two ways, which is also illustrated by the different (font) sizes of O₂in FIG. 2. First, since the blood that is shunted does not have O₂extracted by tissue capillaries, the blood returning to the lungs has a higher O₂concentration after the creation of the shunt than before. Second, O₂is carried in the blood in two forms: (i) dissolved in arterial plasma, and (ii) bound to a protein called hemoglobin that is contained in red blood cells. Oxygen binds to hemoglobin with curvilinear kinetics, so that O₂very efficiently binds to (and is carried by) hemoglobin at high PaO₂(partial pressure of O₂in arterial plasma), but when the PaO2 is low (in particular below a PaO₂of 60 mmHg), O₂is less efficiently bound to (or carried by) hemoglobin. Since the amount of O₂that is bound to hemoglobin is related to the PaO₂, an increase in PaO2 will result in greater binding of O₂to hemoglobin, and increased oxygen carrying capacity.
With respect to circulatory effects, an important consequence of decreasing SVR is related to the fact that the lungs regulate their blood flow according to the O[0035] ₂content. A low O₂content in the small pulmonary arteries impairs blood flow to the lung resulting in a high pulmonary pressure—a process called hypoxic pulmonary vasoconstriction. Therefore increasing the O₂content in the pulmonary arterial blood should decrease the pulmonary arterial blood pressure. Other important circulatory consequences, as described supra with respect to cardiac consequences, are a decrease in systemic arterial blood pressure, a decrease in systemic arterial systolic pressure and/or a decrease in systemic arterial diastolic pressure.
As a person of average skill in the art would readily appreciate, the different distinct effects could be beneficial to patients with cardiac problems as a cardiac therapy, to patients with respiratory problems as a respiratory or cardio-respiratory therapy, or to patients with circulatory problems as a circulatory therapy. An illustrative list of therapies is for instance: [0036]
Cardiac therapies. The shunt device of the present invention could benefit patients with cardiac failure or patients who suffer from a low cardiac output (congestive heart failure) by providing an increased cardiac output. [0037]
Respiratory or cardio-respiratory therapies. The shunt device of the present invention could benefit patients with pulmonary arterial hypertension to lower pulmonary arterial blood pressure, patients with heart and/or respiratory failure by increasing arterial oxygen concentration, patients with chronic obstructive pulmonary disease by increasing of blood oxygen concentration. [0038]
Circulatory therapies: The shunt device of the present invention could benefit patients with hypertension to lower systemic arterial, systolic and/or diastolic blood pressure. [0039]
Other diseases or conditions that could benefit from the present invention are, for instance, hypotension (by increasing cardiac output), lung fibrosis, adult respiratory distress syndrome, and the like. [0040]
The blood flow rate through the shunt device is preferably at least 5 ml/min. In case the shunt device is a cylinder then the parameters of the lumen of the shunt device that determine the blood flow rate through its lumen can be determined with the Poiseuille equation: [0041] $BFR = \frac{πΔ \Pr^{4}}{3 η l}$
whereby the volume flow rate (BFR) is a function of a blood with viscosity η, the pressure difference ΔP across the lumen of the shunt device, length l of the lumen of the shunt device and radius r of the lumen of the shunt device as shown by [0042] shunt device 410 in FIG. 4. One could also refer to the cross sectional area CSA of the lumen of shunt device 410, which is in case of a cylinder equivalent to πr². Generally speaking, the shape of the lumen could be a circle, an oval or any other shape as long as the requirement of blood flow is met.
In an illustrative example using the Poiseuille equation, ΔP could range from about 30 mmHg (in someone with a MAP of 40 mmHg and a venous pressure of 10 mmHg) to about 150 (in someone with a MAP of 160 mmHg and a venous pressure of 10 mmHg). The blood viscosity could be determined in a variety of ways that could for instance be obtained from a paper by Johnston B M et al. (2004) entitled “[0043] Non-Newtonian blood flow in human right coronary arteries: steady state simulations” and published in J Biomechanics 37:709-720. With a viscosity of 0.0345P and a combination of a radius of 3 mm and a length of 3 mm of the lumen of the shunt device one would achieve a blood flow rate through the shunt of over 5 ml/min. As a person of average skill would readily appreciate, different combinations of radius and length could be determined to achieve the desired blood flow rate. In general, the length could range from about 2.5 mm to about 15 mm, and the radius could range from about 2.5 mm to about 15 mm. For the length one could determine a minimum length of e.g. 2.5 mm given an exemplary wall thickness of a human adult aorta of about 1.5 mm and an exemplary wall thickness of a human adult inferior vena cava of about 1 mm. One could also express the lumen opening in terms of cross section area, which could range from about 19 mm²to about 750 mm².
The shunt device is preferably made from any biocompatible material strong enough or sufficiently reinforced to maintain a lumen that meets the desired blood flow rate. In one embodiment, the shunt device is made of metal, preferably titanium, while in other embodiments the shunt device could be formed from conventional vascular graft materials, polytetrafluoroethylene (PTFE), nickel titanium memory, elastic material, or the like. The inner surface of the shunt device is preferably coated in whole or in part to inhibit the formation of blood clots. The surface could be coated with for instance polytetrafluoroethylene (Teflon®), or similar coatings/products. The shunt device might also be coated with antibiotic to prevent atheroma, infection, and/or anti-proliferative or anticoagulant agents to prevent clot formation in the lumen. [0044]
In a preferred embodiment, loosing the connection of the shunt device with the artery and vein should be avoided. Different techniques could be employed to provide such a secure connection. For instance, for attachment of shunt devices formed from typical fabric graft materials one could use sutures, staples, biocompatible glues, or the like. In the case of metals and other rigid materials, the shunt device could be formed with flared or flanged ends, such as the umbrella or funnel device [0045] 424 (shown in FIG. 4). Umbrella ends 424 are placed at opposite ends of a tubular element 422 that form shunt device 420. Umbrella ends 424 are positioned respectively inside the artery and inside the vein, and the tubular element connects in between the artery and the vein. In a different embodiment, umbrella ends 434 could be positioned more or less perpendicular with respect to tubular element 432 as shown in shunt device 430. The key idea is that the diameter of the securing (connection) elements is larger than the opening in the artery and vein thereby keeping the shunt device in place. The securing elements could include a mechanism that unfolds when the shunt device is in place and implanted in the artery and vein. The art teaches different techniques and securing type mechanisms that could be used in the present invention.
The shunt device(s) could be implanted in a variety of ways, including the open surgical procedures, the laparoscopic and other minimally invasive techniques, and the intravascular techniques (where all or a portion of the shunt device is introduced at least partially through the lumen of one of the blood vessels to be shunted). The shunt device could also be implanted by, for instance, a surgical procedure such as an aortic surgery. The shunt device could further be implanted through interventional procedures such as, for instance, by means of a catheter through the iliac artery and guided by fluoroscopy. The shunt device could be deployed over a guidewire (e.g. the Seldinger technique) and assembled in the body through interventional radiology techniques like the opening of an umbrella. All such surgical and interventional techniques are well known in the art. It is preferred to leave the shunt device implanted in the person for a long-term period (at least 6 weeks, but most often for years). [0046]
In some cases it might be desired to include a control means to control the blood flow rate with one or more flow control elements, one or more controllers and/or one or more sensors. A [0047] flow control element 520 could be placed in the shunt device 510 as shown in FIG. 5. It could be placed at either end of the shunt device or somewhere in between. In one example, the function of the flow control element could be as simple as to have an electrically, magnetically or mechanically open/close mechanism such as a switch or one-way valve. Such an open/close element could also be a hook with a lever or a gearshift. In another example, a controller 530 could be used to control the timing of opening/closing (e.g. frequency and duration) or to control changes in blood flow rate. Controller 530 could control flow control element 510 such as one-way valve(s), pump(s) (positive displacement pump(s), rotary pump(s), peristaltic pump(s), and the like), controllable orifice(s) and the like. The flow control element could be electrically charged using an internal battery (e.g. a lithium battery; not shown) or by external power (not shown) using a magnetic impeller, both of which are common techniques in the art.
Yet another advancement of the control means for the shunt device is to include one or [0048] more sensors 540 that provide feedback to the controller 530. The figures show two sensors, however, the present invention is not limited to two sensors and could be at least one sensor that is implanted inside the shunt device, near the shunt device, or inside or near the vasculature system. The sensor(s) could also be placed outside the body. Sensors 540 could sense (and/or measure) physiological parameter(s) in real time either periodically or continuously. The selection of one or more physiological parameters could be to reflect the condition of a person or patient who is being treated. Examples of physiological parameters that could be sensed with one or more sensors are blood pressure, heart rate, cardiac output, paO₂, O₂saturation, O₂saturation, mean systemic arterial pressure, and/or mean systemic venous pressure. The controller could include a decision method to determine appropriate action on the flow control element. The controller could either be a stand-alone implantable controller and/or could be operated from outside the body. It might be useful to update the controller or change the current controller settings; e.g. in cases when the controller controls a set-value, a particular range or critical boundaries (minima/maxima), or when the controller requires an upgrade of its code.
The controller may select different criteria that are e.g. dependent on the type of disease, condition and/or desired therapy. In one example, the heart rate could be maintained at a reasonable physiological range and not exceed the person's maximum heart rate. The controller could have a target heart rate range of, for instance, 80 to 140 beats per minute, more usually from 90 to 110 beats per minute. In another example, it might be desired to increase cardiac output, partial pressure of O[0049] ₂dissolved in the arterial blood plasma (PaO₂), the hemoglobin O₂saturation in arterial or venous blood, or the O₂concentration in arterial or venous blood. These increases could be at least 5% compared to their value before implantation, except for HbO₂, which could be at least 1%. In a preferred situation these increases could be higher and on the order of 10% or 20% and up (5% and 10% for HbO₂). In still another example, it might be desired to decrease the pulmonary arterial blood pressure, the systemic arterial blood pressure, the systemic systolic pressure or the systemic diastolic pressure. These decreases could be at least 5% compared to their value before implantation. In a preferred situation these decreases could be higher and on the order of 10% or 20% and up. In yet another example, the blood flow rate could increase from at least 5 ml/min compared to before implantation to a situation where the shunt is capable of carrying up to 5000 ml/min of blood at e.g. a pressure differential across the shunt device of 70 mmHg.
The description supra relates to a shunt device whereby the blood flow rate could be changed and controlled. In these situations, the structural parameters of the shunt device, such as the length, cross section area and radius are fixed. However, in an alternate embodiment, described infra, the shunt device could change its cross section area, radius and/or length. This could be accomplished either in a controlled fashion, like with a controller and sensor(s) as described supra, or in a self-adjustable fashion (i.e. self-organizing fashion). [0050]
FIG. 6 shows an example of a [0051] shunt device 610, 620 with a mechanism of leaves 630 disposed in the lumen of the shunt device that could change the cross section area of the lumen. Leaves 630 could be attached to a central axis or to the inner wall of shunt device 610, 620 respectively. Two or more leaves could be used with the capability of changing their position from a closed position gradually to an open position (compare 610 and 612, and 620 and 622 respectively). The leaves in shunt devices 610, 620 could be integrated with a controller 640 and/or sensor(s) 650 in a similar fashion as described supra.
[0052] Leaves 630 could also be included as a self-adjusting mechanism for opening and closing of the shunt device. When the blood flow increases or blood pressure increases, the flexible leaves automatically open up from a more or less closed position to a more or less open position, and vice versa.
FIG. 7 shows an example of a [0053] shunt device 710 that is made of a smart material such as a memory metal/alloy that can change its length and cross sectional area (radius). For instance, shunt device 710 could be made longer as shown by 720 or wider as shown by 730 (larger cross sectional area). Shunt devices 710 could be integrated with a controller 740 and/or sensor(s) 750 in a similar fashion as described supra. Mechanisms of memory metals/alloys (including particular stent-graft materials) and their controls are known in the art.
In a self-adjustable fashion it could e.g. be desirable to keep the blood flow rate at a level or range across the shunt device without any controller; i.e. the shunt device is self-organizing. To establish this the length and radius need to work in tandem as a function of ΔP and according to the Poiseuille equation (see supra) (see FIG. 8). For instance, length and ΔP have a linear relationship such that when ΔP increases the length increases in a linear fashion to maintain the blood flow rate at the same level, and vice versa. The radius and ΔP have an inverse non-linear relationship such that when ΔP increase the radius decreases in a non-linear fashion to maintain the blood flow rate at the same level, and vice versa. It is pointed out that the length and radius have to work in opposite and unequal value to maintain a particular blood flow rate (see supra for Poiseuille equation). [0054] Shunt device 810 should then be made of a material that is capable of increasing its length, but simultaneously decreasing its radius when ΔP increases, (indicated by changing from 810 and 820). Examples of such materials are elastic materials with reinforced filaments or fibers arranged and distributed over (or within) the shunt device (not shown in 810, 820) to ensure selected and directional changes, according to Poiseuille equation; i.e. (i) an increase in cross sectional area with a decrease in length, and (ii) a decrease in cross sectional area with an increase in length.
Other than following the Poiseuille equation one could change the blood flow rate by following Ohm's law by increasing the resistance to blood flow through the shunt device. Means to increase this resistance could for instance be accomplished by disposing roughness or obstacles such as [0055] bumps 930 or filaments/spokes 940 to the inner wall of the lumen of shunt device 910, 920 respectively as shown in FIG. 9. The blood flow could then also change from laminar flow to non-laminar flow.
FIGS. 10-12 show additional information regarding some physiological effects of an aorto-caval fistula in rats. These effects are the result of a study performed by the inventors of the present invention. FIG. 10 shows the effect of an aorto-caval fistula on several groups of experimental animals. In each group the presence of an aorto-caval fistula was associated with increased aortic blood flow (AF) and with increased partial pressure of oxygen in arterial blood (PaO[0056] ₂) in rats that were receiving supplemental oxygen (FiO₂=0.24, or the fraction of inspired oxygen was 24%). Measurements of: (A): Aortic flow (24% O2) and (B): Arterial blood oxygen tension (FiO₂=0.24) (PaO₂). Note that groups PM and PFM received FiO₂=0.50 during experimentation. Group N represents normal rats (n=6), Group F underwent aorto-caval fistula (n=6), Group P underwent left pneumonectomy (n=6), Group PF underwent left pneumonectomy and the creation of an aorto-caval fistula (n=6), Group M received a toxin that causes pulmonary hypertension called monocrotaline (n=6), Group FM underwent aorto-caval fistula and received monocrotaline (n=6), Group PM underwent left pneumonectomy and received monocrotaline (n=6), Group PFM underwent left pneumonectomy and the creation of an aorto-caval fistula and then received monocrotaline (n=6). (**=p<0.01).
FIG. 11 shows the effect of the presence of an aorto-caval fistula in several groups of experimental animals. Aorta-caval fistuala attenuates the development of pulmonary arterial hypertension. The measurements shown in FIG. 11 are of mean pulmonary artery pressures (PAP). Group N represents normal rats (n=6), Group F underwent aorto-caval fistula (n=6), Group P underwent left pneumonectomy (n=6), Group PF underwent left pneumonectomy and the creation of an aorto-caval fistula (n=6), Group M received monocrotaline (n=6), Group FM underwent aorto-caval fistula and received monocrotaline (n=6), Group PM underwent left pneumonectomy and received monocrotaline (n=6), Group PFM underwent left pneumonectomy and the creation of an aorto-caval fistula and then received monocrotaline (n=6). (*=p<0.05,**=p<0.01). [0057]
FIG. 12 shows photomicrographs of small pulmonary arteries (A-D). (A) shows an example that normal rat (group N) arterioles do not have evidence of neointimal formation (grade 0). (B) shows an example of a [0058] grade 1 neointimal lesion (<50% occlusion) seen in rats that received monocrotaline alone (group M). (C) shows an example of grade 1 neointimal lesion (<50% occlusion) seen in rats that underwent left pneumonectomy and the creation of an aortocaval fistula (ACF) and then received monocrotaline (group PMF). (D) shows an example of a grade 2 neointimal lesion (>50% occlusion) seen in rats that underwent left pneumonectomy and received monocrotaline (group PM). All photomicrographs (X400), elastin van Gieson stain.
The present invention has now been described in accordance with several exemplary embodiments, which are intended to be illustrative in all aspects, rather than restrictive. Thus, the present invention is capable of many variations in detailed implementation, which may be derived from the description contained herein by a person of ordinary skill in the art. For example, in some instances, it may be possible and desirable to implant two or more shunt devices at different locations between the arterial and venous sides of the vasculature. In cases of such multiple shunt device implantations, the individual shunts may be implanted in close proximity to each other or may be distributed at different regions of the vasculature. [0059]
In another aspect, it should be pointed out that the present invention could be used as preventative care or as a therapy for a condition or disease. Furthermore, as a person of average skill would readily appreciate, the long-term implantable shunt device could be beneficial to improve the performance in athletes, military service personnel, performance animals (e.g. dogs and horses). [0060]
The preferred location of the shunt device is between the aorta and inferior vena cava as described supra. However, it would be feasible to implant one or more shunt devices for a long-term period in the pelvis area to link the common iliac artery and vein or femoral artery and vein. In another embodiment the shunt device could be positioned in the axilla and it would link the axillary artery and vein. In yet another embodiment the device could be positioned close to the clavicle and link the subclavian artery and vein. [0061]
All such variations and other variations are considered to be within the scope and spirit of the present invention as defined by the following claims and their legal equivalents. [0062]

Claims

What is claimed is:

1. A therapeutic method for a human, comprising: decreasing the systemic vascular resistance by having for a long-term period an implantable arteriovenous shunt device between an artery and vein of said human, said shunt device having a blood flow rate through said shunt device of at least 5 ml/min after said implantation.

2. The method as set forth in claim 1, wherein said artery is an aorta and said vein is an inferior vena cava.

3. The method as set forth in claim 1, wherein said method is a respiratory or cardio-respiratory therapy.

4. The method as set forth in claim 3, wherein said respiratory or said cardio-respiratory therapy is based on an increase of the partial pressure of O₂dissolved in the arterial blood plasma, an increase of the hemoglobin O₂saturation in arterial or venous blood, or an increase of the O₂concentration in arterial or venous blood.

5. The method as set forth in claim 1, wherein said method is a cardiac therapy.

6. The method as set forth in claim 5, wherein said cardiac therapy is based on an increase of the cardiac output.

7. The method as set forth in claim 1, wherein said method is a circulatory therapy.

8. The method as set forth in claim 7, wherein said circulatory therapy is based on a decrease of the pulmonary arterial blood pressure, a decrease of the systemic arterial blood pressure, a decrease of the systemic systolic pressure or a decrease of the systemic diastolic pressure.

9. The method as set forth in claim 1, further comprising controlling said blood flow rate through said shunt device at a blood flow rate level or range.

10. The method as set forth in claim 9, wherein said controlling further comprises sensing and using physiological parameters, wherein said physiological parameters are blood pressure, heart rate, cardiac output, paO2, O₂saturation, O₂saturation, mean systemic arterial pressure or mean systemic venous pressure.

11. The method as set forth in claim 1, further comprising self-adjusting said blood flow rate through said shunt at a predetermined blood flow rate level or range by having said shunt device capable of self-adjusting its cross sectional area or its length, or both, as a function of the pressure difference across said shunt device.

12. The method as set forth in claim 1, wherein said shunt device is implantable via an open surgical procedure, a minimally invasive surgical procedure, or an intravascular procedure.

13. An apparatus for therapy in a human, comprising: a long-term implantable arteriovenous shunt device between an artery and a vein in said human to decrease the systemic vascular resistance, wherein the cross sectional area and the length of the lumen of said shunt device are selected to having a blood flow rate through said shunt device of at least 5 ml/min after said implantation.

14. The apparatus as set forth in claim 13, wherein said artery is an aorta and said vein is an inferior vena cava.

15. The apparatus as set forth in claim 13, wherein said cross sectional area is in the range of about 19 mm²to about 750 mm²

16. The apparatus as set forth in claim 13, wherein said length is in the range of about 2.5 mm to about 15 mm.

17. The apparatus as set forth in claim 13, wherein the radius is in the range of about 2.5 mm to about 15 mm.

18. The apparatus as set forth in claim 13, further comprising a control means to control said blood flow rate through said shunt at a blood flow rate level or range.

19. The apparatus as set forth in claim 18, wherein said control means comprises one or more sensors to sense said blood flow rate or the pressure difference across said shunt device.

20. The apparatus as set forth in claim 18, wherein said control means comprises one or more flow control elements.

21. The apparatus as set forth in claim 13, wherein said shunt device is a self-adjustable shunt device to self-adjust its cross sectional area or its length, or both, as a function of the pressure difference across said shunt device to automatically control said blood flow rate through said shunt at a predetermined blood flow rate level or range.

22. The apparatus as set forth in claim 13, wherein the inner wall of said shunt device has a coating to prevent clot formation or atheroma formation.