Patent Publication Number: US-2006015065-A1

Title: Method of drug perfusion in paraaortic lymph node tumors, sheath for inserting catheter, and oxygenated blood perfusion apparatus

Description:
BACKGROUND OF THE INVENTION  
      1. Field of the Invention  
      The present invention relates to a method of local drug delivery by way of perfusion; specifically, to delivery of a drug to paraaortic lymph node tumors by way of perfusion (hereinafter may be referred to as, for example, a “method of drug perfusion in paraaortic lymph node tumors”); to an apparatus for performing the method; and to a sheath used for performing the method. More particularly, the present invention relates to an effective method for delivering, by way of perfusion, a drug of high concentration to paraaortic lymph nodes, while preventing inflow of the drug to normal tissues, to thereby provide a chemical treatment against tumors; to an apparatus for performing the method; and to a sheath used for performing the method.  
      2. Description of the Related Art  
      The lymphatic system is constituted of lymph ducts spread throughout the body, and lymph nodes, which are nodules of tissue found along the lymph ducts. Lymph fluid containing lymphocytes flows through the lymph ducts. Lymphocytes produce antibodies for defending the living body against bacteria and viruses. Lymphocytes are differentiated and proliferated in the lymph nodes. The lymph nodes filter the lymph in order to remove foreign matter such as bacteria.  
      The lymph nodes are found systemically, but primarily in the armpits and the neck. Of such lymph nodes, those present around the abdominal aorta are called paraaortic lymph nodes. The aorta is the major artery of the cardiovascular system for pumping blood from the heart to the entire body. The paraaortic lymph nodes, which are located around the aorta, are connected to organs throughout the whole body through lymph ducts.  
      When a patient suffers stomach cancer or renal cancer as a result of the development of a malignant tumor primarily occurring in an organ other than the stomach or kidneys, the tumor may spread to the paraaortic lymph nodes through the lymph ducts around that organ. In such a case, as the conditions aggravate, tumor cells happen to pass through some lymph nodes, and ultimately the tumor may be spread systemically through the blood vessels and lymph ducts. Such tumors that have already been spread over the whole body are extremely difficult to cure, and the prognosis is generally very poor.  
      Hitherto, when a tumor is found in a paraaortic lymph node, therapy has followed either a surgical approach or a chemical approach.  
      In the surgical approach, lymph nodes are dissected (removed) by surgical operation and the tumor tissue is removed. Although this approach may promise a radical treatment, a great burden is imposed on the patient, since a large incision running from the abdomen to the chest is made, and not only lymph nodes but sometimes their surrounding tissue are also removed to a great extent. Moreover, there is a risk that the patient may be infected and develop, e.g., sepsis during or after the surgical operation.  
      Meanwhile, in the chemical approach, a drug such as an anticancer agent is administered to the tumor tissue, to thereby suppress differentiation of tumor cells and destroy the cells. In general, the drug is administered to the tumor tissue either via the oral route or by means of a catheter or a like apparatus, which is inserted into a blood vessel such as the jugular vein for delivering the drug to the tumor tissue through the liquid-feeding passage provided in the apparatus.  
      This approach neither leaves a long cut in the patient&#39;s skin nor removes tissue from the patient. Therefore, a smaller burden will be imposed on the patient. However, this approach cannot prevent the anticancer drug from migrating into another organ, thereby reducing the concentration of the drug to which the tumor tissue is exposed, and lowering the anti-tumor effect. Another possible disadvantage is that when the drug flows into unintended tissues; i.e., tissues other than the tumor tissue, normal cells will be injured, causing adverse side effects.  
      Conventionally, in the therapy of a pelvic tumor, perfusion with an anticancer agent has been performed in order to administer the agent effectively to the tumor tissue while preventing the above-mentioned adverse side effects. According to this method, two balloon catheters are employed such that one is indwelled in the aorta and the other in the vena cava, and the balloons are inflated for closure thereof to thereby block blood flow. Subsequently, tourniquets are placed on the limbs to stop blood circulation in the lower limbs. The balloon inflation regions of the balloons and the tourniquets mounted on the two limbs create a closed region isolated from blood circulation. The pelvic tumor tissue is contained in the thus-created closed region.  
      After blockage of the blood vessels, an anticancer agent is fed to the closed region through the artery site, and the bodily fluid is removed at a venous site. This method promises an enhanced anti-tumor effect and reduced side effects, because it enables targeted exposure of an anticancer agent of high concentration to only the tumor tissue, since the anticancer agent is administered after the arteriovenous blood flow has been cut, to thereby prevent the agent from being delivered to the whole body (see, for example, Patent Document 1).  
      Patent Document 1: Japanese Patent Application Laid-Open (kokai) No. 2003-102829  
      However, in the treatment of paraaortic lymph node tumors, perfusion in a manner as described above has not been performed, and demand still exists for development of effective treatment for such tumors.  
     SUMMARY OF THE INVENTION  
      In view of the foregoing, an object of the present invention is to provide a drug perfusion method employable in the treatment of a tumor developed in paraaortic lymph nodes, the method ensuring effective exposure of the lymph nodes with a therapeutic agent of high concentration, while preventing the therapeutic agent fed to the tumor tissue from leaking into surrounding tissues, and reducing or preventing side effects attributable to the therapeutic agent; an apparatus for performing the drug perfusion method; and a sheath used for performing the drug perfusion method.  
      Another object of the present invention is to provide a catheter-introducing sheath employable in the treatment of a tumor developed in paraaortic lymph nodes, wherein the use of the sheath reduces the number of instruments which are percutaneously introduced into the body or a blood vessel of the patient and indwelled therein.  
      A further object of the present invention is to provide a catheter-introducing sheath capable of attaining smooth insertion of three catheters into the patient&#39;s body or blood vessels.  
      According to the invention described in claim  1 , there is provided a drug perfusion method of delivering a drug by way of perfusion to a site of tumor tissue located in a paraaortic lymph node and recovering the drug, comprising: 
          a perfusion preparatory step including introducing a plurality of balloon catheters into a living body percutaneously so as to indwell the catheters in blood vessels which are branched from the aorta and are present around paraaortic lymph nodes, so that balloon inflation regions of the balloon catheters are positioned at predetermined sites of the blood vessels, and applying to predetermined positions of the lower limbs tourniquets having inflatable regions;     a closed-region creating step of creating a closed region of arteriovenous vessels by inflating the balloons of the balloon catheters and the inflatable regions of the tourniquets so as to cut blood flow to and from the closed region;     an oxygenated blood supply step of feeding oxygenated blood to organs to which blood supply has been cut as a result of the closed-region creating step having been performed;     a drug administration step of administering a drug solution containing a drug to the closed region; and     a bodily fluid recovering step of recovering from the closed region bodily fluid containing the drug.        

      According to the invention as described in claim  2 , there is provided a drug perfusion method of delivering a drug by way of perfusion to a site of tumor tissue located in a paraaortic lymph node as recited in claim  1 , wherein the balloons of the balloon catheters are indwelled so that the balloon inflation regions are positioned at predetermined sites in at least the right renal artery, the left renal artery, the celiac artery, the superior mesenteric artery, the inferior mesenteric artery, the aorta proximal to the heart with respect to the branching portion of the celiac artery, and the inferior vena cava.  
      Thus, the perfusion method as recited in claim  1  or claim  2  includes closing major branching blood vessels of the aorta to thereby create a blood vessel closure region around the tumor tissue, and subsequent administering of a drug to the closed region. Since the drug administered to the closed region remains to stay within the region, the concentration of the drug within the region can be maintained high, and therefore, lymph node tumors can be effectively exposed to the drug of high concentration.  
      Also, since the perfusion method as recited in claim  1  or claim  2  prevents the drug from coming into contact with normal tissues that are present outside the closed region, side effects of the drug can be reduced or prevented.  
      Moreover, according to the perfusion method as recited in claim  1  or claim  2 , oxygenated blood is fed to organs to which blood supply has been cut. Therefore, ischemia of the organs which would otherwise be caused due to stopped blood flow is prevented, to thereby reduce or prevent the risk of injuring the organs.  
      According to the invention described in claim  3 , oxygenated blood is fed to organs through a balloon catheter indwelled in the right renal artery, a balloon catheter indwelled in the left renal artery, and at least one balloon catheter selected from among the three balloon catheters indwelled at predetermined positions in the celiac artery, the superior mesenteric artery, and the inferior mesenteric artery.  
      Thus, according to the perfusion method as recited in claim  3 , in the case of feeding oxygenated blood to the celiac artery, the superior mesenteric artery, and the inferior mesenteric artery, feeding of oxygenated blood through only one of these three arteries can transport oxygenated blood to all the organs that communicate with these three arteries. Therefore, cumbersome manipulation of feeding blood to all three of the arteries simultaneously is no longer necessary, and organs can be protected with a simplified blood feeding procedure.  
      According to the invention described in claim  4 , a drug is administered through a balloon catheter which is indwelled in the aorta at a predetermined position thereof, the position being on the heart side with respect to the branching portion of the celiac artery.  
      Thus, according to the perfusion method as recited in claim  4 , a single balloon catheter indwelled in the aorta at a predetermined position on the heart side of the branching portion is used to inflate the balloon and also to administer the drug. Therefore, the number of instruments to be inserted into the patient&#39;s body can be reduced, to thereby reduce the burden imposed on the patient.  
      According to the invention described in claim  5 , there is provided a catheter-introducing sheath for introducing into a living body a catheter which is used for performing the perfusion method of delivering, by way of perfusion, a drug to a paraaortic lymph node tumor, comprising: 
          a first passage for allowing passage of a first catheter therethrough, a second passage branching from the first passage and allowing passage of a second catheter therethrough, and a third passage branching from the first passage and allowing passage of a third catheter therethrough.        

      Thus, the catheter-introducing sheath as recited in claim  5  has a structure which allows insertion of three catheters simultaneously. Therefore, use of the catheter-introducing sheath of the present invention can reduce the number of instruments to be percutaneously inserted into the patient&#39;s body, to thereby reduce the burden imposed on the patient.  
      According to the invention described in claim  6 , there is provided a catheter-introducing sheath for introducing into a living body a catheter which is used for performing the perfusion method of delivering, by way of perfusion, a drug to a paraaortic lymph node tumor, comprising: 
          a tubular body having a first passage for allowing passage of a catheter therethrough,     a first branched connector which is connected to an end of the tubular body and which has a second passage and a third passage, the second passage directly communicating, via a first end of the first branched connector, with the first passage and the third passage branching from the second passage, and     a second branched connector which is connected to a second end of the first branched connector, the second end being opposite the first end, and which has a fourth passage and a fifth passage, the fourth passage directly communicating with the second passage and the fifth passage branching from the fourth passage.        

      According to the invention described in claim  7 , the first and the second branched connectors in the catheter-introducing sheath as recited in claim  6  are made of the same material.  
      According to the invention described in claim  8 , the axis running through the first, second, and the fourth passages, the axis running through the third passage, and the axis running through the fifth passage do not lie within a single plane.  
      Thus, since the catheter-introducing sheath according to any of claim  6 ,  7  or  8  is constructed by connecting existing two-way connectors, design modification for fabricating a three-way connector is no longer necessary.  
      Also, in the catheter-introducing sheath according to any of claim  6 ,  7  or  8 , the two branching portions, one in the first branched connector and the other in the second branched connector, are located apart from each other and at offset position. Therefore, when a balloon catheter is inserted into one connector through its branch tube, the front end of the balloon catheter is prevented from being caught at the branching portion of the other connector, ensuring smooth insertion of the balloon catheter.  
      Moreover, the catheter-introducing sheath according to any of claim  6 ,  7  or  8  is constructed such that the axis of the branching tube of the first branched connector, the axis of the branching tube of the second branched connector, and the axis of the first passage do not lie within a single plane. Therefore, when a balloon catheter is inserted through the branching tube of the second branched connector, the incident of catheter entering the branching tube of the first branched connector and blocking the branching portion thereof will not occur, whereby a smooth insertion of the balloon catheter can be attained.  
      According to the invention described in claim  9 , there is provided a catheter introducer for introducing into a living body a catheter-inserting sheath which is used for performing the perfusion method of delivering, by way of perfusion, a drug to a paraaortic lymph node tumor, comprising: 
          a catheter-inserting sheath, and     a dilator; 
 
 wherein the catheter-inserting sheath comprises: 
    a first passage for allowing passage of the first catheter therethrough,     a second passage branching from the first passage and allowing the second catheter to pass therethrough, and     a third passage branching from the first passage and allowing the third catheter to pass therethrough.        

      According to the invention described in claim  10 , there is provided a catheter introducer for introducing into a living body a catheter-inserting sheath which is used for performing the perfusion method of delivering, by way of perfusion, a drug to a paraaortic lymph node tumor, comprising: 
          a catheter-inserting sheath, and     a dilator; 
 
 wherein the catheter-inserting sheath comprises: 
    a tubular body having a first passage for allowing passage of a catheter therethrough,     a first branched connector which is connected to an end of the tubular body and which has a second passage and a third passage, the second passage directly communicating, via a first end of the first branched connector, with the first passage and the third passage branching from the second passage, and     a second branched connector which is connected to a second end of the first branched connector, the second end being opposite the first end, and which has a fourth passage and a fifth passage, the fourth passage directly communicating with the second passage and the fifth passage branching from the fourth passage.        

      According to the invention described in claim  11 , the dilator of the catheter introducer as recited in claim  9  is inserted into the above-mentioned first passage. Also, according to the invention described in claim  12 , the dilator of the catheter introducer as recited in claim  10  is inserted into a passage formed by the first, second, and the third passage.  
      As described above, the catheter introducer according to any of claim  9 ,  10 , or  11  has a three-way sheath-introducer. Therefore, the number of instruments to be percutaneously inserted into the patient&#39;s body can be reduced, to thereby reduce the burden of the patient.  
      In the catheter introducer of the present invention, a dilator is inserted through straight-channel-forming passages among a plurality of passages. Therefore, insertion of the dilator into the sheath and removal therefrom can be performed smoothly.  
      According to the invention described in claim  13 , there is provided an oxygenated blood perfusion apparatus equipped with fluid discharge means for discharging bodily fluid out of a living body, bodily-fluid-oxygenating means for oxygenating the discharged bodily fluid, and feeding means for feeding oxygenated blood into the living body through a plurality of balloon catheters indwelled in the living body, wherein any one to three of said plurality of balloon catheters are respectively inserted into the living body through their corresponding catheter-inserting sheaths, each sheath comprising: 
          a first passage for allowing passage of the first catheter therethrough,     a second passage branching from the first passage and allowing the second catheter to pass therethrough, and     a third passage branching from the first passage and allowing the third catheter to pass therethrough.        

      According to the invention described in claim  14 , there is provided an oxygenated blood perfusion apparatus equipped with fluid discharge means for discharging bodily fluid out of a living body, bodily-fluid-oxygenating means for oxygenating the discharged bodily fluid, and feeding means for feeding oxygenated blood into the living body through a plurality of balloon catheters indwelled in the living body, wherein one to three of said plurality of balloon catheters are respectively inserted into the living body through their corresponding catheter-inserting sheaths, each sheath comprising: 
          a tubular body having a first passage for allowing passage of a catheter therethrough,     a first branched connector which is connected to an end of the tubular body and which has a second passage and a third passage, the second passage directly communicating, via a first end of the first branched connector, with the first passage and the third passage branching from the second passage, and     a second branched connector which is connected to a second end of the first branched connector, the second end being opposite the first end, and which has a fourth passage and a fifth passage, the fourth passage directly communicating with the second passage and the fifth passage branching from the fourth passage.        

      Thus, the oxygenated blood perfusion apparatus as recited in claim  13  or  14  includes a plurality of balloon catheters connected to the apparatus and inserted into a living body via catheter-inserting sheaths, each having three passageways. Thus, the number of instruments which are percutaneously introduced into the body or a blood vessel of the patient and indwelled therein can be reduced.  
      As described above, the present invention attains effective exposure of lymph nodes to a drug of high concentration. Also, the invention reduces or prevents adverse side effects attributable to the drug. Moreover, the invention reduces or prevents injury of organs which would otherwise occur due to stopped blood flow. Furthermore, the invention reduces or prevents organs that communicate with the right renal artery, the left renal artery, the celiac artery, the superior mesenteric artery and the inferior mesenteric artery from being injured due to loss of blood, etc. 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
      Various other objects, features, and many of the attendant advantages of the present invention will be readily appreciated as the same becomes better understood with reference to the following detailed description of the preferred embodiments when considered in connection with accompanying drawings, in which:  
       FIG. 1  is an explanatory view schematically showing the blood vessels and branches thereof and locations of catheters inserted according to an embodiment of the present invention;  
       FIG. 2  is an explanatory enlarged view of the area surrounded by a broken line in  FIG. 1 ;  
       FIG. 3  is a sketch of a non-branched introducer according to an embodiment of the present invention;  
       FIG. 4  is an elevational sectional view of a non-branched sheath according to an embodiment of the present invention;  
       FIG. 5  is a sketch of a three-way introducer according to an embodiment of the present invention;  
       FIG. 6  is an elevational sectional view of a three-way sheath according to an embodiment of the present invention;  
       FIG. 7  is an elevational sectional view of a balloon catheter according to an embodiment of the present invention;  
       FIG. 8  is an elevational sectional view of another balloon catheter according to an embodiment of the present invention;  
       FIG. 9  is an explanatory view showing the configurations of perfusion circuits A and B according to an embodiment of the present invention;  
       FIG. 10  is an explanatory view showing a settings display panel of a perfusion apparatus employed in the perfusion circuit A according to an embodiment of the present invention;  
       FIG. 11  is an explanatory view showing a settings display panel of a perfusion apparatus employed in the perfusion circuit B according to an embodiment of the present invention;  
       FIG. 12  is a flow chart of the perfusion process according to an embodiment of the present invention; and  
       FIG. 13  is a graph representing experimental data obtained in an embodiment of the present invention. 
    
    
     DETAILED DESCRIPTION OF THE INVENTION  
      Some embodiments of the present invention will next be described with reference to the drawings. The elements, configurations and the like described hereinbelow should not be construed as limiting the invention thereto. As will be appreciated, various modifications may be made without departing from the scope of the invention. For example, a non-branched sheath  40 - 1 , which is inserted into the right axillary artery in an embodiment, may be inserted into the brachial artery.  
       FIGS. 1 and 2  show an embodiment of the drug perfusion method according to the present invention as applied to a case in which a malignant pelvic tumor spreads to the paraaortic lymph nodes.  FIG. 1  is an illustration of the embodiment of the present invention showing the branches of blood vessels and the insertion positions of catheters. FIG.  2  shows an enlarged illustration showing the area enclosed by the broken line in  FIG. 1 . In  FIGS. 1 and 2 , balloon catheters hidden by blood vessels or equipment are represented by broken lines in order to facilitate understanding of the invention.  
      Firstly, the main organs and the branches of blood vessels around the aorta will be described. A blood vessel originating from the left ventricle of the heart  1  extends to the aorta  3  via the aortic arch  2 , and the aorta  3  is branched into the common right and left iliac arteries at the pelvis. The common right iliac artery communicates with the right femoral artery  5 , and the left common iliac artery communicates with the left femoral artery  6 .  
      The aortic arch  2  has a branch to the brachiocephalic artery  7 , and the brachiocephalic artery  7  is branched into the right subclavian artery  8  and the right common carotid artery. The right subclavian artery  8  runs on the lateral side of the first rib, where it changes its name to right axillary artery  9 . The aortic arch  2  has another branch to the left subclavian artery  10 , located downstream of the branch to the brachiocephalic artery  7 . The left subclavian artery  10  runs on the lateral side of the first rib, where it changes its name to left axillary artery  11 .  
      The aorta  3  has a branch en route to the celiac artery  12 , and the celiac artery  12  is branched into the splenic artery  15 , the gastric coronary artery  13 , and the common hepatic artery  14 . The splenic artery  15 , the gastric artery  13 , and the hepatic artery  14  communicate with the spleen  18 , the stomach  16 , and the liver  17 , respectively.  
      Downstream of the branch to the celiac artery  12 , the aorta  3  has another branch to the superior mesenteric artery  19 , which communicates with the small intestine (not shown). Downstream of the branch to the superior mesenteric artery  19 , the aorta  3  further has branches to the right renal artery  20  and left renal artery  21 , which communicate with the right kidney  22  and the left kidney  23 , respectively. Downstream of the branches to the right renal artery  20  and left renal artery  21 , the aorta  3  has a branch to the inferior mesenteric artery  24 , which communicates with the hindgut (not shown).  
      The first collateral pathway  29   a  extends between the common hepatic artery  14  and the superior mesenteric artery  19 , and the second collateral pathway  29   b  extends between the superior mesenteric artery  19  and the inferior mesenteric artery  24 .  
      Downstream of the branches to the right renal artery  20  and left renal artery  21 , the aorta  3  has 4 branches to the first to fourth lumbar arteries on each of the left and right sides. The first to fourth lumbar arteries communicate with the first to fourth paraaortic lymph nodes, respectively. The middle sacral artery  3   a  is branched from the branch point of the right femoral artery  5  and the left femoral artery  6 . The middle sacral artery  3   a  also has branches on the left and right sides to the fifth lumbar arteries. The left and right fifth lumbar arteries communicate with the respective fifth paraaortic lymph nodes. In  FIG. 1 , the first to fifth lumbar arteries are represented by reference numeral  25 , and the first to fifth paraaortic lymph nodes are represented by reference numeral  26 .  
      An artery branches into capillary vessels in each organ and tissue to supply nutrients and oxygen to the organ and the cells. After supplying nutrients and oxygen, blood receives waste products and carbon dioxide and returns to capillary vessels. The capillary vessels then merge to form a vein.  
      The right femoral vein  27  in the right lower limb and the left femoral vein  28  in the left lower limb merge at the abdomen to form the inferior vena cava  4 . The inferior vena cava  4  communicates with the right atrium of the heart downstream of the blood flow.  
      The following description is based on the assumption that a patient has a tumor in a paraaortic lymph node  26 . Examples of the primary focus of a tumor in the paraaortic lymph node include malignant pelvic tumors such as bladder cancer and uterus carcinoma. Bladder cancer is caused by canceration of the transitional epithelium, which covers the surface of the bladder and has high stretchability. Although bladder cancer tends to occur inside the bladder, similar lesions may also be found in the ureters and the renal pelvises, which are located upstream of urine flow. Uterus carcinoma includes uterus sarcoma, cervical carcinoma, and endometrial carcinoma, among others. When malignant pelvic tumors advance, tumor cells may spread to the paraaortic lymph nodes through the lymph ducts or the blood vessels around the bladder or the uterus.  
      Sheath introducers, sheaths, and catheters according to the present invention will next be described with reference to FIGS.  3  to  8 .  
       FIGS. 3 and 4  show the structure of a non-branched introducer  30  according to the present invention.  FIG. 3  is a sketch of the non-branched introducer  30  according to an embodiment of the present invention.  FIG. 4  is an elevational sectional view of a non-branched sheath  40  according to an embodiment of the present invention.  
      The non-branched introducer  30  is used as a guide for a balloon catheter when the catheter is percutaneously inserted into a blood vessel. The non-branched introducer  30  has, as primary components, the non-branched sheath  40 , a dilator  50 , and a guide wire  60 .  
      The non-branched sheath  40  has a tubular body  41  and a rear end portion  42  as major components. The tubular body  41  and the rear end portion  42  are connected together through a known technique such as application of an adhesive or melt adhesion.  
      The tubular body  41  is a flexible or rigid tubular member made of polytetrafluoroethylene (PTFE). The tubular body  41  has a passage provided therein, through which the opposite ends of the tubular body  41  communicate with each other. One end portion of the tubular body  41  has a diameter decreasing along the direction of insertion of the sheath. Thus, the tubular body  41  and the dilator  50  form no step therebetween, allowing smooth insertion of the non-branched introducer  30  into the blood vessel.  
      The rear end portion  42  is a flexible or rigid cylindrical member made of polytetrafluoroethylene (PTFE). The rear end portion  42  is attached to the rear end of the tubular body  41 . The rear end portion  42  has a passage provided therein which communicates with the passage of the tubular body  41 . In  FIG. 4 , the passage of the tubular body  41  and the passage of the rear end portion  42  together form a passage indicated by reference number  45 .  
      The rear end portion  42  has a hemostatic valve  43  provided therein made of an elastic material such as a synthetic rubber or a thermoplastic elastomer. The circumferential perimeter of the hemostatic valve  43  is held by sandwiching between the rear end portion  42  and a cap member  44 , to thereby fix the hemostatic valve  43  in the rear end portion  42 . The cap member  44  has a thread  44   a , with which the cap member  44  is engaged with a thread portion (not shown) provided in the rear end portion  50   a  of the dilator.  
      The hemostatic valve  43  is provided with a small hole  43   a  at a center portion thereof, through which opposite sides of the hemostatic valve  43  communicate with each other. A dilator or a balloon catheter is inserted into the passage  45  through the small hole  43   a.    
      The rear end portion  42  has a projection  42   a  extending from a circumferential portion thereof. The projection  42   a  has a side port  46  provided therein, through which the passage  45  communicates with the tip of the projection  42   a . A flexible tube  47  is connected to the projection  42   a , and a three-way cock  48  is attached to the other end of the flexible tube  47 .  
      The three-way cock  48  has a plurality of ports. The three-way cock  48  has a selector valve which functions to switch communication between the tube  47  and one of these ports. A liquid-feeding pump or a liquid-removing pump can be connected to the ports of the three-way cock  48 . Through use of such a liquid-feeding pump, a drug solution or other liquids (hereinafter simply referred to as “a drug solution”) is fed into a living body sequentially via the three-way cock  48 , the tube  47 , the side port  46 , and the passage  45 . Through use of such a liquid-removing pump, bodily fluid is removed from the living body sequentially via the passage  45 , the tube  47 , and the three-way valve  48 .  
      The dilator  50  is a flexible stick-shaped member made of polytetrafluoroethylene (PTFE). The dilator  50  is used for preventing the tubular body  41  from kinking on the occasion of insertion of the non-branched introducer  30  into the blood vessel. The dilator  50  has a tubular passage (not shown) provided therein for allowing the tip and rear ends of the dilator to communicate with each other. The guide wire  60  can be inserted into the tubular passage.  
      The dilator  50  is inserted into the passage  45  of the non-branched sheath  40  through the small hole  43   a  of the hemostatic valve  43 . The tip portion of the dilator  50  projects over the tip portion of the non-branched sheath  40 . The rear portion of the dilator  50  is adapted to screw into the thread  44   a  of the cap member  44 . This structure prevents relative movement between the dilator  50  and the non-branched introducer  30  which may otherwise occur when the introducer  30  is inserted into the blood vessel.  
      The guide wire  60  is a member for leading the tip portion of the dilator  50  to a target site. The guide wire  60  is a filament-shaped member made of a material such as stainless steel or a nickel-titanium alloy. The guide wire  60  is inserted into the tubular passage (not shown) of the dilator  50 . The tip portion of the guide wire  60  projects over the tip portion of the dilator  50 , and the rear end portion of the guide wire  60  projects over the rear end portion of the dilator  50 .  
       FIGS. 5 and 6  show the structure of a three-way introducer  31 .  FIG. 5  is a sketch of the three-way introducer  31  according to an embodiment of the present invention.  FIG. 6  is an elevational sectional view of a three-way sheath  70  according to an embodiment of the present invention.  
      The three-way introducer  31  is used as a guide for a balloon catheter when the catheter is percutaneously inserted into a blood vessel. The three-way introducer  31  has, as primary components, a three-way sheath  70 , a dilator  50 , and a guide wire  60 . The dilator  50  and the guide wire  60  may be the same as those employed in the above-mentioned non-branched introducer  30 .  
      The three-way sheath  70  has a tubular body  71 , a first branched connector  72 , a second branched connector  81 , a first rear portion  73 , a second rear portion  82 , and a third rear portion  90 .  
      The tubular body  71  is a flexible or rigid tubular member made of PTFE. The tubular body  71  has a length of 300 mm and a diameter of 5 mm, and has a passage  96  provided therein, through which the opposite ends of the tubular body  71  communicate with each other. One end portion of the tubular body  71  has a diameter decreasing along the direction of insertion of the sheath. Thus, the tubular body  71  and the dilator  50  form no step therebetween, allowing smooth insertion of the three-way introducer  31  into a blood vessel.  
      The first branched connector  72  is a flexible or rigid member made of a material such as PTFE. The first branched connector  72  has a cylindrical main tube  72   a , and a branch tube  72   b  branched from the main tube  72   a.    
      The main tube  72   a  is in the form of a hollow cylinder having a length of 25 mm and a diameter of 6 mm, and has a passage  76 , through which the opposite ends of the main tube  72   a  communicate with each other. One end of the main tube  72   a  is connected to one end of the tubular body  71  through a known technique such as adhesion. The passage  76  of the main tube  72   a  is connected directly to the passage  96  of the tubular body  71 . The other end of the main tube  72   a  is connected to a main tube  81   a  of the second branched connector  81 . The branch tube  72   b  is branched from the main tube  72   a  at a portion about 8 mm from the connection end of the main tube  72   a  to the tubular body  71 , such that the inner angle formed by the main tube  72   a  and the branch tube  72   b  is about 30°.  
      The branch tube  72   b  is in the form of a hollow cylinder having a length of 15 mm and a diameter of 6 mm, and has a passage  77 , through which the rear end of the branch tube  72   b  communicates with the passage  76 . The open end of the branch tube  72   b  is connected to a rear end portion  73 . The rear end portion  73  has a hemostatic valve  74  provided therein made of an elastic material such as a synthetic rubber or a thermoplastic elastomer. The circumferential perimeter of the hemostatic valve  74  is held by sandwiching between the rear end portion  73  and a cap member  75 , to thereby fix the hemostatic valve  74  in the rear end portion  73 . The hemostatic valve  74  is provided with a small hole  74   a  at a center portion of the valve  74 . A balloon catheter is inserted through the small hole  74   a  sequentially into the passages  77 ,  76 , and  96 .  
      The rear end portion  73  has a projection  73   a  extending from a circumferential portion thereof. The projection  73   a  has a side port  78  provided therein, through which the passage  77  communicates with the tip of the projection  73   a.    
      The second branched connector  81  is a flexible or rigid member made of PTFE. The second branched connector  81  is identical with the first branched connector  72  mentioned above, and has a main tube  81   a , and a branch tube  81   b  branched from the main tube  81   a.    
      The main tube  81   a  is in the form of a hollow cylinder having a length of 25 mm and a diameter of 6 mm, and has a passage  85 , through which the opposite ends of the main tube  81   a  communicate with each other. One end of the main tube  81   a  is connected to one end of the main tube  72   a  of the first branched connector  72  through a known technique such as adhesion. The passage  85  of the main tube  81   a  is connected directly to the passage  76  of the first branched connector  72 . The other end of the main tube  81   a  is connected to the third rear portion  90 . The branch tube  81   b  is branched from the main tube  81   a  at the point about 8 mm from the end of the main tube  81   a  connected to the first branched connector  72 , such that the inside angle formed by the main tube  81   a  and the branch tube  81   b  is about 30°.  
      The branch tube  81   b  is in the form of a hollow cylinder having a length of 15 mm and a diameter of 6 mm, and has a passage  86 , through which the rear end of the branch tube  81   b  communicates with the passage  85 . The open end of the branch tube  81   b  is connected to the second rear portion  82 . The second rear portion  82  has a hemostatic valve  83  provided therein made of an elastic material such as a synthetic rubber or a thermoplastic elastomer. The circumferential perimeter of the hemostatic valve  83  is held by sandwiching between the second rear portion  82  and a cap member  84 , to thereby fix the hemostatic valve  83  in the second rear portion  82 . The hemostatic valve  83  is provided with a small hole  83   a  at a center portion thereof, through which opposite sides of the hemostatic valve  83  communicate with each other. A balloon catheter is inserted through the small hole  83   a  sequentially into the passages  86 ,  85 ,  76 , and  96 .  
      The second rear portion  82  has a projection  82   a  extending from a circumferential portion thereof, through which opposite sides of the hemostatic valve  83  communicate with each other. The projection  82   a  has a side port  87  provided therein, through which the passage  86  communicates with the tip of the projection  82   a.    
      The third rear portion  90  is connected to the other end of the main tube  81   a . The third rear portion  90  has a hemostatic valve  91  provided therein made of an elastic material such as a synthetic rubber or a thermoplastic elastomer. The circumferential perimeter of the hemostatic valve  91  is held by sandwiching between the rear end portion  90  and a cap member  92 , to thereby fix the hemostatic valve  91  in the rear end portion  90 . The cap member  92  has a thread  92   a , with which the cap member  92  is engaged with a thread portion (not shown) provided in the rear end portion of the dilator  50   a . The hemostatic valve  91  is provided with a small hole  91   a  at a center portion thereof, through which opposite sides of the hemostatic valve  83  communicate with each other. A dilator or a balloon catheter is inserted through the small hole  91   a  sequentially into the passages  85  and  96 .  
      The third rear portion  90  has a projection  90   a  extending from a circumferential portion thereof. The projection  90   a  has a side port  93  provided therein, through which the passage  85  communicates with the tip of the projection  90   a.    
      Flexible tubes  79 ,  88 , and  94  are connected to the projections  73   a ,  82   a , and  90   a , respectively. Three-way cocks  80 ,  89 , and  95  are attached to the other ends of the flexible tubes  79 ,  88 , and  94 , respectively. Each of the three-way cocks has a plurality of ports. Through the tubes and the side ports, for example, introduction of saline into the passage  96  or removal of bodily fluid can be performed.  
      The second branched connector  81  is preferably identical with the first branched connector  72 . As these connectors, connectors generally used for two-way catheter sheaths may be employed. That is, according to the present invention, typical two-way connectors can effectively be utilized to produce three-way connectors. Thus, three-way sheaths can be produced at low cost without newly designing three-way connectors. In addition, through use of three or more two-way connectors, four-way sheaths or higher-way sheaths can be produced.  
      Moreover, since the first branched connector  72  and the second branched connector  81  are connected with each other as described above, the portion at which the passage  77  is branched from the passage  76  and the portion at which the passage  86  is branched from the passage  85  are spaced from each other by a predetermined distance. This structure prevents the tip of a balloon catheter inserted via one branch tube from being caught at the other branch portion formed by the main tube and the other branch tube. Thus, according to the present invention, smooth insertion of a balloon catheter can be performed.  
      Further, as shown in  FIG. 5 , the axis A of the branch tube of the first branched connector  72 , the axis B of the branch tube of the second branched connector  81 , and the axis C of the passage  96  are not coplanar. This structure successfully prevents a balloon catheter inserted via the branch tube of the second branched connector  81  from unfavorably entering into and plugging the branch tube of the first branched connector  72 , which may otherwise occur.  
      Next will be described balloon catheters employed in the present invention. In one embodiment of the present invention, three types of balloon catheters are used.  
       FIG. 7  is an elevational sectional view of a balloon catheter  32  according to such an embodiment of the present invention. In the present embodiment, the balloon catheter  32  is used as a first balloon catheter. The balloon catheter  32  has, as primary components, a basal portion  101 , a rear end portion  102 , a branch tube  102   b , a balloon  104 , a front coil marker  105 , a tubular passage  108 , a lumen  106 , a syringe  109   a , and a plunger  109   b.    
      The basal portion  101  is a flexible member made of a resin such as polyethylene, polyethylene terephthalate, nylon, or polyester. The basal portion  101  has the tubular passage  108  provided therein. Through the tubular passage  108 , the rear end of the rear end portion  102  communicates with a balloon-inflating opening  103  provided at a center portion of the balloon  104 . The rear end portion  102  is connected to the syringe  109   a  enclosing a liquid (not shown) such as saline. When an operator applies pressure on the plunger  109   b  of the syringe  109   a , the liquid flows through the tubular passage  108  and the balloon-inflating opening  103  into the inner space of the balloon  104 .  
      The balloon  104  is a flexible member made of a resin such as polyethylene, polyethylene terephthalate, nylon, or polyester. The material forming the balloon  104  is softer than that of the basal portion  101 . In addition, the wall forming the balloon  104  is thinner than that of the basal portion  101 . Thus, when the liquid flows into the inner space of the balloon  104 , the balloon  104  inflates. The balloon  104  is inflated until the balloon  104  comes into close contact with the inside wall of the blood vessel, to thereby block the blood flow in the blood vessel.  
      The basal portion  101  has a lumen  106  provided therein. Through the lumen  106 , the rear end of the branch tube  102   b  communicates with side openings  107 . The side openings  107  are provided in the basal portion  101  between the balloon  104  and the tip end of the basal portion  101 . Therefore, even after the balloon  104  is inflated to plug the blood vessel, a drug solution can be fed through the lumen  106  to the region where the tip end of the basal portion exists and which is blocked by the balloon.  
      The rear end of the branch tube  102   b  may be connected to, for example, a syringe containing a drug solution or a liquid-feeding pump (not shown). Through use of such a syringe or a pump, a drug or other substances can be fed through the lumen  106  and the side openings  107  to the region where the tip end of the basal portion exists and which is defined by the blood vessel and the balloon which blocks blood flow.  
      The front coil marker  105  is made of a radiopaque material such as titanium. The front coil marker  105  allows an operator to specify the position of the tip of the balloon catheter  32  when carrying out an intervention under radioscopy. Provision of the front coil marker  105  enables the operator to selectively advance the balloon  104  toward the target site through confirmation of the position of the front coil marker  105  during angiography under X-ray fluoroscopy.  
       FIG. 8  is an elevational sectional view of another balloon catheter  33  according to an embodiment of the present invention. The balloon catheter  33  is used as a second balloon catheter in the embodiment according to the present invention. The balloon catheter  33  has a basal portion  111 , a rear end portion  112 , a branch tube  112   b , an inflatable balloon  114 , a front coil marker  115 , a tubular passage  118 , a lumen  116 , a syringe  119   a , and a plunger  119   b.    
      The basal portion  111 , the rear end portion  112 , the branch tube  112   b , the balloon  114 , the front coil marker  115 , the tubular passage  118 , the syringe  119   a , and the plunger  119   b  have structures similar to those of the basal portion  101 , the rear end portion  102 , the branch tube  102   b , the balloon  104 , the front coil marker  105 , the tubular passage  108 , the syringe  109   a , and the plunger  109   b , respectively, of the balloon catheter  32 .  
      The difference between the balloon catheter  32  and the balloon catheter  33  resides in the location of side openings  117  provided in the basal portion  111 . Specifically, the basal portion  111  has a lumen  116  provided therein, through which the rear end of the branch tube  112   b  communicates with the side openings  117 . The side openings  117  are provided in the basal portion  111  between the balloon  114  and the rear end of the basal portion  111 . Therefore, even after the balloon  114  is inflated to plug the blood vessel, a drug solution can be fed through the lumen  116  to the region where the rear end of the basal portion exists and which is blocked by the balloon, or bodily fluid or other liquids can be removed from the region.  
      Different from typical balloon catheters used in the medical field, the balloon catheters  32  and  33  employed in the present invention have a basal portion containing both the tubular passage used for inflation of the balloon and the lumen used for administration of a drug solution. Use of either balloon catheter alone enables the operator to simultaneously inflate the balloon and administer a drug solution. Therefore, there is no need to insert two catheters into the body; i.e., a balloon catheter for blocking the blood vessel and a catheter for administration of a drug solution, thereby reducing the burden placed on the patient&#39;s body.  
      A balloon catheter  34  is used as a third balloon catheter in the embodiment according to the present invention. Different from the above-described balloon catheters  32  and  33  the balloon catheter  34  is a typical balloon catheter used in the field of the medicine. Specifically, the balloon catheter  34  has a basal portion, a rear end portion, and a balloon, but has no lumen for administration of a drug solution as provided in the balloon catheters  32  and  33 .  
      The balloon catheters  32 ,  33 , and  34  in the above-mentioned embodiment of the invention are constituted such that the balloon catheters themselves are inserted into the blood vessel without use of any guide wire. However, these balloon catheters may be of an overwire type, an RX type, or a monorail type, each of which uses a guide wire.  
      The introducers  30  and  31  and the balloon catheters  32 ,  33 , and  34  are constituted as above. A balloon catheter is inserted into a blood vessel and indwelled at a predetermined position by use of an introducer; this step will next be described with reference to  FIG. 1 .  
      In this embodiment, a balloon catheter of the type such as the balloon catheter  32  shown in  FIG. 7  is employed to block the celiac artery  12 , the superior mesenteric artery  19 , the inferior mesenteric artery  24 , the right renal artery  20 , and the left renal artery  21 . Since the lumen  106  is provided inside the balloon catheter  32  so as to communicate with the tip side of the balloon  104 , oxidized blood can be fed into the organ side through the lumen  106  after the balloon  104  is inflated.  
      In this embodiment, a balloon catheter of the type such as the balloon catheter  33  shown in  FIG. 8  is employed to block the aorta  3 . Since the lumen  116  is provided inside the balloon catheter  33  so as to communicate with the rear side of the balloon  114 , a drug solution such as a contrast medium can be fed into the area where the vessels are blocked through the lumen  116  after the balloon  114  is inflated.  
      Further, in this embodiment, the balloon catheter  34  is employed to block the inferior vena cava  4 . The balloon catheter  34  does not have a lumen and is used merely to block blood flow through inflation.  
      The balloon catheters  32 ,  33 , and  34  are introduced into a living body through the non-branched sheath  40  or the three-way sheath  70 . A method for percutaneously introducing the sheath used to insert the balloon catheter will next be described.  
      Firstly, a site of the skin above the target vessel for insertion is subjected to local anesthesia in preparation for introducing the non-branched sheath  40 . After the effect of the anesthesia is confirmed, the anesthetized position is punctured by use of a known puncture needle or a similar needle. The guide wire  60  is then inserted into the vessel from the punctured portion and allowed to indwell at a predetermined position.  
      The rear end of the guide wire  60  is then inserted into the passage of the dilator  50 , and the tip end of the non-branched introducer  30  is slowly inserted into the vessel percutaneously until the rear end of the guide wire  60  appears from the rear end of the dilator  50 . The insertion of the non-branched introducer  30  is stopped when the tubular body  41  of the non-branched sheath  40  is located at a predetermined position in the vessel, and the non-branched sheath  40  is indwelled thereto.  
      Subsequently, the guide wire  60  is pulled out from the vessel to the outside of the body. The engagement between the thread  44   a  in the cap member  44  provided in the rear end portion  42  and the thread portion of the dilator  50  is released, and the dilator  50  is pulled out from the passage  45  of the non-branched sheath  40  to the outside of the body, to thereby indwell the tip end of the non-branched sheath  40  inside the body percutaneously. In this way, the tip end of the non-branched sheath  40  is inserted into the vessel.  
      In  FIG. 1 , the non-branched sheaths  40  are inserted into a living body. In this embodiment, the non-branched sheaths  40  are employed as sheaths to be inserted into the right axillary artery  9 , the left axillary artery  11 , the left femoral artery  6 , and the right femoral vein  27 . In  FIG. 1 , the non-branched sheaths  40  inserted into these vessels are represented by reference numerals  40 - 1 ,  40 - 2 ,  40 - 3 , and  40 - 4 .  
      The non-branched sheath  40 - 3  is placed inside the aorta  3  such that the tip end of the tubular body  41  is located around the lumbar arteries  25 ; an anticancer agent will be administered through the non-branched sheath  40 - 3 .  
      The three-way sheath  70  is inserted into a vessel by means of the three-way introducer  31  through the same method employed for inserting the non-branched sheath  40  into a vessel. In this embodiment, the three-way sheath  70  is inserted through the right femoral artery  5 .  
      The balloon catheters  32 ,  33 , and  34  are introduced into a vessel through the non-branched sheath  40  or the three-way sheath  70  and indwelled at predetermined positions; this step will next be described.  
      In  FIG. 1 , reference numerals  32 - 1  and  32 - 2  denote the balloon catheters  32  introduced into a vessel through the non-branched sheaths  40 - 1  and  40 - 2 , which are inserted into the right axillary artery  9  and the left axillary artery  11 , respectively, and indwelled at the right renal artery  20  and left renal artery  21 , respectively.  
      Reference numerals  32 - 3 ,  32 - 4 , and  32 - 5  denote the balloon catheters  32  introduced into a vessel through the three-way sheath  70 , which is inserted into the right femoral artery  5 , and indwelled at the celiac artery  12 , the superior mesenteric artery  19 , and the inferior mesenteric artery  24 , respectively.  
      The balloon catheter  33  is introduced into a vessel through the non-branched sheath  40 - 3 , which is inserted into the left femoral artery  6 , and indwelled in the aorta  3  at a predetermined position thereof. The balloon catheter  34  is introduced into a vessel through the non-branched sheath  40 - 4 , which is inserted into the right femoral vein  27 , and indwelled in the inferior vena cava  4  at a predetermined position thereof.  
      The balloon catheter  32 - 1  is introduced into a vessel through the non-branched sheath  40 - 1 , which is inserted into the right axillary artery  9 , and indwelled in the right renal artery  20  at a predetermined position thereof; the method for introducing and indwelling the catheter will next be described.  
      The balloon  104  of the balloon catheter  32 - 1  is initially in a deflated state. The tip end of the balloon catheter  32 - 1  is introduced into the passage  45  of the tubular body  41  through the small hole  43   a  provided in the hemostatic valve  43  of the non-branched sheath  40 - 1 , and inserted into the right axillary artery  9 .  
      The operator operates and guides the balloon catheter  32 - 1  while observing X-ray images obtained from fluororoentgenography such that the tip end is located at a predetermined position in the right renal artery  20 , to thereby indwell the balloon catheter  32 - 1  therein.  
      The method described above may be employed to introduce the balloon catheter  32 - 2  into a vessel through the non-branched sheath  40 - 2 , which is inserted into the left axillary artery  11 , and to indwell the catheter in the left renal artery  21  at a predetermined position thereof. The method described above is also used to introduce the balloon catheters  32 - 3 ,  32 - 4 , and  32 - 5  into vessels through the three-way sheath  70 , which is inserted into the right femoral artery  5 , and to indwell the catheters at predetermined positions in the celiac artery  12 , the superior mesenteric artery  19 , and the inferior mesenteric artery  24 , respectively.  
      The method described above may also be employed to introduce the balloon catheter  33  into a vessel through the non-branched sheath  40 - 3 , which is inserted into the left femoral artery  6 , and to indwell the catheter in the aorta  3  at a predetermined position thereof. The method described above may also be employed to introduce the balloon catheter  34  into a vessel through the non-branched sheath  40 - 4 , which is inserted into the right femoral vein  27 , and to indwell the catheter in the inferior vena cava  4  at a predetermined position thereof.  
      No particular limitations are imposed on the insertion positions of catheters and balloon sheaths, but sheaths and balloon catheters are preferably inserted into different vessels such as the right axillary artery, the left axillary artery, the right femoral artery, the left femoral artery, and the right femoral vein as described above. This is because, when a plurality of sheaths or balloon catheters are introduced through the same vessel, the sheath or the catheter which has already been introduced may interfere with insertion of the next sheath or catheter. Also, passing of a plurality of sheaths or balloon catheters through a channel in a narrow blood vessel is likely to impose a burden on a patient and damage a sheath or catheter.  
      Preferably, the three-way sheath  70  is inserted through the femoral artery. The three-way sheath  70  has a large diameter, since three catheters are introduced therethrough. The femoral artery has a diameter large enough to pass the three-way sheath  70 , and thus is preferable for introduction.  
      Preferably, the balloon catheter  33  is also inserted through the femoral artery. The balloon catheter  33  is used to block the aorta and has a larger diameter. The femoral artery has a diameter large enough to pass the balloon catheter  33  and thus is preferable for introduction.  
      A method for placing a tourniquet on the lower limb will next be described. In  FIG. 1 , reference numeral  35 - 1  denotes a tourniquet  35  applied to the right femoral region, and reference numeral  35 - 2  denotes a tourniquet  35  applied to the left femoral region.  
      A tourniquet comprises a flexible belt containing an inflatable tube, and pressurizing equipment connected to the tube as main components. In order to apply the tourniquet, the flexible tube is first rolled around the application area and firmly tied so as not to be loosened. The tourniquet  35 - 1  is applied to the right femoral region lower than the introduction positions of the three-way sheath  70  and the non-branched sheath  40 - 4 . The tourniquet  35 - 2  is applied to the left femoral region lower than the introduction position of the non-branched sheath  40 - 3 .  
      The tourniquet  35 - 1  inflates when air or liquid is fed into the tube contained therein from pressurizing equipment (not shown). Upon inflation, vessels in the mounted position of the tourniquet are stressed, to thereby block blood flow to/from arteries and veins in the right lower limb. This is also the case for the tourniquet  35 - 2 , and blood flow to/from arteries and veins in the left lower limb is blocked when the tourniquet  35 - 2  is inflated.  
      The balloon  104  of the balloon catheter  32 - 1  is indwelled at a predetermined position in the right renal artery  20 , and the plunger  109   b  of the syringe  109   a  is then pushed in, to thereby pass the liquid contained in the syringe  109   a  into the tubular passage  108  of the basal portion  101 . The liquid in the tubular passage  108  is fed into the balloon  104  to inflate the balloon  104 . The inflated balloon  104  tightly fits against the inner wall of the right renal artery  20  to form a blood flow blocked portion, whereby drug flow from the aorta  3  to the right kidney  22  is blocked.  
      The same method as above may be performed to block blood flow in the left renal artery  21  through inflation of the balloon  104  of the balloon catheter  32 - 2 , whereby drug flow from the aorta  3  to the left kidney  23  is blocked.  
      The same method as above may be performed to block blood flow in the celiac artery  12  through inflation of the balloon  104  of the balloon catheter  32 - 3 , whereby drug flow from the aorta  3  to the stomach  16 , the liver  17 , and the spleen  18  is blocked.  
      The same method as above may be performed to block blood flow in the superior mesenteric artery  19  through inflation of the balloon  104  of the balloon catheter  32 - 4 , whereby drug flow from the aorta  3  to the small intestine is blocked.  
      The same method as above may be performed to block blood flow in the inferior mesenteric artery  24  through inflation of the balloon  104  of the balloon catheter  32 - 5 . In this way, drug flow from the aorta  3  to the hindgut is blocked.  
      The same method as above may be performed to block blood flow at a predetermined position in the aorta  3  through inflation of the balloon  114  of the balloon catheter  33 . In this way, backflow of a drug from downstream of the aorta  3  to the heart and the upper limb is prevented.  
      The same method as above may be performed to block blood flow at a predetermined position in the inferior vena cava  4  through inflation of the balloon of the balloon catheter  34 . In this way, backflow of a drug from the aorta  3  to the inferior vena cava in the upper limb is prevented.  
      By means of the above steps, a blood-flow-blocked region can be provided in a region where blood flow is blocked by means of the tourniquets  35 - 1  and  35 - 2  and balloon inflation regions of the balloon catheters  32 - 1 ,  32 - 2 ,  32 - 3 ,  32 - 4 ,  32 - 5 ,  33 , and  34 .  
       FIG. 9  is an illustration showing the configuration of a perfusion circuit according to an embodiment of the present invention. A method for administering a drug in the aorta blocked through the above technique will next be described. In this embodiment, two types of perfusion are performed. One is performed to protect organs (organ-protecting perfusion A), and the other is performed to administer a drug such as an anticancer agent (drug-administering perfusion B).  
      (Organ-Protecting Perfusion A)  
      In this type of perfusion, venous blood drained from the superior and inferior vena cavas is oxygenated by means of an artificial lung, and the oxygenated blood is fed into the right renal artery  20 , the left renal artery  21 , the celiac artery  12 , the superior mesenteric artery  19 , and the inferior mesenteric artery  24 . This type of perfusion is performed in order to protect organs, in which blood supply is blocked by inflation of balloons, through feeding of oxygenated blood.  
      The configuration of equipment for performing the organ-protecting perfusion comprises venous cannulas  121  and  122  for removal of blood, a drainage tube  123 , a reservoir  124 , a pump  125 , an artificial lung  126 , a heat exchanger  127 , a filter  128 , a feeding tube  129 , and balloon catheters  32 - 1 ,  32 - 2 ,  32 - 3 ,  32 - 4 ,  32 - 5 .  
      The venous cannulas  121  and  122  are inserted through the jugular by means of a known method and indwelled in the superior vena cava and the inferior vena cava, respectively. Venous blood is drained to the outside of the body by means of the two cannulas and, via the drainage tube  123 , stored in the reservoir  124 . A flow sensor or a similar sensor may be provided between the cannulas  121 ,  122  and the reservoir  124 . The venous blood stored in the reservoir  124  is fed into the artificial lung  126  by means of the pump  125 . A known pump such as a roller pump or a centrifugal pump may be employed as the pump  125 .  
      The venous blood fed into the artificial lung  126  undergoes gas exchange of carbon dioxide and oxygen, to thereby produce oxygenated blood containing a large amount of oxygen. In the artificial lung  126 , gases are exchanged by use of a membrane such as a hollow fiber membrane or a film membrane. The artificial lung  126  is equipped with the heat exchanger  127 . The heat exchanger  127  provides temperature control of blood. In the heat exchanger  127 , blood temperature is controlled by warm or cold water through a medium having a high heat conductivity such as a metal plate.  
      The oxygenated blood gas-exchanged in the artificial lung  126  is filtrated by means of the filter  128  and then returned to arteries. In the filter  128 , foreign substances such as blood clots and air bubbles are removed. The oxygenated blood passing through the filter  128  is fed into arteries through the feeding tube  129  and then the balloon catheters  32 - 1 ,  32 - 2 ,  32 - 3 ,  32 - 4 , and  32 - 5 .  
      The oxygenated blood passing through the balloon catheter  32 - 1  is fed into the right renal artery  20  through the lumen  106  and supplied to the right kidney  22 . The oxygenated blood passing through the balloon catheter  32 - 2  is fed into the left renal artery  21  through the lumen  106  and supplied to the left kidney  23 .  
      The oxygenated blood passing through the balloon catheter  32 - 3  is fed into the celiac artery  12  through the lumen  106  and supplied to the stomach  16 , the liver  17 , and the spleen  18 . The oxygenated blood passing through the balloon catheter  32 - 4  is fed into the superior mesenteric artery  19  through the lumen  106  and supplied to the small intestine. The oxygenated blood passing through the balloon catheter  32 - 5  is fed into the inferior mesenteric artery  24  through the lumen  106  and supplied to the hindgut.  
      In another conceivable embodiment, oxygenated blood is fed into any one or two catheters selected from the balloon catheters  32 - 3 ,  32 - 4 , and  32 - 5  and is not fed into the other catheters.  
      As shown in  FIG. 2 , the common hepatic artery  14  and the superior mesenteric artery  19  communicate through the first collateral pathway  29   a  extending therebetween, and the superior mesenteric artery  19  and the inferior mesenteric artery  24  communicate through the second collateral pathway  29   b  extending therebetween. Therefore, oxygenated blood is not necessarily fed into all of the three arteries; i.e., the common hepatic artery  14 , the superior mesenteric artery  19 , the inferior mesenteric artery  24 , and oxygenated blood can be supplied to all of the above three arteries by feeding only one or two arteries. In this embodiment, a complicated operation that oxygenated blood is fed into the all above three arteries is unnecessary.  
      In particular, oxygenated blood is preferably fed only into the balloon catheter  32 - 4  inserted into the superior mesenteric artery  19 . Since the small intestine may be greatly damaged when an insufficient amount of oxygen is supplied, oxygenated blood must be preferentially fed into the superior mesenteric artery  19 , which communicates with the small intestine. Meanwhile, the other organs may not be greatly damaged even when blood supply is interrupted for a short period of time, and oxygenated blood supplied through the collateral pathways  29   a  and  29   b  may be sufficient to protect the organs.  
      In this case, a balloon catheter into which oxygenated blood is not fed is not necessarily a balloon catheter having a lumen such as the balloon catheter  32 , and may be a conventional balloon catheter without a lumen such as the balloon catheter  34 .  
       FIG. 10  is an illustration showing a settings display panel  161  of a controller  160  of the embodiment of the present invention employed in perfusion A. The settings display panel  161  is a screen for presetting various values of a perfusion apparatus used in perfusion A and for confirming the operating conditions, and comprises an oxygenated blood perfusion settings display  162 , an operation display  163 , a running/stopped display  164 , and an oxygenated blood feeding key  165 .  
      The oxygenated blood perfusion settings display  162  comprises a feed rate settings display  166  for displaying the “feed rate set value” of oxygenated blood, a perfusion time settings display  167  for displaying the “perfusion time set value,” and an oxygen saturation settings display  168  for displaying the “oxygen saturation set value” (i.e., the oxygen saturation (SO 2 ) in blood).  
      A function key  169  is used to sequentially switch, by pushing the key, a display to which set value can be input, between the feed rate settings display  166 , the perfusion time settings display  167 , and the oxygen saturation settings display  168 . Set values can be continuously changed by means of an up key  170  and a down key  171 .  
      Signals corresponding to the preset values of the feed rate settings display  166 , the perfusion time settings display  167 , and the oxygen saturation settings display  168  are transmitted to the controller  160 , and the controller  160  can start and control the pump  125  to achieve predetermined operations such that a predetermined amount of blood or other fluid is perfused within a predetermined period of time.  
      In response to operation of the oxygenated blood feeding key  165  at any time during operation, a signal corresponding to the “feed rate set value” displayed on the feed rate settings display  166  is transmitted to the controller  160 , and the controller  160  can start and control the pump  125  to achieve predetermined operations.  
      When the running/stopped display  164  is pressed at startup, a signal corresponding to the “feed rate set value” displayed on the feed rate settings display  166  is transmitted to the controller  160 , and the controller  160  starts and controls the pump  125  to achieve predetermined operations.  
      The operation display  163  displays the states of the respective operations during running and includes a running/stopped display  172  for displaying a running or stopped state, a total feed amount display  173  for displaying the total amount of oxygenated blood fed, an oxygen saturation display  174  for displaying oxygen saturation, and a remaining perfusion time display  175  for displaying the remaining time of perfusion. The value displayed on the total feed amount display  173  is calculated from a value measured by means of a flow sensor or similar sensor.  
      Operation of the controller  160  will next be described. An operator sets the “feed rate set value,” the “perfusion time set value,” and the “oxygen saturation set value” by use of the settings display panel  161 . Thereafter, the anticancer agent perfusion apparatus dotted a line in  FIG. 9  is activated by pressing of the running/stopped display  164 . Specifically, the controller  160  starts and controls the pump  125  and the artificial lung  126  on the basis of the set values displayed on the oxygenated blood perfusion settings display  162 . At this point in time, the running/stopped display  164  is changed from “stop” to “start.” 
      As shown in  FIG. 9 , venous blood is first stored in the reservoir  124  via the cannulas  121  and  122  and then the drainage tube  123  through the suction and discharge operations of the pump  125 .  
      The venous blood stored in the reservoir  124  is fed into the artificial lung  126  through operation of the pump  125 . In the artificial lung  126 , the venous blood is subjected to oxygenation under the control by the controller  160 . An dissolved oxygen sensor is provided in the artificial lung  126 , and the controller  160  controls the operation of the artificial lung  126  in a feedback manner according to the measurements of the dissolved oxygen sensor such that the oxygen saturation in the oxygen saturation settings display  168  is maintained.  
      The oxygenated venous blood is fed into the feeding tube  129  through the suction and discharge operations of the pump  125 . The oxygenated blood passes through the filter  128  and is fed inside the body through the balloon catheters  32 - 1 ,  32 - 2 ,  32 - 3 ,  32 - 4 , and  32 - 5  at a predetermined flow rate adjusted by means of a feeding pump.  
      When the oxygenated blood perfusion is applied for a predetermined period of time, a counter (not shown) provided in the controller  160  is activated, and the controller  160  stops the pump  125  and the artificial lung  126 . At this point in time, the running/stopped display  172  is changed from “start” to “stop.” 
      (Perfusion B for Administering A Drug)  
      In the perfusion B, a drug solution containing an anticancer agent is administered through the non-branched sheath  40 - 3 , and a drug-containing bodily fluid is collected through the non-branched sheath  40 - 4 .  
      In the perfusion B, circulation is performed through a circuit containing the non-branched sheath  40 - 3 , the non-branched sheath  40 - 4 , a discharge tube  131 , a discharge pump  132 , a reservoir  133 , a feeding pump  134 , a feeding tube  135 , a drug feeder  136 , a controller  137 , flow rate sensors  138 - 1  and  138 - 2 , and a settings display panel  139 .  
      The three-way cock  48  of the non-branched sheath  40 - 4  is connected to the discharge tube  131 . The discharge tube  131  is connected to the reservoir  133 . The discharge tube  131  is provided with the flow rate sensor  138 - 2  and the discharge pump  132 .  
      Blood is drawn from the inferior vena cava under suction generated by the discharge pump  132 , and then flows sequentially through the passage  45 , the side port  46 , the flexible tube  47 , and the three-way cock  48  of the non-branched sheath  40 - 4  into the discharge tube  131 . Subsequently, the blood is delivered to the reservoir  133 . The discharge pump  132  employed in the present invention may be a known pump such as a roller pump or a centrifugal pump.  
      The discharge tube  131  is connected with the reservoir  133 , which is connected to the drug feeder  136 . The drug feeder  136 , which is an apparatus for feeding an anticancer agent into the discharge tube  131 , contains a syringe pump and is controlled by the controller  137 .  
      The syringe pump has a worm gear structure or a ball screw structure, and is able to feed a predetermined amount of a drug contained in the syringe by maintaining the syringe body in a stationary state and moving a piston by a predetermined distance through use of a slider. The anticancer agent stored in the reservoir  133  is drawn under suction made by the feeding pump  134  and delivered into the body by means of the pump  134 .  
      One or more additional feeders containing a necessary agent such as infusion liquid, saline, or an anticoagulant may be provided in the blood circuit in a manner similar to that of the drug feeder  136 , for adding the necessary agent to the circuit of the perfusion B in a predetermined amount. Thus, proportions of necessary agent, anticancer agent, and blood can be set or controlled arbitrarily.  
      The flow rate sensor  138  may include a Doppler ultrasound flow meter, which enables measurement of volumes of blood collected from or delivered into the body without coming into direct contact with the liquid to be measured containing an anticancer agent, blood, or others. Other ultrasound-based flow rate measuring methods include, in addition to the Doppler method, the time difference method and sing-around method. Any of these methods may be employed to construct a sensor.  
      The flow rate sensor  138  has a transmitting piezoelectric element (not shown) which generates ultrasonic waves into the flow, and a receiving piezoelectric element (not shown) which receives a Doppler signal. The transmitting piezoelectric element transmits ultrasonic waves to the flow containing blood flowing through the feeding tube  135  or the discharge tube  131 . The receiving piezoelectric element receives a Doppler signal corresponding to the flow rate of the blood-containing flow.  
      The received signal is amplified in an amplifier (not shown). High-frequency components of the resultant signal are removed by a low-pass filter, and then transmitted to the controller  137  as a measurement value corresponding to the flow rate.  
      In the embodiment shown, the flow rate sensors  138 - 1  and  138 - 2  are disposed around the feeding tube  135  and the discharge tube  131 , respectively. Alternatively, the flow rate sensor  138 - 1  may be disposed in a flow channel (not shown) within the feeding pump  134  in place of the surroundings of the feeding tube  135 . Similarly, the flow rate sensor  138 - 2  may be disposed in a flow channel (not shown) within the discharge pump  132  in place of the surroundings of the discharging tube  131 .  
       FIG. 11  shows the settings display panel  139  of the controller  137  employed in the perfusion B. The settings display panel  139  is a screen for presetting various values for performing the anticancer agent perfusion therapy and for confirming the operating conditions. The settings display panel  139  comprises an anticancer agent perfusion settings display  141 , an operation display  142 , an start/stop switch  143 , and an anticancer agent administration key  144 .  
      The anticancer agent perfusion settings display  141  comprises a feed rate settings display  145  for displaying the “feeding rate set value” of the anticancer agent-containing blood or the like, a discharge rate settings display  146  for displaying the “discharge rate set value” of the blood or the like, a perfusion time settings display  147  for displaying the “perfusion time set value,” and a anticancer agent feeding amount settings display  148  for displaying the “the anticancer agent amount set value” representing the amount of the agent to be fed into the body within a time period of an operation.  
      A function key  149  is used to sequentially switch, by pushing the key, a display to which set value can be input, between the feed rate settings display  145 , the discharge rate settings display  146 , the perfusion time settings display  147 , and the anticancer agent feed amount settings display  148 . Set values can be continuously changed by means of an up key  157  and a down key  158 .  
      Signals corresponding to the set values of the feed rate settings display  145 , the discharge rate settings display  146 , and the perfusion time settings display  147  are transmitted to the controller  137 , and the controller  137  can start and control the feeding pump  134  and the discharge pump  132  to achieve predetermined operations such that a predetermined amount of blood or other fluid is perfused within a predetermined period of time.  
      By operating the anticancer agent administration key  144  at any time during operation, a signal corresponding to the “the anticancer agent feed amount set value” displayed on the anticancer agent feed amount settings display  148  is transmitted to the controller  137 , and the controller  137  can start and control the drug feeder  136  to achieve predetermined operations.  
      By pressing the start/stop switch  143  at startup, a signal corresponding to the “anticancer agent perfusion time set value” displayed on the anticancer agent perfusion time settings display  148  is transmitted to the controller  137 , and the controller  137  starts and controls the drug feeder  136  to achieve predetermined operations.  
      The operation display  142  displays the states of the respective operations during running and includes a running/stopped display  152  for displaying a state of running or being stopped, a total anticancer agent feed amount display  153  for displaying the total amount of anticancer agent fed, a total feed amount display  154  for displaying the total amount of blood or other fluid fed, a total discharge amount display  155  for displaying the total amount of blood or other fluid discharged, and a remaining perfusion time display  156  for displaying the remaining time of perfusion.  
      The displayed value on the total anticancer agent feed amount display  153 , indicating the total amount of the anticancer agent fed, is calculated by use of the “feed amount set value” displayed on the anticancer agent feed amount settings display  148  together with the number of times the anticancer agent administration key  144  is pressed. The displayed value on the total feed amount display  154  is calculated from the value measured by means of the flow rate sensor  138 - 1 . The displayed value on the total discharge amount display  155  is calculated from the value measured by means of the flow rate sensor  138 - 2 .  
      The operation of the anticancer agent perfusion apparatus will next be described. An operator sets the “feed rate set value,” the “discharge rate set value,” the “perfusion time set value,” and the “anticancer agent feed amount set value” by use of the settings display panel  139 . Thereafter, the anticancer agent perfusion apparatus dotted a line in  FIG. 9  is activated by switch-on of the start/stop switch  143 . Specifically, the controller  137  starts and controls the feeding pump  134 , the discharge pump  132 , and the drug feeder  136  in accordance with the set values displayed on the anticancer agent perfusion settings display  141 . At this point in time, the running/stopped display  152  is changed from “stop” to “running.” 
      As shown in  FIG. 9 , firstly, the anticancer agent contained in the drug feeder  136  is introduced into the blood circuit. The anticancer agent is delivered to the feeding tube  135  by means of the pump  134 .  
      The anticancer agent has been stored in advance in the reservoir  133  in the form of a mixture with saline, the mixture having an appropriate anticancer agent concentration. The anticancer agent contained in the reservoir  133  is delivered into the feeding tube  135  by means of the feeding pump  134 . Subsequently, the anticancer agent is delivered through the non-branched sheath  40 - 3  into the body at a predetermined flow rate adjusted by means of the feeding pump  134 .  
      Specifically, the flow rate sensor  138 - 1  measures the flow rate of the anticancer agent delivered through the feeding tube  135  and transmits a signal corresponding to the flow rate to the controller  137 . If the deviation of the flow rate value reflected by the signal from the “feeding rate set value” is greater than a predetermined threshold, the controller  137  controls the feeding pump  134  in a feedback manner, whereby the flow rate is recovered and maintained to the “feeding rate set value.” 
      When the feeding pump  134  is activated, the anticancer agent fed through the feeding tube  135  is delivered intracorporeally by way of perfusion. Bodily fluid containing the anticancer agent is delivered through the non-branched sheath  40 - 4  into the discharging tube  131 . The bodily fluid is delivered by means of the discharge pump  132  into the reservoir  133 .  
      To the bodily fluid contained in the reservoir  133 , the anticancer agent is added by means of the drug feeder  136 . A sensor (not shown) is provided in the reservoir  133  for measuring the concentration of the anticancer agent contained therein, and the anticancer agent is added to the reservoir  133  until the resultant mixture has an appropriate anticancer agent concentration.  
      The bodily fluid such as blood (hereinafter may be referred to simply as “blood”) is delivered to the feeding tube  135  by means of the feeding pump  134 , and the fluid is fed into the body through the non-branched sheath  40 - 3  at a flow rare of 200 mL/min adjusted by means of the feeding pump  134 .  
      The flow rate sensor  138 - 2  measures the flow rate of the blood delivered into the discharge tube  131  and transmits a signal corresponding to the flow rate to the controller  137 . The controller  137  controls the discharge pump  132  in a feedback manner in accordance with the signal reflecting the flow rate so that the flow rate is maintained to the “discharge rate set value.” 
      By activating the anticancer agent administration key  144  at an arbitrary but appropriate time during the operation, the anticancer agent is introduced into the blood circuit by means of the drug feeder  136  in an amount (200 mL) displayed on the anticancer agent feed amount settings display  148 .  
      The anticancer agent introduced to the blood circuit is mixed with the blood contained in the reservoir  133  by means of the feeding pump  134 . Thus, the blood containing the anticancer agent is again fed into the body through the non-branched sheath  40 - 3  at a predetermined flow rate adjusted by means of the feeding pump  134 .  
      The operator may change, during operation, the amount of the anticancer agent fed into the body or may determine the number of times the anticancer agent should be fed, based on the anticancer agent content of the blood determined through a known technique such as centrifugation of the blood received in the reservoir  133  or urinalysis.  
      When the anticancer agent perfusion is applied for a predetermined period of time, a counter (not shown) provided in the controller  137  is activated, and the controller  137  stops the feeding pump  134 , the discharge pump  132 , and the drug feeder  136 . At this point in time, the running/stopped display  152  is changed from “running” to “stopped.” 
      A drug employed in the present invention includes not only drugs used for therapy of cancers in chemotherapy, immunotherapy, a therapy using a radioactive isotope, gene therapy, or a similar therapy, but also agents, such as antihemolytic agents, used in preliminary treatments for cancer therapy.  
      Chemotherapy is a method for treating cancer through destruction of tumor cells by use of drugs such as anticancer agents. Anticancer agents are typically classified into antimetabolites, alkylating agents, anticancer antibiotics, and vegetable alkaloids. Antimetabolites inhibit cell division of rapidly growing cancer cells through use of enzymes contained in a large amount in the cancer cells. Alkylating agents, which have been developed in the form of toxic gas, react with and destroy DNA—which plays an important role in essential life activities such as transfer of genetic information—by binding thereto, to thereby kill cancer cells.  
      Similar to typical antibiotics, anticancer antibiotics are generally produced from microorganisms contained in the soil. Vegetable alkaloids inhibit the function of microtubules, which are important to cell division, to thereby kill cancer cells. Examples of such an anticancer agent which acts on the microtubules include paclitaxel.  
      Immunotherapy is another method for treating cancer in which tumor tissues are killed through enhancement of immunofunction of a patient. Examples of drugs employed for enhancing immunofunction include cytokines, vaccines, and immunocytes of the patient himself/herself. A cytokine, a substance produced by immunocompetent cells, activates or proliferates immunocompetent cells. The activated immunocytes directly or indirectly kill tumor cells.  
      A vaccine is a substance produced through detoxication (e.g., destruction) of tumor cells of a patient, and the thus-treated cells are inoculated to the patient. Through the vaccine inoculation, immunoreaction against a cancer-specific antigen is induced in the patient&#39;s body, to thereby kill tumor cells. Examples of the immunocytes of patient include lymphocyte and dendritic cells. These cells are collected from the patient, cultured ex vivo, and returned to the patient&#39;s body. Such immunotherapy is generally said to cause less intense side effect than does chemotherapy.  
      In the present invention, as a radioactive isotope, there may be employed an element such as  123 I,  125 I,  131 I,  32 P,  64 Cu,  211 At,  177 Lu,  90 Y,  186 Re,  212 Pb, or  212 Bi. Alternatively, a known tumor-specific antigen labeled with any of the radioactive isotopes may be employed. Such a radioactive isotope directly acts on DNA of tumor cells to render the cells no longer able to divide and to induce apoptosis, to thereby kill the tumor cells. The radioactive isotope is mixed with, for example, saline before use.  
      As a gene, DNA molecule, RNA molecule, or cell for gene therapy, a substance generally employed in gene therapy of cancer may be employed. The gene, DNA molecule, RNA molecule, or cell may be employed singly or in combination with one or more other drugs, to inhibit functions of a cancer gene, recover functions of an inactivated cancer suppressor gene, or enhance the immunological competence against tumors. Such a gene, DNA molecule, RNA molecule, or cell is used in the form of a mixture with, for example, saline.  
      As a gene for gene therapy, a cancer suppressor gene, a drug metabolizing enzyme gene, or a DNA vaccine may be employed. The cancer suppressor gene employed in the present invention is exemplified by a p53 gene. When the p53 gene is introduced into mutated cancer cells in which cancer suppressor genes have been inactivated, the p53 gene lowers oncogenicity of the cells.  
      A drug metabolizing enzyme gene is a gene employed in suicide gene therapy and is derived from a microorganism which, in nature, is not present in cells of mammals. The metabolizing enzyme gene selectively kills only cells to which the metabolizing enzyme gene is introduced, by introducing into cells the metabolizing enzyme gene and administering a prodrug which is transformed into an active (toxic) product by an enzyme encoded by the gene. The prodrug is typically an antimicrobial agent such as an antivirus or an antifungal agent.  
      As a combination of the drug metabolizing enzyme gene and the prodrug, there may be employed a combination of herpes simplex virus thymidine kinase (HSV-TK), and ganciclovir (GCV) or aciclovir (ACV); a combination of cytosine deaminase and 5-fluorocytosine (5-FC); a combination of varicella zoster virus thymidine kinase and 6-methoxypurine arabinoside (ara-M); a combination of  E. coli  gpt and 6-thioxanethine (6-TX); and a combination of  E. coli  deoD and 6-methylpurine-2′-deoxyriboside (Mep-dR).  
      As a DNA molecule for gene therapy, an antisense oligodeoxynucleotides (antisense ODN) may be employed in the present invention. An antisense oligodeoxynucleotide is a small DNA molecule which has a base sequence complementary to mRNA of the target cancer, and inhibits expression of the target cancer gene by hybridizing the target mRNA in cells and inhibiting translation to proteins.  
      As a RNA molecule for gene therapy, an antisense RNA or a ribozyme may be employed in the present invention. The antisense RNA is expressed by an antisense gene (cDNA) and inhibits expression of the target cancer gene. The ribozyme is an RNA molecule that has the ability to cleave the complementary mRNA strands, and is formed from an antisense portion against the target mRNA and an active portion exhibiting the cleavage activity. The active portion cleaves mRNA of the target cancer gene and inhibits translation to proteins, to thereby suppress expression of the target gene. In embodiments of the present invention, any of hammerhead type, hairpin type, and hepatitis D type ribozymes may be employed.  
      As a cell for gene therapy, an effector cell into which a cytokine gene is introduced may be employed in the present invention. The cytokine gene may be tumor necrosis factor (TNF), interferon-γ (INF-γ), FCR, TCR, IL-2R, IL-2, IL-7, or IL-12. The effector cell may be tumor infiltrating lymphocyte (TIL), LAK cell, or cytotoxic T cell (CTC).  
      The gene, DNA molecule, RNA molecule, and cell for gene therapy are not limited to those described above, and other genes, DNA molecules, RNA molecules, and cells may be employed.  
      The term “agents used in preliminary treatments for cancer therapy” refers to substances which are used in operation, treatment, or diagnosis of cancer but which themselves have no effect of directly or indirectly killing tumors. Examples of the agents used in preliminary treatments for cancer therapy include antihemolytic agents such as haptoglobulin, which is used to prevent hemolysis of the blood vessels during insertion of catheter. Examples of the agents used in diagnosis of cancer include iodine contrast agents employed in angiography.  
      The bodily fluid collected from the body may be any bodily fluid contained in the body, including blood and lymph.  
      Now, with reference to the flow chart shown in  FIG. 12 , the technique and procedure of the drug perfusion therapy according to the invention will be described. The procedure described below was decided to be employed, in view that the occurrence of advanced cancer in a site within the paraaortic lymph nodes  26  was clear from laboratory tests and that the test results did not support surgical operation, but intervention by way of perfusion. The mode of this embodiment is shown in  FIG. 1 .  
      In Step S 1 , a patient is generally anesthetized in a routine manner.  
      In Step S 2 , tourniquets  35  are placed. In this step, the tourniquets  35  are kept in a loosened state so that the blood flow in the lower limbs is not blocked.  
      In Step S 3 , sheaths are indwelled at predetermined locations in the blood vessels. Specifically, tips of non-branched sheaths  40 - 1 ,  40 - 2 ,  40 - 3 ,  40 - 4 , and three-way sheath  70  are percutaneously inserted and indwelled in the right axillary artery  9 , the left axillary artery  11 , the left femoral artery  6 , the right femoral vein  27 , and the right femoral artery  5 , respectively.  
      In Step S 3 , blood-removing cannulas  121  and  122  employed in the process of perfusion A are also percutaneously inserted through the jugular veins and indwelled at the superior vena cava and the inferior vena cava, respectively, through a known method.  
      In Step S 4 , balloon catheters are indwelled at predetermined locations in the blood vessels. Specifically, a balloon catheter  32 - 1  is inserted through the non-branched sheath  40 - 1  into the right axillary artery  9 , and the balloon-inflating portion thereof is indwelled at a predetermined location in the right renal artery  20 . A balloon catheter  32 - 2  is inserted through the non-branched sheath  40 - 2  into the left axillary artery  11 , and the balloon-inflating portion thereof is indwelled at a predetermined location in the left renal artery  21 . Balloon catheters  32 - 3 ,  32 - 4 , and  32 - 5  are inserted through the three-way sheath  70  into the right femoral artery  5 , and the balloon-inflating portions thereof are indwelled at predetermined locations in the celiac artery  12 , the superior mesenteric artery  19 , and the inferior mesenteric artery  24 .  
      A balloon catheter  33  is inserted through the non-branched sheath  40 - 3  into the left femoral artery  6 , and the balloon-inflating portion thereof is indwelled at a predetermined location in the aorta  3  between the celiac artery  12  and the heart. A balloon catheter  34  is inserted through the non-branched sheath  40 - 4  into the right femoral vein  27 , and the balloon-inflating portion thereof is indwelled at a predetermined place in the inferior vena cava  4 .  
      Prior to controlling the balloon catheters  32 ,  33 , and  34  under X-ray fluoroscopy, syringes containing a contrast medium have been connected to three-way cocks of the non-branched sheath  40  and the three-way sheath  70 . If a branched portion is present in the blood vessel, the radiopaque contrast medium is injected into the blood vessel by means of pressurizing the syringe, and the balloon-inflating portion is selectively advanced into a suitable one of the branches while performing angiography through an appropriate level of X-ray irradiation.  
      In Step S 5 , preliminary cava blocking is carried out. Specifically, the tourniquets  35  placed in Step S 2  are inflated by applying an appropriate pressure to thereby block the blood flow in the lower limbs. In addition, preliminary aorta/cava blocking is performed in the aorta and the cava by applying an appropriate pressure to the balloon catheters  32 - 1 ,  32 - 2 ,  32 - 3 ,  32 - 4 ,  32 - 5 ,  33 , and  34  indwelled in Step S 4 , thereby inflating the balloon-inflating portions thereof.  
      In Step S 6 , positions of collateral blood vessels are confirmed. Specifically, a radiopaque contrast medium is introduced to the blood vessel, and angiography is performed through an appropriate level of X-ray irradiation, to thereby determine whether collateral blood vessels are present or absent in the regions of the above-mentioned preliminary aorta/cava blocking and to specify the sites. The radiopaque contrast medium is fed through the lumen  116  of the balloon catheter  33 . Specifically, a syringe containing the contrast medium is attached to the branch tube  112   b  of the balloon catheter  33 , and the plunger of the syringe is pushed, to thereby feed the contrast medium. The contrast medium is fed to the blood vessel via the side openings  117 .  
      After confirmation that collateral blood vessels to and from tumor tissues have been secured, and that therefore drugs can reach the tumor tissues, the tourniquets  35  and balloons are immediately deflated to thereby restore the blood flow.  
      In Step S 7 , a drug perfusion apparatus is set. The perfusion method of the present invention employs two types of perfusion; i.e., perfusion A and perfusion B, as shown in  FIG. 9 . A liquid-feeding tube  135  is connected to one of the ports provided in the three-way cock  48  of the non-branched sheath  40 - 3 . In addition, a syringe (not shown) containing necessary agents, including an anticoagulant (such as heparin) and a contrast medium, is connected to the branch tube  112   b  of the balloon catheter  33 .  
      The following parameters are set for perfusion A by means of the settings display panel  161  shown in  FIG. 10 : the “liquid feed rate setting” displayed on the liquid feed rate settings display  166  is set at 360 mL/min; the “perfusion time setting” displayed on the perfusion time settings display  167  is set at 30 min; and the “oxygen saturation setting” displayed on the oxygen saturation settings display  168  is set at 99 to 100%.  
      The following parameters are set for perfusion B by means of the settings display panel  139  shown in  FIG. 11 : the “liquid feed rate setting” displayed on the liquid feed rate settings display  145  is set at 200 mL/min; the “liquid discharge rate setting” displayed on the liquid discharge rate settings display  146  is set at 180 to 200 mL/min; and the “perfusion time setting” displayed on the perfusion time settings display  147  is set at 30 min.  
      In Step S 8 , aorta/cava blocking is performed. Specifically, while appropriately feeding an anticoagulant such as heparin, the tourniquets  35  are inflated by pressurizing at an appropriate pressure, to thereby block the blood flow in the lower limbs. The balloons of the balloon catheters  32 - 1 ,  32 - 2 ,  32 - 3 ,  32 - 4 ,  32 - 5 ,  33 , and  34  are also inflated by pressurizing at an appropriate pressure the syringes mounted at the rear end of the catheters, to thereby form a closed region in the aorta/cava.  
      In Step S 9 , the perfusion A is carried out by actuating the running/stopped display  164  provided on the settings display panel  161 . Specifically, oxygenated blood is fed to the right kidney, the left kidney, the stomach  16 , the liver  17 , the spleen  18 , the small intestine, and the hindgut through the lumen  116  of the balloon catheters  32 - 1 ,  32 - 2 ,  32 - 3 ,  32 - 4  and  32 - 5 .  
      In Step S 10 , the perfusion B is started by activating the start/stop switch  143  provided on the settings display panel  139  while operation of the perfusion A is maintained. Specifically, a drug solution containing an anticancer agent is administered to the aorta/cava closed region through the passage  45  of the non-branched sheath  40 - 3 . In addition, bodily fluid containing the anticancer agent is removed from the aorta/cava closed region through the passage  45  of the non-branched sheath  40 - 4 .  
      During the above anticancer agent perfusion procedure, the anticancer agent is administered to the cancer tissues by actuating the anticancer agent administration key  144  at 10-minute intervals. In the present embodiment, the dose of the anticancer agent, the times of anticancer agent administration, and the frequency of anticancer agent administration can be modified depending on conditions of the patient or based on the anticancer agent content of the blood as determined by, for example, centrifugation of the blood stored in the reservoir  133  or urinalysis.  
      At an arbitrary, appropriate time, a haptoglobulin-containing antihemolytic agent may desirably be administered intravenously. In addition, blood circulating conditions are preferably maintained, by providing blood transfusion or fluid transfusion during operation.  
      After an appropriate amount of an anticancer agent has been administered predetermined times, the running/stopped display  152  automatically changes to thereby complete the process of perfusion B (Step S 1 ).  
      Thereafter, the process of perfusion A is completed by operating the running/stopped display (Step S 12 ). Subsequently, the tourniquets  35  and the balloon-inflating portions of the balloon catheters  32 ,  33 , and  34  are deflated, to thereby release the aorta/cava blocking. An appropriate amount of a heparin antagonist such as protamine is administered for the purpose of hemostasis.  
      Thereafter, the tools are removed (step S 13 ). Specifically, the balloon catheters  32 ,  33 , and  34 , the non-branched sheath  40 , the three-way sheath  70 , and tourniquets  35  are removed, and a hemostatic procedure is performed. When the patient is awaken from anesthesia, the process is finished.  
      The perfusion method of the present invention will next be described by way of an example. In this example, a living body to be treated has a tumor in the paraaortic lymph nodes metastasized from the cervical carcinoma. The non-branched sheaths  40 - 1 ,  40 - 2 , and  40 - 3  employed in the example have sizes of 6 Fr., 6 Fr., and 9 Fr., respectively. The three-way sheath  70  has a size of 12 Fr. The balloon catheters  32 - 1 ,  32 - 2 ,  32 - 3 ,  32 - 4 , and  32 - 5  have sizes of 6 Fr., 6 Fr., 7 Fr., 4 Fr., and 4 Fr., respectively.  
      In the process of perfusion A, the venous blood is removed through use of cannulas  121  and  122  (360 ml/min), oxygenated in an artificial lung so that the resultant blood has an oxygen saturation level of 99 to 100%, and then is delivered to a feeding tube. In this example, the oxygenated blood was found to have an oxygen saturation level of 99%. The process of perfusion A was continued until the blocking of blood vessels was released after completion of the process of perfusion B described below.  
      In the process of perfusion B, an anticancer agent cisplatin (140 mg) mixed with saline was fed to the closed region in the aorta through the passage  45  of the non-branched sheath  40 - 3  at a feed rate of 200 mL/min (liquid removal rate was 190 mL/min). Perfusion B was performed for 30 minutes. During the process of perfusion B, the anticancer agent was quantified by measuring the amount of platinum contained in the blood collected from the predetermined blood vessels; i.e., (i) the abdominal aorta within the blood vessel closed region, (ii) the inferior vena cava within the blood vessel closed region, and (iii) the radial artery outside the blood vessel closed region.  
       FIG. 13  shows some data obtained in the above experiment. As shown in  FIG. 13 , in the abdominal aorta within the blood vessel closed region (i) and the inferior vena cava within the blood vessel closed region (ii), cisplatin level was found to be high immediately after administration and then decreased gradually. In contrast, in the radial artery outside the blood vessel closed region (iii) (that is, systemically), substantially no increase in the cisplatin level was observed. These results indicate that the perfusion method of the present invention enables delivery of a drug of high concentration to the blood vessel closed region with substantially no leakage of the drug to outside the blood vessel closed region.