Abstract:
A method for investigating the thrombocyte function of the blood, and particularly of platelet aggregation, wherein the following steps are carried out: a) cross-flowing an aperture with blood or blood components; b) determining the active radius of the aperture depending on time and c) evaluating the time-dependent modification of the radius as a measure for blood cell and/or thrombocyte function.

Description:
[0001]    This is a continuation application of U.S. Ser. No. 10/513,815, filed Apr. 7, 2005, and hereby claims the priority thereof to which it is entitled. 
     
    
     BACKGROUND OF THE INVENTION 
       [0002]    1. Field of the Invention 
         [0003]    The invention at hand has to do with a technique and mechanism for testing the thrombocyte function in blood. 
         [0004]    2. Description of the Related Art 
         [0005]    There are various mechanisms for testing the aggregation of blood platelets or the coagulation of blood. For example, a mechanism is based on the EP 0223244 in which the blood is aspirated through an aperture out from a blood supply space by means of a moveable piston in a cylinder and the pressure in the space between the piston and the aspirated in blood is measured, whereby the piston is driven in such a way that a target pressure value is maintained in the space. The piston movement serves as a measurement for the amount of blood flow. 
       SUMMARY OF THE INVENTION 
       [0006]    The role of the invention at hand consists in creating a technique and a mechanism that enable to get an exact determination of the thrombocyte function in the blood. 
         [0007]    This role is performed by a method for testing the thrombocyte function in blood, whereby an aperture with blood or blood components is flowed through, including the steps of determining the effective radius of the aperture as a function of time by measuring the drop in pressure at the aperture as a function of time and determining the blood flow volume through the aperture as a function of time; calculating the hemodynamically effective radius of the aperture by the Hagen-Poiseuille law; and evaluating the time-dependent change in the radius as a measure for the blood cell and/or thrombocyte function. The present invention also includes a mechanism for carrying out this method. 
         [0008]    The essential advantage of the invention at hand consists in allowing for an exact determination of the blood platelet delay time by means of which the arterial thrombus growth is controlled or influenced. Thus, since in accordance with the invention it becomes possible to measure the designated blood platelets&#39; delay time, for the first time evidence ban be gathered on e.g. existing disease risks, such as arterial thrombotic tendency, for example the risk of myocardial infarction in a patient. For the first time medications can be developed that selectively have an effect on the blood platelet delay time to eliminate such risks. 
         [0009]    The determination of the blood platelet delay time in a patient&#39;s fresh blood so to speak ‘bedside’ very quickly (without blood thinners) and on a very small volume of blood can be arrived at by means of a special design of the invention-related mechanism. 
         [0010]    With a particularly preferred design of the invention the thrombocyte function can be determined at a very high degree of reproducibility and preciseness fast and with only a little volume of blood. 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0011]    Below the invention and its designs will be explained in more detail in connection with the figures. Shown are: 
           [0012]      FIG. 1  a mechanism for determining the blood platelet delay time in schematic representation; 
           [0013]      FIG. 2  a diagram for demonstrating the relationship of the aperture diameter to the time, caused due to occlusion by the blood platelets; 
           [0014]      FIG. 3  a diagram for demonstrating the wall sear rate as a function of time; 
           [0015]      FIG. 4  a mechanism designed as a disposable part for implementing the invention-related technique in schematic representation; and 
           [0016]      FIGS. 5 and 6  preferred designs of the invention. 
       
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
       [0017]    The following considerations and realizations led to the inventions. A time-dependent determination of the loading of an aperture by means of blood platelets when flowing through it surprisingly revealed that the aperture closes in a completely defined way, that is in accordance with the straight line depicted in  FIG. 2 , whose slant  2  dr/dt yields the growth rate. When simultaneously calculating the blood platelets&#39; time-dependent wall shear rate that represents a measurement for blood platelets&#39; transport rate, it was recognized that in time the wall shear rate sharply rises from a low value at first in the area of the aperture. But since the growth rate during this time remains exactly the same, it can be inferred that a blood platelet delay time exists that indicates that time over which the individual blood platelets first allow an adhesion of other blood platelets. In other words each blood platelet “determines” when, i.e. thus after which lag in time or delay time, other platelets may adhere to it. This blood platelet delay time in connection with certain disease risks and with the development of medications is of primary importance. This means that by the invention-related finding of the mentioned rise dr/dt, i.e. therefore the blood platelet delay time, selective evidence on disease risks, e.g. on the risk for myocardial infarction in a patient, can be gathered and for this reason medications can be selectively developed that influence the blood platelet delay time. 
         [0018]      FIG. 1  shows an existing mechanism for determining the blood platelet delay time in schematic representation. In essence here according to arrow  1  blood is moved out of a supply space that is not described in any greater detail, for instance via a capillary  4  that forms a blood flow resistance stream Wc, through an aperture  3  of an aperture holder  2 . The aperture  3  forms a blood flow resistance Wa. 
         [0019]    According to the following equation 
         [0000]    
       
         
           
             
               
                 
                   Wa 
                   = 
                   
                     
                       Δ 
                        
                       
                           
                       
                        
                       P 
                     
                     Q 
                   
                 
               
               
                 
                   ( 
                   1 
                   ) 
                 
               
             
           
         
       
     
         [0000]    (Q=volume of blood flow per time)
 
as well as according to the Hagen-Poiseuille law
 
         [0000]    
       
         
           
             
               
                 
                   Wa 
                   = 
                   
                     
                       
                         8 
                          
                         
                             
                         
                          
                         µl 
                       
                       π 
                     
                     · 
                     
                       1 
                       
                         r 
                          
                         
                             
                         
                          
                         4 
                       
                     
                   
                 
               
               
                 
                   ( 
                   2 
                   ) 
                 
               
             
           
         
       
     
         [0000]    by time-dependent calculation of the resistance. Wa the effective hemodynamic radius of the aperture  3  in accordance with the equation 
         [0000]    
       
         
           
             
               
                 
                   r 
                   = 
                   
                     
                       
                         
                           8 
                            
                           
                               
                           
                            
                           µl 
                         
                         π 
                       
                       · 
                       
                         1 
                         Wa 
                       
                     
                     4 
                   
                 
               
               
                 
                   ( 
                   3 
                   ) 
                 
               
             
           
         
       
     
         [0000]    can be calculated and spread of time in accordance with  FIG. 2 . 
         [0020]    In equations 1 through 3: 
         [0000]    Δp designates the drop in pressure at the aperture, Wa the flow resistance of the aperture, μ the viscosity of the blood flowing through the aperture, 1 the gauge of the aperture and r the radius of the same. 
         [0021]    In  FIG. 2  it can be seen that the opening of the aperture  3  quite definitely closes as a function of time surprisingly in accordance with a straight line with a constant slope of dr/dt=const) with a very high value of statistical probability: e.g. RSq=0.982. If a platelet diameter of 2 μm is assumed, a platelet delay time of 2/0.7=2.8 sec is obtained. With a first control person with normal platelet function a platelet delay time of 2.77+0.32 sec. was determined. The number of measurements was 11. With a second control person the platelet delay time amounted to 2.65+0.1 sec. with 11 measurements and a normal platelet function as well. 
         [0022]    Instead of the drop in pressure Δp at the aperture  3  the drop in pressure Δp′ can be measured at the capillary  4  and the aperture  3 , whereby then the capillary  4  flow resistance We has to be deducted to determine the growth rate. 
         [0023]    According to the formula: 
         [0000]    
       
         
           
             
               
                 
                   γω 
                   = 
                   
                     
                       4 
                        
                       Q 
                     
                     
                       π 
                        
                       
                           
                       
                        
                       
                         r 
                         3 
                       
                     
                   
                 
               
               
                 
                   ( 
                   4 
                   ) 
                 
               
             
           
         
       
     
         [0000]    the wall shear rate γω in the area of the aperture can be calculated and spread in a time-dependent fashion like  FIG. 3 . The result is that the platelets&#39; transport rate on the thrombus that is approximately proportional to the wall shear rate rates during the measuring by the factor  4 . During this rise though, just as in  FIG. 2 , the thrombus growth rate remains exactly the same. The inference is that the individual blood platelets in the area of the aperture  3  determine in accordance with a platelet delay time when other blood platelets may adhere to them. The blood platelet delay time, therefore, matches the time difference between a blood platelet&#39;s adhesion on the wall of the aperture  3  or on another blood platelet and the adhering of an additional blood platelet. 
         [0024]      FIG. 4  illustrates a design of the mechanism at hand in schematic representation, wherein blood from a blood supply space  10  is pressed or conveyed with the assistance of a piston  12  through the aperture  3  into a blood collecting space  14 . The blood supply space  10  is preferably designed in a cylinder  16  in which the piston  12  is pushably arranged. The piston/cylinder arrangement  12 ,  16  can for this purpose have the shape of a blood withdrawal syringe, wherein the blood supply space  10  is filled when withdrawing blood from a patient&#39;s vein. After removing the withdrawal cannula, the forward end  18  of the piston/cylinder arrangement  12 , 16  can be connected with the section encompassing the blood collection space  14  that is preferably designed as a disposable or single use section, wherein the part of its access opening  20  that is connectable to the piston/cylinder arrangement  12 ,  16  has an aperture holder  22  with the aperture  3  downstream, through which the blood traverses from the blood supply space  10  into the blood collecting space  14  upon activation of the piston  12  in the direction of the arrow  24 . 
         [0025]    A capillary  4  (see  FIG. 1 ) can be placed upstream to aperture  3 , as is already familiar. 
         [0026]    To measure the pressure reduction on the aperture  3 , the disposable section can have a passage  26  that is connected to a pressure meter mechanism in a gauge when taking readings and that runs inside or along its wall from outside to the space upstream of aperture  3 . 
         [0027]    One advantage here is that after withdrawing blood, for instance at the patient&#39;s bed, the disposable section for carrying out the technique at hand can be connected directly to the piston/cylinder arrangement  12 ,  16  that serves for withdrawal of blood and, along with the piston/cylinder arrangement  12 ,  16 , put into the gauge that implements the technique at hand and activates the piston  12 . 
         [0028]    It should be pointed out that for measuring with a small volume of blood (e.g., in pediatrics) it can be advantageous when carrying out the technique at hand not to activate the piston  12  continuously, but rather intermittently, whereby, for example, the movement of the piston  12  is interrupted at intervals that could be on the order of 3 seconds. 
         [0029]    Only one segment of the straight-line dr/dt in  FIG. 2  can also be measured, e.g., for measuring with little blood, whereby the corresponding bleeding time can be determined by extrapolating. 
         [0030]    Since it is known that a straight line is to be determined, measurements with stark deviations can be recognized as erroneous and corrected by extrapolating in the areas of deviation. Furthermore, it can also be sufficient to determine only a segment of the straight line and not to determine measured areas by extrapolating. For example, this measuring of only segments can be carried out to save time. 
         [0031]    Since the platelet delay time is not dependent on the capillary resistance in the case of using a capillary, capillary errors do not enter into the measurement, thus the measurement precision and reliability can be enhanced. 
         [0032]    Below a variation on the invention-related technique is explained in more detail in connection with  FIG. 5 , by which is possible a particularly advantageous, clear and significant assessment for the user or measurement of the thrombocyte function with a relatively small volume of blood, with short measuring times and an even greater reproducibility. 
         [0033]    These advantages are achieved due to the fact that by this variation the slope of the straight-lines dr/dt is indeed determined, yet no value CT of the bleeding time is extrapolated, but rather an angle PTGA (Platelet Thrombus Growth Angle) that exists between the straight line and the t-axis (see  FIG. 5 ). This is particularly advantageous if this angle is relatively small and the straight line for this reason runs flat, as is the case with a very slow thrombus formation in the aperture  3  which applies, e.g., to a taking of medication (for example, aspirin). In this case, enormous fluctuations in the CT value would result by the technique explained above even with small deviations of the slope dr/dt of the straight line. These fluctuations are greater the farther the CT value is removed from the t-axis zero point. In such a case, the determination or indication of the PTGA is more significant since it is not subjected to the designated fluctuation. Furthermore, this PTGA can be derived very quickly from the straight-line&#39;s slope determined at the start of a measurement by the formula indicated below; thus the measuring time can be relatively short and only a relatively small volume of blood is needed for measuring. 
         [0000]      PTGA=−(((arcTan( dr/dt ))/( n /))90)  (5)
 
       Determined. 
       [0034]    Accordingly even the PTGA′ can be determined by the formula: 
         [0000]      PTGA′=90−PTGA  (6)
 
         [0000]    and applied. 
         [0035]    The thrombocyte function can, as already mentioned, be quickly established by this variation of the invention at hand, i.e., even with a small volume of blood, particularly also with relatively long thrombus formation times in the aperture  3 , as this is possible, for example, with influences of medications, e.g., with the taking of aspirin. Here the values of the PTGA or the PTGA′ determined are to a certain extent comparatively significant because they are not subjected to such great fluctuations as the CT values determined. 
         [0036]    A still more improved measurement is made possible with an additional variation of the technique at hand, according to which a fit operation is performed to compensate for changes in blood viscosity and/or the resistance We of capillary  4  ( FIG. 1 ). Here, with a value t=0, the start value of the aperture opening is always set or fitted to a pre-established defined value V (from, e.g., 150 μm in  FIGS. 2 and 5 ) in such a way that the straight line at the beginning of a measurement is calculated by extrapolating up to the zero point of the t-axis and the value thereby determined for t=0 is shifted to the pre-established value V. Proceeding from this value V, the straight line is then determined and the CT value according to  FIG. 2  or the PTGA or PTGA′ according to  FIG. 5 . In this way the measurement data can be further enhanced because fluctuations in viscosity or the capillary resistance are compensated. 
         [0037]    Below an additional variation of the technique at hand is explained by which a quality control of the determined straight line or the determined PTGA or PTGA′ is effected. In so doing, as indicated earlier above, it is determined how precisely the measured values dr/dt line up on a straight line or not. With deviations of a pre-established number of values beyond a prescribed measure, the corresponding measurement is deemed not processable or corrected. 
         [0038]    With certain disease conditions or under the influence of medication, there may be deviations from the linear relation dr/dt. For example, in  FIG. 2  by means of a pointed line is depicted that the slope of the straight line during a measurement can change in such a way that the straight line can encompass two segments of varying slopes dr 1 /dt and dr 2 /dt, whereby the point of intersection P of these segments is to be ascribed for a certain thrombus formation that is established by a certain disease pattern. In such cases, the point P is very significant for which reason it is determined with the measurement. 
         [0039]    Below an additional preferred form of implementation of the technique at hand, shown in  FIG. 6 , is explained in more detail. This essentially has a piston/cylinder arrangement  11  that encompasses a cylinder  30  and a piston  50 . The piston  50  can be moved in the direction of the arrow  70 , i.e. therefore in its axial direction in the cylinder  30  by means of a drive that is not illustrated in any more detail. 
         [0040]    The piston  50  preferably has the shape of a metal part polished on its outer surface that consists in particular of stainless steel and possesses the shape of a lengthwise cylindrical rod section. Between the outer surface of the piston and the inner surface of the cylinder  30 , that also preferably consists of stainless steel, is arranged an O-ring gasket  90  that preferably consists of a rubber material. Since the outer surface of the piston  50  is polished between the gasket  90  and the piston  50 , there is extremely little friction so that a smooth movement of the piston  50  in the direction of the arrow  70  is assured. 
         [0041]    With its end away from the drive that is not illustrated in more detail, the piston  50  extends out into a blood uptake space  110  that is established by means of a beaker-shaped vessel  130  that is positioned tightly up against the cylinder  30  with its upper edge area adjacent to the piston  50  with the aid of a gasket  150 . For this reason the cylinder  30  has a flange section  170  that extends radially outwards and, on the upper edge of the vessel  130 , a flange section  190  that protrudes toward the outside radially as well, whereby the O-ring gasket  150  is kept between the flange sections  170  and  190  and connects the latter tightly to each other. On the bottom  210  of the vessel  130 , an aperture holder  230  is located that holds a platelet  250  or the like with an aperture  270  arranged in it, whereby a capillary  290  led from outside through the bottom part  210  in an inherently familiar way ends shortly prior to the aperture  270  in such a way that out of a blood supply space (not shown) blood that has been aspirated in through the capillary  290  with the movement of the piston  50  in the direction of the arrow  70  is taken in through the aperture  270  into the uptake space  110 . The aperture  270  can also be designed and arranged in another way. For example, the end of the capillary  290  that protrudes through into the uptake space  110  can form it. 
         [0042]    One pressure-measuring mechanism P that is not illustrated in greater detail is connected to a passageway  310 , preferably in the wall of the cylinder  30 , for measuring the pressure outside of the blood that has been aspirated through the aperture  270  into the uptake space  110 . In this way it is achieved that the vessel  130  is fastened to the aperture holder  230  and the capillary  290  and can be designed as a so-called disposable part and via the gasket  150  optionally to the piston/cylinder arrangement  11  the simplest way. 
         [0043]    It should be pointed out that instead of determining the drop in pressure at the aperture  3 , an electrical resistance also could be established by application of a potential difference for determining the hemodynamic resistance of the aperture  3 . The radius of the aperture  3  that just exists can also be optically determined. 
         [0044]    The invention being thus described, it will be apparent that the same may be varied in many ways. Such variations are not to be regarded as a departure from the spirit and scope of the invention, and all such modifications as would be recognized by one skilled in the art are intended to be included within the scope of the following claims.