the present invention , generally referred to as a single riser / single capillary ( srsc ) blood viscometer , uses a single riser tube and a single flow restrictor ( e . g ., a capillary tube ) structure for determining the viscosity of the circulating blood of a living being . although the srsc blood viscometer can be implemented in a number of ways , two exemplary apparatus / methods are set forth below . the first implementation uses the srsc structure along with mass detection and hence is hereinafter referred to as a mass detection capillary blood viscometer ( mdcbv ) 20 . the second implementation uses the srsc structure along with column height detection and hence is hereinafter referred to as a column height detection capillary ( chdc ) blood viscometer 1020 . referring now in detail to the various figures of the drawing wherein like reference characters refer to like parts , there is shown at 920 a mass detecting capillary blood viscometer ( mdcbv ). the mdcbv 920 basically comprises a blood receiver 922 and an analyzer / output portion 924 . the patient is coupled to the mdcbv 920 through a circulating blood conveyor 926 , e . g ., a needle , an iv needle , an in - dwelling catheter , etc ., or any equivalent structure that can convey circulating blood from a patient to the mdcbv 920 . as will be discussed in detail later , the analyzer / output portion 924 provides a display 28 for presenting the viscosity information , as well as other information to the operator . the analyzer / output portion 924 may also provide this information to other suitable output means 330 , such as a datalogger 332 , other computer ( s ) 334 , a printer 336 , a plotter 338 , remote computers / storage 340 , to the internet 342 or to other on - line services 344 . the blood receiver 922 basically comprises a valve mechanism 946 coupled to a riser tube r on one side and coupled to a flow restrictor 24 ( e . g ., a capillary tube ) on the other side . the output of the flow restrictor 24 is directed into a fluid collector 26 via an adaptor 34 . when the blood conveyor 926 is coupled to the blood receiver 922 , the valve mechanism 946 controls the flow of blood into the blood receiver 922 , as will be discussed in detail later . the upper end of the riser tube r is exposed to atmospheric pressure . the riser tube r may be positioned at any non - zero angle to a horizontal reference position ( e . g ., the datum line as shown in fig4 ); one exemplary position is at a vertical orientation with respect to the datum line as shown in fig4 . it should be understood that the blood receiver 922 may be disposable or non - disposable . as will be discussed in detail later , where the blood receiver 922 is disposable , the components ( valve mechanism 946 , riser tube r and flow restrictor 24 ) are releasably secured in a blood receiver housing 962 that can be quickly and easily inserted , used during the viscosity test run and then quickly and easily removed for disposal ; another disposable blood receiver 922 is then inserted in preparation for the next viscosity test run . on the other hand , where the blood receiver 922 is non - disposable , the components ( valve mechanism 946 , riser tube rand flow restrictor 24 ) can be thoroughly washed and cleaned in place in preparation for the next viscosity test run . it should be understood that the flow restrictor 24 does not necessarily have to be an elongated tube but may comprise a variety of configurations such as a coiled capillary tube . the analyzer / output portion 924 basically comprises a mass detector 28 , a level detector 400 , a processor 30 , the display 928 , a bar code reader 978 , an environmental control unit 980 , and overflow detector 981 , a first battery b 1 and a second back - up battery b 2 . the fluid collector 26 is positioned on top of the mass detector 28 which monitors the increasing mass of blood collecting in the fluid collector 26 . the overflow detector 981 ensures that when the column of blood is generated , no blood overflows the riser r . the processor 30 ( e . g ., a “ 386 ” microprocessor or greater , or any equivalent ) is arranged to analyze the data from the mass detector 28 and to calculate the blood viscosity therefrom , as will also be discussed in detail later . furthermore , the processor 30 also controls the display 928 for providing the viscosity information and the other information to the operator as well as to the other output means 330 . the processor 30 also controls the valve mechanism 946 based on the data from the mass detector 28 , as will be discussed later . battery b 1 provides all of the requisite power to the analyzer / output portion 24 , with battery b 2 serving as a back - up power supply . the bar code reader 978 , the environmental control unit 980 and the level detector 400 will be described later . in general , via the use of the valve mechanism 946 , a column of blood 38 is initially generated in the riser r and then that column of blood 38 is permitted to fall through the riser tube r , through the flow restrictor 24 and into the fluid collector 26 . this movement of blood can be represented by a height vs . time relationship ( fig1 a ) with regard to the column of blood in the riser r and by a mass vs . time relationship ( fig1 b ) with regard to the blood being received in the fluid collector 26 . as shown more clearly in fig2 - 3 , the preferred embodiment of the mdcbv 920 comprises the blood receiver 922 and the analyzer / output portion 924 contained in respective housings 960 and 962 , each of which can be releasably secured to a common frame , e . g ., a conventional intravenous ( iv ) pole 48 . in this configuration , the analyzer / output portion 924 can be positioned in an inclined orientation ( see fig3 ) to facilitate user operation and viewing of the display 928 . however , it should be understood that the respective housing constructions are exemplary , and others can be incorporated without limiting the scope of this invention . the display 928 may comprise any suitable conventional devices , e . g ., an eld ( electroluminescent display ) or lcd ( liquid crystal display ) that permits the visualization of both text and graphics . the resolution of this display 928 is preferably 800 × 600 vga or above . furthermore , while the preferred embodiment utilizes a touch screen display which incorporates , among other things : instruction , and / or data , display 965 ( which also includes the command line display shown as “ run test ”; e . g ., “ testing ”, “ test in progress ,” etc .) it should be understood that any equivalent display device is within the broadest scope of the invention . thus , any number of user interfaces and buttons may be available through the display 928 . therefore the invention 920 is not limited to the embodiment that is shown in fig2 . moreover , the display 928 can be operated to minimize or maximize , or overlay any particular graphic or text screen , as is available in any conventional object - oriented operating system , such as microsoft ® windows . the lower housing 960 comprises the blood receiver 922 and the mass detector 28 . in the preferred embodiment , the mass detector 28 may comprise a precision balance , or load cell , such as the adventurer ™ by ohaus corporation of florham park , n . j . thus , as the collector 26 collects more of the blood during the viscosity test run , the changing mass value is transmitted to the processor 30 from the mass detector 28 for viscosity determination ; in particular , the mass detector 28 generates an electrical signal that corresponds to the mass variation in time . it should be understood that the term “ mass ” may be interchanged with the term “ weight ” for purposes of this invention . it should also be understood that the connection between the mass detector 28 and the processor 30 is bi - directional ; this allows the processor 30 to reset the mass detector 28 in preparation for a new test run . it should also be understood that although it is preferable to have the riser tube r in a vertical position , it is within the broadest scope of this invention to have the riser tube r oriented at any angle greater than zero degrees , with respect to a horizontal reference ( e . g ., datum line shown in fig4 ). where the blood receiver 922 is disposable , it is releasably secured in the housing 960 such that once a test run is completed and / or a new patient is to be tested , all of the lumens ( e . g ., the riser tube r , the capillary 24 , the adaptor 34 and the valve mechanism 946 ) can be easily / quickly removed , disposed of and a new set inserted . for example , a bracket 147 ( fig2 ) may be used to releasably secure the upper portion of the riser tube r . a door 976 ( which can be vertically or horizontally hinged to the housing 960 ) is provided to establish a temperature - controlled environment during the test run . in particular , the door 976 also supports an environmental control unit 980 ( e . g ., a heater , fan and / or thermostat ) such that when it is closed in preparation for the test , the flow restrictor 24 is then heated ( or cooled ) and maintained throughout the test run at the same temperature and environment as the living being . prior to the run , the living being &# 39 ; s temperature is taken and the operator enters this temperature ( via the touch screen display 928 ). the environmental control unit 980 then operates to achieve and maintain this temperature . it should be noted that it is within the broadest scope of this invention to include a environmental control unit 980 that achieves and maintains the entire blood receiver 922 at the patient &# 39 ; s temperature during the run . by properly maintaining the temperature throughout the test run , the effects of any temperature variation in the viscosity measurement is minimized . the door 976 may also support the bar code reader 978 . the bar code reader 978 automatically reads a bar code ( not shown ) that is provided on the riser tube r . the bar code contains all of the predetermined data regarding the characteristics of the flow restrictor 24 ( e . g ., its length and diameter ) and the characteristics of the riser tube r . this information is passed to the processor 30 which is then used to determine the viscosity . the batteries b 1 / b 2 may each comprise a 12 vdc , 4 amp - hour battery , or any equivalent power supply ( e . g ., batteries used in conventional lap - top computers such as lithium ion batteries ). the display 928 provides the status indicators 972 a / 972 b for each battery in the mdcbv 920 . in particular , when the mdcbv 920 is operating off of battery b 1 , the two battery indicators 972 a / 972 b appear on the display 928 . however , once battery b 1 is depleted , the battery b 1 indicator 972 a disappears and the battery b 2 indicator 972 b blinks to warn the operator that the mdcbv 920 is now operating off of the back - up battery b 2 and re - charge of battery b 1 is necessary . the preferred fluid collector 26 of the present invention is similar to that disclosed in application ser . no . 09 / 789 , 350 . in particular , the collector 26 comprises an inner circular wall 35 that divides the collector 26 into a central portion 31 and an annular portion 39 . the central portion 31 collects the blood as it enters the collector 26 . the column of blood 38 falls through the riser tube r , the flow restrictor 24 , the adaptor 34 and then into the central portion 31 . any overflow spills into the annular portion 39 . it should be understood that the phrase “ column of blood 38 ” is meant to cover the continuous element of blood that occupies the riser tube r as well as the blood that occupies the flow restrictor 24 and the adaptor 34 . to minimize any surface tension effects that would normally occur if an open end 36 of the adaptor was positioned above the level of collected blood 300 in the central portion 31 , it is necessary to begin collecting mass vs . time data only when the open end 36 of the adaptor 34 is submerged within the collected blood 300 . this is shown most clearly in fig4 . in order to accomplish this , the open end 36 of the adaptor 34 is placed appropriately below the datum line ( e . g ., the top edge 37 of the inner wall 35 of the preferred collector 26 ) and the level detector 400 is provided for detecting when the collected blood 300 has reached the datum level . the level detector 400 informs the processor 30 when this event has occurred . thus , the processor 30 is able to determine those mass vs . time data points where surface tension effects are minimized . the level detector 400 can be implemented in various ways known to those skilled in art , e . g ., float sensors , tuning fork sensors , ultrasonic sensors , optical sensors , proximity sensors , capacitance sensors , etc . and all of which generate an electrical signal when a particular fluid level has been reached . an exemplary sensor is the coleparmer ew - 20603 - 22 capacitive level sensor . it should be understood that the output side 3 of the flow restrictor 24 can be integrally formed with the input side 5 of the adaptor 34 . the concept of the blood viscosity determination using the mdcbv 920 is that a portion of the circulating blood of the living being is diverted from the living being using the blood conveyor 926 into the blood receiver 922 to create a column of blood 38 ( fig4 ) in the riser tube r . next , the column of blood 38 is allowed to fall and collect in the fluid collector 26 over time , whereby the changing mass of this collector 26 is monitored over time . from this mass vs . time data and based on the characteristics of the flow restrictor 24 and the riser tube r , the circulating blood viscosity can be determined . in addition , where the blood exhibits yield stress , τ y , a residual amount of the column of blood 38 remains in the riser tube r after a long period of time at the end of the viscosity test run ; furthermore , there are surface tension effects that also contribute to this residual amount of the column of blood 38 as a result of the gas - liquid interface 23 ( fig4 ). the height of this residual column of fluid is known as δh ∞ , where δh = h ( t )− datum level and where h ( t ) represents the height of the column of blood 38 in the riser tube r at any time ; the term h ∞ ( fig1 a ) represents the final height of the column of blood 38 in the riser tube r at the end of the test run after a long period of time . as will also be discussed later , the viscosity determination of the blood can be determined using the mdcbv 920 without the need to determine h ( t ) or the initial position , h i , of the column of blood 38 in the riser tube r at which data is collected . to obtain accurate data , it is important to “ wet ” all of the lumens , namely , the riser tube r , the valve mechanism 946 , the flow restrictor 24 and the adaptor 34 before data is taken . as a result , in order to generate the column of blood 38 and then allow it to fall , the valve mechanism 946 must be operated as follows : when the viscosity test run is initiated , the processor 30 activates the valve mechanism 946 by commanding a valve driver 986 ( e . g ., a 500 ma solenoid , or stepper motor , etc .) which rotates the valve into the position shown in fig5 a . this allows the diverted portion of the circulating blood to flow up into the riser tube r to create the column of blood 38 . when the overflow detector 981 detects a predetermined height , h 0 , of the column of blood 38 , the overflow detector 981 informs the processor 30 which then commands the valve driver 986 to rotate the valve into the position shown in fig5 b . as a result , the column of blood 38 begins to fall through the riser tube r , through the valve mechanism 946 , into the flow restrictor 24 , through the adaptor 34 and into the central portion 31 of the fluid collector 26 . as mentioned earlier , the processor 30 is informed by the level detector 400 when the open end 36 of the adaptor 34 is submerged under the level of the collected blood 300 in order to minimize any surface tension effects . next , the valve driver 986 is commanded by the processor 30 into the position shown in fig5 c which halts all motion of the column of blood 38 . the initial position of the column of blood , hi , is thereby established for viscosity determination purposes , as will be discussed later . finally , the processor 30 commands the valve driver 986 to rotate the valve into the position shown in fig5 d and the column of blood 38 begins falling while data is collected . the overflow detector 981 may comprise an optical source 981 a , e . g ., a light emitting diode ( led ) and a photodetector 981 b for detecting emitted light from the optical source 981 a ; once the upper end of the column of blood 38 interrupts the emitted light , the photodetector 981 b informs the processor 30 which operates the valve mechanism 946 , as discussed previously . it should be understood that this implementation of the overflow detector 981 is exemplary only and that it is within the broadest scope of this invention to include all methods of level detection known to those skilled in the art of detecting the level of the column of blood 38 in the riser tube r . [ 0061 ] fig6 depicts a second embodiment of the mdcbv 920 wherein the flow restrictor 24 forms the lower end of the riser tube r , rather than being located on the other side of the valve mechanism 946 . as a result , the input side 5 of the adaptor 34 is coupled to the valve mechanism 946 . for proper operation , the datum line needs to be above the input side 7 of the flow restrictor 24 , as shown in fig6 . other than that , the operation of this variation is governed by the same equations for the first embodiment as will be discussed below . [ 0062 ] fig7 depicts a third embodiment of the mdcbv 920 wherein the valve mechanism 946 ′ is positioned at the top of the riser tube r , rather than at the bottom . the advantage of this valve mechanism 946 ′ position is that there is no need to first fill the riser tube r to a predetermined level before proceeding with the test run ; instead , in accordance with the valve mechanism 946 ′ operation as shown in fig8 a - 8 b , the test run proceeds with the processor 30 commanding the valve driver 986 to rotate the valve to the position shown in fig8 a and then the processor 30 stops any more input flow from the blood conveyor 926 as shown in fig8 b . in particular , as used in this embodiment , the blood conveyor 926 is coupled to the valve mechanism 946 ′ at a port 763 ; the top end of the riser tube r is coupled to the valve mechanism 946 ′ at a port 765 . the valve mechanism 946 ′ also includes a vent coupler 762 that couples the top of the riser r to a third port 764 that is exposed to atmospheric pressure ; thus when the valve is rotated into the position shown in fig8 b , the blood in the riser tube r will flow downwards . again , it should be emphasized that to minimize any surface tension effects , the level detector 400 informs the processor 30 when the open end of the adaptor 34 is submerged in the collected blood 300 . other than that , the operation of this variation is governed by the same equations mentioned previously . the concept of the blood viscosity determination using the mdcbv 920 is based on the discussion of determining the viscosity of non - newtonian fluids , such as blood , as discussed in detail in application ser . no . 09 / 789 , 350 , whose entire disclosure is incorporated by reference herein . the mdcbv 920 basically comprises a cylinder ( i . e ., the riser tube r ) having a diameter , φ r , into which a portion of the circulating blood of the living being is diverted for viscosity analysis . the bottom of the riser tube r is coupled to the flow restrictor 24 ( e . g ., a capillary tube ), having a diameter φ c and a length l c . it is preferable that the diameter of the adaptor 34 be similar to the diameter of the riser tube r , φ r . using this configuration of riser tube r and flow restrictor 24 , once the column of blood 38 is generated ( as shown in fig4 ), when the valve mechanism 946 is rotated to the position shown in fig5 b , the column of blood 38 is subjected to a decreasing pressure differential that moves the column 38 through a plurality of shear rates ( i . e ., from a high shear rate at the beginning of the test run to a low shear rate at the end of the test run , as can be clearly seen in the column height change — fig1 a and the mass accumulating in the collector 26 ′— fig1 b ), which is especially important in determining the viscosity of non - newtonian fluids , such as blood . in particular , once the desired height , h i is achieved by the column of blood 38 and with the upper end of the riser tube r exposed to atmospheric pressure , a pressure differential is created between the column of fluid 38 and the outlet 36 of the adaptor 34 . as a result , the column of blood 38 flows down the riser tube r , through the flow restrictor 24 , through the adaptor 34 and into the collector 26 ′. as the column of blood 38 flows through these components , the movement of column of blood 38 causes the pressure differential to decrease , thereby causing the movement of the column of blood 38 to slow down . this movement of the column of blood 38 , initially at a high shear rate and diminishing to a low shear rate , thus covers the plurality of shear rates . however , it should be understood that it is within the broadest scope of this invention to include any other configurations where the column of blood 38 can be subjected to a decreasing pressure differential in order to move the column of blood 38 through a plurality of shear rates . the rate of flow through the flow restrictor 24 is equal to the rate of change of the mass of the blood 300 collected on the mass detector 28 . hence , the corresponding flow rate in the flow restrictor 24 can be expressed as : q  ( t ) = 1 ρ    m  t ( 1 ) in order to determine the viscosity of the blood , it is necessary to know the pressure drop across the flow restrictor 24 . what is measured using the mdcbv 20 is the total pressure drop between the riser tube r and the flow restrictor 24 including not only the pressure drop across the flow restrictor or capillary tube 24 ( δp c ) but also the pressure drop occurring at the inlet and outlet ( δp e ) of the capillary tube 24 . one of the accurate methods for determining ( δp e ) is to make a bagley plot ( see c . w . macosko , rheology : principles , measurements , and applications ( vch , 1993 )) with at least two short capillary tubes ( not shown ) of the same diameter . hence , the pressure drop occurring at the inlet and at the outlet of the capillary tube 24 has to be subtracted from the total pressure difference ( δp t ). considering these pressure drops , the pressure drop across the capillary tube 24 can be described as it should be noted that the contribution from the second term on the right hand side ( δp e ) in eq . ( 2 ) is less than 0 . 5 %; hence this term can be neglected for all practical purposes , and as a result , equation 2 reduces to : an expression , therefore , for the total pressure as well as the pressure across the capillary tube 24 is : δ p t = δp c = ρg [ h i − δh ( t )− h ∞ ]= ρg [ h i − h ∞ δh ( t )] ( 4 ), where δh ( t ) represents the changing height of the falling column of blood 38 and is given by the following equation : δ   h  ( t ) = 4  m  ( t ) ρπ   φ r 2 ( 5 ) h i is the initial height of the column of blood 38 ; h ∞ is the final height of the column of blood 38 after a long period of time ; and in addition , the final mass after a long period of time , m ∞ , can be expressed in terms of the height of the column of blood 38 as follows : m ∞ - m i = ρ  ( πφ r 2 4 )   ( h i - h ∞ ) ; ( 6 ) ( h i - h ∞ ) = 4  ( m ∞ - m i ) ρπφ r 2 ( 7 ) thus , making the substitution of equations 5 and 7 into equation 4 , δ   p c = ρ   g  [ 4  ( m ∞ - m i ) ρπ   φ r 2 - 4  m  ( t ) ρπφ r 2 ] = 4  g πφ r 2  [ m ∞ - m i - m  ( t ) ] ( 8 ) it is assumed that any surface tension effects are constant with time and throughout the test run , e . g ., the surface tension experienced at h i is similar to the surface tension effect experienced at h ∞ . the significance of equation 8 includes , among other things , that in order to determine the pressure across the capillary tube 24 , only the final mass , m ∞ , the diameter of the riser r and the mass data detected by the mass detector 28 , m ( t ), need be known ; the initial height of the blood column 38 , h i , nor the final height , h ∞ , nor the initial mass , m i , need to be known . furthermore , equation 8 also represents , in accordance with the assumption that the surface tension is constant , a surface tension - free capillary . the shear rate dependent viscosity for a non - newtonian fluid , such as blood , flowing in the capillary tube 24 is obtained from experimental data with some mathematical treatment , and the necessary equations can be found in any standard handbook ( e . g ., c . w . macosko ). the shear rate at the capillary tube 24 wall is obtained form the classical weissenberg - rabinowitsch equation ( see s . l . kokal , b . habibi , and b . b . maini , novel capillary pulse viscometer for non - newtonian fluids , review of scientific instrument , 67 ( 9 ), pp . 3149 - 3157 ( 1996 )): γ . w  ( t ) = -  v z  r  r = r = 1 4  γ . aw  [ 3 +   ln   q  ln   τ w ] ( 9 ) where { dot over ( γ )} aw is the apparent or newtonian shear rate at the wall and where φ c is the diameter of the capillary tube 24 . γ . aw  ( t ) = 32   q  ( t ) πφ c 3 ( 10 ) τ w  ( t ) = δ   p  ( t )  φ c 4  l c ( 11 ) thus , the viscosity corresponding to the wall shear rate is calculated in the form of a generalized newtonian viscosity : η = τ w γ . w = πφ c 4  δ   p 32  ql c  ( 3 +   ln   q  ln   τ w ) - 1 = ρ   g   φ c 4 8  l c  φ r 2  [ m ∞ - m i - m  ( t ) ] (  m  t )   ( 3 + 1 n ′ ) ( 12 ) where   1 n ′ =   ln   q  ln   τ w . thus , equation 12 represents the viscosity of the blood in terms of the mass measured by the mdcbv 920 . the viscosity versus shear rate information can be obtained from equations 9 - 12 by measuring the mass of the collected fluid with respect to the time from which the pressure drop and flow rate can be calculated . the values of r and l c must be obtained by calibration . since equation ( 9 ) is non - linear , the procedure to calculate the shear rate and the corresponding viscosity is not straightforward . one of the approaches to obtain the viscosity from the general equations presented above is to adopt a finite difference technique for differentiation of equation ( 9 ). if there is enough data near the point of interest , it is possible to evaluate the derivative as : 1 n ′ =  ln   q  ln   τ w = 1 n ( 13 ) where n is simply the exponent of the power law constitutive equation . even though the power - law exponent is used in the above equations , this does not limit the capability of the present measurement for power - law fluids . the rigorous approach can still be taken for obtaining a viscosity versus shear rate relationship for any fluid ( see s . l . kokal , b . habibi , and b . b . maini , “ novel capillary pulse viscometer for non - newtonian fluids , review of scientific instrument , 67 ( 9 ), 3149 - 3157 ( 1996 )). in application ser . no . 09 / 789 , 350 there is a figure , namely , fig7 which illustrates the viscosity results using a mass detector viscometer for blood and which shows an excellent agreement with those from a conventional rotating viscometer , e . g ., the physica uds - 200 over a range of shear rates . as mentioned earlier fig1 a and 1b provide a summary of the height vs . time characteristic , and the mass vs . time characteristic , of the falling column of blood 38 during the viscosity test run . as can be seen in fig8 a , the level of the column of blood 38 initially is at h i . during the test run , the column of blood 38 falls and arrives at a final column height of h ∞ after a long period of time ( e . g ., 2 - 5 minutes after the column of blood 38 begins to fall ). as also mentioned earlier , this final height h ∞ can be attributed to both the surface tension effect of the gas - liquid interface 23 ( fig4 ) as well as any yield stress , τ y , exhibited by the blood . with regard to the change in mass , m ( t ), as shown in fig8 b , the mass climbs quickly and then slows down towards a final mass value , m ∞ after a long period of time . as mentioned earlier , what is important here is that the viscosity of the blood can be determined using the mdcbv 920 without the need to know h i and h ∞ . [ 0091 ] fig9 depicts a fourth embodiment of the mdcbv 920 wherein the changing mass of the riser r and flow restrictor 24 are detected , rather than detecting the change in mass of the collected blood 300 in the collector 26 . thus , rather than obtaining an increasing mass with time , the mass detector 28 detects the decreasing mass of the riser r / flow restrictor 24 assembly with time , as shown in fig1 . the empty weight of the riser r , flow restrictor 24 and a base 29 ( upon which the flow restrictor 24 is disposed ) are taken into account before the test run is conducted . as a result , the expression for the pressure drop across the capillary tube 24 is : δ   p c = 4  g πφ r 2  [ ( m i - m ∞ ) - m  ( t ) ] . ( 14 ) other than that , the theory of operation of this fourth embodiment of the mdcbv 920 is similar to that discussed above with regard to the other embodiments of the mdcbv 920 . a column height detection capillary ( chdc ) blood viscometer 1020 is discussed next . the chdc blood viscometer 1020 utilizes the same structure , for example , the riser tube r and the flow restrictor 24 , but with the mass detector 28 and the overflow detector 981 replaced by column level detector 1056 . as a result , the viscosity of the circulating blood of the living being can be determined using the chdc viscometer 1020 . in particular , it can be shown that the viscosity of the circulating blood , η , is given by : η = ρ   g   φ c 4 8  l c  φ r 2  ( h i - h ∞ - δ   h  ( t )  h  ( t )  t  ( 3 + 1 n ′ ) ) the column level detector 1056 is similar to the one disclosed in application ser . no . 09 / 573 , 267 whose entire disclosure is incorporated by reference herein . the column level detector 1056 detects the level of the column of blood in the riser tube r and may comprise and led array 1064 and a ccd 1066 arrangement ( fig1 ). to that end , the chdc blood viscometer 1020 basically comprises the blood receiver 922 and an analyzer / output portion 1024 . it should be emphasized that it is within the broadest scope of this invention to include all ways known in the art for detecting the level of the column of blood and the present invention is not limited , in any way , to the use of optical detection . as with the mdcbv 920 , the output side 3 of the flow restrictor 24 can be integrally formed with the input side 5 of the adaptor 34 . [ 0098 ] fig1 depicts one embodiment of the chdc blood viscometer 1020 which operates similarly to the mdcbv 920 except that the level of the column of blood 38 is monitored rather than the changing mass in the collector 26 . in addition , the function of the overflow detector 981 in the mdcbv 920 is accomplished by the column level detector 1056 , thereby informing the processor 30 when to operate the valve mechanism 960 to allow the column of blood 38 to fall . as a result , the chdc blood viscometer 1020 utilizes height vs . time data , as shown in fig1 a , to determine the blood viscosity . fig1 is a functional diagram of the chdc blood viscometer 1020 that depicts the operation of the chdc blood viscometer 1020 , including the use of the submerged end 36 of the adaptor 34 and the level detector 400 . [ 0099 ] fig1 is a second embodiment of the chdc blood viscometer 1020 wherein the flow restrictor 24 forms the lower end of the riser tube r , rather than being located on the other side of the valve mechanism 946 . as a result , the input side 5 of the adaptor 34 is coupled to the valve mechanism 946 . for proper operation , the datum line needs to be above the input side 7 of the flow restrictor 24 , as shown in fig1 . other than that , the operation of this variation is governed by the same equations for the first embodiment of the chdc blood viscometer 1020 as will be discussed below . [ 0100 ] fig1 depicts a third embodiment of the chdc blood viscometer 1020 wherein the valve mechanism 946 ′ is positioned at the top of the riser tube r , rather than at the bottom . the same discussion that applies to the third embodiment of the mdcbv 920 that was discussed earlier , applies here for the chdc blood viscometer 1020 . without further elaboration , the foregoing will so fully illustrate our invention and others may , by applying current or future knowledge , readily adapt the same for use under various conditions of service .