Abstract:
A vascular sensing system includes blood flow restricting means, a sensor, and means for producing an output representing a return of blood flow after the blood vessel has been temporarily collapsed by the blood flow restricting means. The blood flow restricting means is capable of placement on a human toe having a blood vessel, and is capable of manipulating the blood vessel. The sensor is operably connected to the blood flow restricting means and is physically spaced from the toe. Further, a method of vascular sensing includes taking pressure measurements with an pressure cuff positioned on a toe, and conducting a waveform analysis of the pressure measurements to determine a return of blood flow pressure.

Description:
BACKGROUND OF THE INVENTION 
   Blood pressure measurement is generally referred to as sphygmomanometry. Segmental sphygmomanometry is measurement of blood pressures at different portions, or segments, of a patient&#39;s body. Often, bilateral vascular measurements are taken along symmetrical segments of a patient&#39;s body, for instance, left and right ankles, and left and right forearms. Segmental sphygmomanometry allows comparisons of blood pressures between segments and between symmetrically paired locations, which can provide information as to conditions of corresponding blood vessels. Peripheral arterial disease (PAD) is a condition where fatty deposits (or plaque) collect along walls of blood-carrying arteries. PAD is also known as atherosclerosis or the hardening of arteries. PAD is associated with a high risk of both fatal and nonfatal ischemic events, such as myocardial infarction (MI), stroke, and other thromboembolic events. However, once detected, plaque buildup associated with PAD can often be stopped or reduced. 
   One important and well-known blood pressure indicator is the ankle-brachial index (ABI). The ABI provides a ratio of a systolic blood pressure in a patient&#39;s ankle divided by a systolic blood pressure in the patient&#39;s arm. ABI readings that fall outside of a normal range (e.g., outside about 0.91 to about 1.30) and asymmetrical bilateral ABI readings (e.g., ABI readings that differ significantly between left and right limbs) are indicators that assist in diagnosis of PAD. 
   Segmental sphygmomanometry can be conducted at a vascular lab using non-invasive testing equipment. However, many patients do not undergo regular vascular testing. Moreover, PAD is generally under-diagnosed. Yet it is desirable to diagnose PAD prior to an ischemic event. More robust diagnoses of PAD are possible with the aid of segmental blood pressure testing in a primary care environment. Primary care is basic or general care usually given by doctors who work with general and family medicine, internal medicine (internists), pregnant women (obstetricians), and children (pediatricians). In addition, a nurse practitioner (NP), a State licensed registered nurse with special training, can also provide this basic level of health care. A substantial obstacle to providing segmental blood pressure testing in the primary care environment is the complexity of testing procedures and testing equipment. 
   Known segmental blood pressure testing equipment can include multiple pressure cuffs and multiple flow sensors, all of which require proper connection to testing control equipment and proper positioning relative to a patient&#39;s body. Generally, a segmental testing procedure is conducted as follows. A number of blood pressure cuffs are simultaneously placed on the extremities on which the pressure measurements are to be performed. Three locations are typically included: arm, ankle and toe. A flow sensor, such as a Doppler flow sensor, is placed over a desired artery distal to the inflated cuff. Then, in order to obtain a pressure measurement at a cuff, the cuff is inflated to a pressure higher than the patient&#39;s systolic blood pressure. The precise pressure level to which a cuff is inflated is determined by medical personnel (i.e., the primary care provider) operating the testing equipment. Inflation of a cuff temporarily halts blood flow at that cuff. Then the pressure in the cuff is gradually lowered by medical personnel, and a pressure reading is taken at the appearance of a distal blood flow (i.e., a return of blood flow), which is detectable with the flow sensor as a point of apparition of a pulsating waveform generated on a display screen of the testing equipment or as an audible nock. 
   Improper use of segmental blood pressure testing equipment due to inadequate training and incorrect technique can undermine diagnostic utility of the testing procedure. For instance, the flow sensor must be properly positioned relative to vasculature to obtain accurate results. Primary care providers can be overburdened by the use of complex segmental blood pressure testing equipment. Mover, documentation of vascular data is subjective, because operators select return of flow pressures based upon the appearance of an audible nock or by waveform interpretation. This presents an obstacle to obtaining accurate vascular test data in the primary care environment. Complexity and variability of prior art systems prevents primary care providers from integrating diagnostic procedure and practice, thereby inhibiting disease detection. 
   Diagnoses of cardiovascular conditions may require interpretation of vascular test data by a specialist. Vascular testing conducted in a primary care environment may require interpretation by a physician qualified in an appropriate specialty who is in a location physically remote from the primary care environment. Intercommunication of test data and test interpretation becomes important in providing quick diagnoses. 
   It is therefore desired to provide a vascular sensing system that is sufficiently easy to use in a primary care environment, so that primary care providers, such as technologists and primary care physicians, can reliably and accurately perform testing and acquire cardiovascular data. It is further desired to provide vascular test data to a qualified interpreting physician, who may be at a location remote from the primary care environment, thereby facilitating a diagnosis by a physician qualified in an appropriate specialty. 
   Thus, a reliable and accurate vascular testing system is needed that easily permits non-invasive measurement of vascular pressure characteristics in a primary care environment for assisting diagnosis of vascular conditions. 
   BRIEF SUMMARY OF THE INVENTION 
   The present invention relates to a sensing system and method for measuring vascular pressures. The vascular sensing system includes blood flow restricting means, a sensor, and means for producing an output representing a return of blood flow after the blood vessel has been temporarily collapsed by the blood flow restricting means. The blood flow restricting means is capable of placement on a human toe having a blood vessel, and is capable of manipulating the blood vessel. The sensor is operably connected to the blood flow restricting means and is physically spaced from the toe. 
   Further, the method of vascular sensing includes taking pressure measurements with an pressure cuff positioned on a toe, and conducting a waveform analysis of the pressure measurements to determine a return of blood flow pressure. 

   
     BRIEF DESCRIPTION OF THE DRAWINGS 
       FIG. 1  is an exemplary representation of an arrangement of a vascular sensing system. 
       FIG. 2  is an exemplary representation of vascular testing locations. 
       FIG. 3  is a block diagram of a diagnostic test unit. 
       FIG. 4  is a graph of a cuff pressure signal over time, as cuff pressure is gradually decreased. 
       FIG. 5  is a graph of resultant pressure oscillations in the cuff pressure signal of  FIG. 4 . 
       FIG. 6  is a graph plotting peak-to-trough pressure amplitude of the pressure oscillations of  FIG. 5  versus the corresponding cuff pressure of  FIG. 4 . 
       FIG. 7  is a graph of a bell-shaped curve fitted to the plot of  FIG. 6 . 
       FIG. 8  is a block diagram of a digit pressure filtering algorithm. 
       FIG. 9  is a graph of an amplified pressure signal. 
       FIG. 10  is a graph of a bias signal corresponding to the pressure signal of  FIG. 9 . 
       FIG. 11  is a flow chart of a bleed rate adjustment algorithm. 
       FIG. 12  is a graph of resultant cuff pressure oscillations after adjustment. 
   

   DETAILED DESCRIPTION 
   The present invention relates to a vascular testing system. More particularly, the present invention relates to a vascular testing system for non-invasive measurement of vascular pressure and flow characteristics in a primary care environment. 
   Vascular conditions such as peripheral arterial disease (PAD) are problematic. In general, and particularly where a patient exhibits one or more symptoms of PAD, it is desirable to conduct vascular testing in a primary care environment. PAD symptoms are present when patients experience leg pain with exercise, experience leg pain at rest, have a non-healing wound on a foot or leg, or have numbness or discoloration in a foot or leg. In addition, patients over the age of 70 having decreased pedal pulses and patients over the age of 50 who smoke and/or have diabetes and have decreased pedal pulses are at risk for PAD. 
   Segmental sphygmomanometry is measurement of blood pressures at different portions, or segments, of a patient&#39;s body. Bilateral vascular measurements are measurements taken along symmetrical segments of a patient&#39;s body, for instance, left and right ankles, and left and right forearms. Segmental sphygmomanometry allows comparisons of blood pressures between segments and between symmetrically paired locations, which can provide information as to conditions of corresponding blood vessels. One important and well-known segmental blood pressure indicator is the ankle-brachial index (ABI). 
   Another vascular test is pulse volume recording (PVR). PVR involves the use of pressure cuffs to determine characteristics of blood flow by measuring a volume change in a limb segment. This is achieved by inflating a pressure cuff so that it is sensitive to the swelling and contraction of a limb segment with each heartbeat, but not tight enough to prevent blood flow. In that way blood volume changes per cardiac cycle can be measured. 
     FIG. 1  is an exemplary representation of an arrangement of a vascular testing system  20 . The vascular testing system  20  includes a diagnostic test unit  22  having a single air outlet  24 , and one or more pressure applicators  26 . The diagnostic test unit  22  can be connected to a computer  30  having a display  32  for providing an interface  34  with the vascular testing system  20 . 
   As shown in  FIG. 1 , the vascular testing system  20  is utilized in a primary care environment for sensing and testing vascular conditions of a patient  36 . A care provider  38 , such as a lab technician or a primary care physician, can position the one or more pressure applicators  26  along the patient&#39;s  36  body. The one or more pressure applicators  26  are oscillometric pressure cuffs. Each of the pressure applicators  26  can be positioned at an exterior location along the patient&#39;s  36  body for sensing vascular pressures at desired vascular locations, such as at toes, ankles, thighs and arms. One or more pressure applicators  26  can be placed on a patient&#39;s  36  body at a time. 
   In the embodiment shown in  FIG. 1 , the diagnostic test unit  22  includes a single air outlet  24  such that only one pressure applicator  26  can be connected to the diagnostic test unit  22  at a time. The interface  34  permits display of instructions for guiding the care provider  38  through a process of engagement and disengagement of particular pressure applicators  26  positioned at particular vascular locations, (such as those shown in  FIG. 2 ) to the air outlet  24  of the diagnostic test unit  22 . 
   Each of the pressure applicators  26  can be attached to the air outlet  24  of the diagnostic test unit  22 , in fluid communication therebetween. Tubing or other suitable connectors can be used to connect each of the pressure applicators  26  to the diagnostic test unit  22 . Because the diagnostic test unit  22  has a single air outlet  24  in the embodiment shown in  FIG. 1 , only a single pressure applicator  26  is connected to the diagnostic test unit  22  at one time. This minimizes a risk of improper connections, and generally simplifies set-up of the vascular testing system  20 . 
   The diagnostic test unit  22  is capable of continuously streaming raw pressure data to the interface  34  during operation. The diagnostic test unit  22  can be connected to the computer  30 , which can be a PC type desktop or laptop computer. The computer  30  permits, inter alia, collecting, sorting, interpretering, organizing, displaying and transmitting data from the diagnostic test unit  22 . The computer  30  operatively communicates with the interface  34 . 
   Generally, the interface  34  permits interaction with the vascular testing system  20  by the care provider  38 . The interface  34  in the primary care environment allows display of measurements sensed by the vascular testing system  20 , such as current pressure reading values and captured waveform data. The interface  34  further allows the care provider  38  to enter patient data to a database, which facilitates coordination of various patient data with information collected as part of vascular testing. The interface  34  can include forms and displays for patient information, insurance information, history/risk factors, visit data, indications of a test, results of a test, interpretation (this function can be disabled until the test is signed by a qualified diagnosing physician), and reporting. In addition, the interface  34  can provide suitable appointment, scheduling and billing functionality. In one embodiment, the interface  34  includes software compatible with Microsoft WINDOWS operating systems. In further embodiments, the interface  34  may include other types of software (e.g., software compatible with UNIX, LINUX, MACINTOSH, or other operating systems). 
   The vascular testing system  20  can be connected to the Internet, via a modem or other similar device, for communicating with servers and a remote interface. For instance, data collected in the primary care environment can be transmitted over the Internet or other network, via file transfer protocol (FTP) or other suitable means, to a database server (not shown) that in turn communicates with an interface (not shown) physically remote from the primary care environment, such as at a specialized vascular laboratory. Data can thereby be transmitted, with appropriate compression and/or encryption, between an interface on a technician-side (e.g., the interface  34  in the primary care environment) and a specialist-side interface (e.g., an interface in a vascular laboratory). Transmittal of vascular data collected in the primary care environment can be transmitted to a qualified interpreting physician, such as a specialist in an appropriate vascular field, for interpreting the data and making a diagnosis. 
   An Internet-compatible vascular testing system can be configured such as that described in U.S. patent application Ser. No. 10/227,770, entitled SYSTEM AND METHOD FOR TESTING FOR CARDIOVASCULAR DISEASE, which is hereby incorporated by reference in its entirety. 
     FIG. 2  is an explementary representation of vascular testing locations, including arm locations  40 L and  40 R, thigh locations  42 L and  42 R, calf locations  44 L and  44 R, ankle locations  46 L and  46 R, and toe locations  48 L and  48 R. 
   Segmental pressure testing can be conducted at vascular locations such as the arm locations  40 L and  40 R, the ankle locations  46 L and  46 R, and the toe locations  48 L and  48 R. PVR testing can be conducted at vascular locations such as the thigh locations  42 L and  42 R, the calf locations  44 L and  44 R, and the ankle locations  46 L and  46 R. Pressure measurements at particular vascular locations are generally taken over a period of about 15 seconds to about 60 seconds. 
     FIG. 3  is a block diagram of the diagnostic test unit  22 . The diagnostic test unit  22  includes a central processing unit (CPU)  70 , reset and supervisory circuitry  72 , non-volatile memory  74 , a bridge  76 , an external connector  78 , a medical power supply  80 , an internal power regulator  82 , and means for controlling pressure in a pressure applicator including a motor driver  84 , an electric motor  86  (e.g., a DC motor), a micro-diaphragm pump  88 , a first valve  90 , a first valve  92 , a proportional valve driver  94 , a variable orifice valve  96  (e.g., a proportional valve), a relief valve  98 , a pressure sensor  100 , and an air outlet  24 . The diagnostic test unit also includes a signal processor  102 . The diagnostic test unit  22  can further include a power entry  104  and an power switch  106 . 
   The reset and supervisory circuitry  72  and non-volatile memory  74  are operatively connected to the CPU  70 . The external connector  78 , which can be a universal serial bus (USB) connector, is operatively connected to the CPU  70  via the bridge  76 . The medical power supply  80  provides two distinct supply voltages to the diagnostic test unit  22  (e.g., providing voltages of 12 volts and 5 volts). The medical power supply  80  further supplies power to the internal regulator  82 , which in turn can supply power at a third voltage (e.g., 3.3 volts). 
   The electric motor  86  is operatably connected to the mirco-diaphragm pump  88  and to the CPU  70  via the motor driver  84 . The micro-diaphragm pump  88  is in fluid communication with the first valve  92 , which is operatably connected to the CPU  70  via the first valve driver  90 . The variable orifice valve  96  is in fluid communication with the first valve  92 , and is operatably connected to the CPU  70  via the variable orifice valve driver  94 . The relief valve  98  is in fluid communication with the variable orifice valve  96 . The pressure sensor  100  is in fluid communication with the relief valve  98  and the air outlet  24 . The pressure sensor  100  is disposed between the valves  92 ,  96 ,  98  and the air outlet  24 , and does not contact a patient&#39;s body. Further, output from the pressure sensor  100  can be transmitted to the signal processor  102 , which is electrically connected to the CPU  70 . 
   The CPU  70  provides control of functions of the diagnostic test unit  22 , such as actuating the electric motor  86  and controlling valves (e.g., the variable orifice valve  96 ). In one embodiment, the CPU  70  is a model HD64F2317 16 Bit CPU available from Hitachi America, Ltd., Brisbane, Calif. 
   The external connector  78  permits the diagnostic test unit  22  to be connected to other devices, such as the computer  30  shown in  FIG. 1 . 
   The electric motor  86  drives the micro-diaphragm pump  88  to generate a fluid displacement pressure. Typically, a fluid displaced by the micro-diaphragm pump  88  is air. The micro-diaphragm pump  88  is connected in fluid communication with a series of one or more valves  92 ,  96 ,  98  by suitable tubing or the like. A one-way check valve (not shown) can be included with the micro-diaphragm pump  88  for preventing fluid flow back through the pump  88 . 
   The first valve  92  is generally positioned adjacent the micro-diaphragm pump  88 . In one embodiment, the first valve  92  is an on/off valve capable of connecting a fluid path to the pressure applicator  26  to either the pump (i.e., an “on” position) or to atmosphere (i.e., an “off” position). The variable orifice valve  96  is positioned adjacent the first valve  92  and distal to the micro-diaphragm pump  88 . The variable orifice valve  96  has a variable orifice size capable of dynamically changing. In one embodiment, the variable orifice valve  96  is a special proportional valve model EV-P-10-2507, available from Clippard Instrument Laboratory, Inc., Cincinnati, Ohio. 
   The relief valve  98  is a mechanical valve positioned adjacent the variable orifice valve  96  and distal to the micro-diaphragm pump  88 . The relief valve  98  facilitates safety monitoring by permitting the vascular testing system  20  to prevent pressure in a pressure applicator from exceeding a maximum value. For example, pressure in a pressure applicator can be prevented from exceeding about 240 millimeters mercury (mmHg) (e.g., using a 4.6 PSI relief valve). 
   The pressure sensor  100  permits measurement of pressures at any pressure applicator connected to the air outlet  24 , thereby allowing measurement of vascular characteristics at a corresponding vascular location. Signals from the pressure sensor  100  are transmitted to the signal processor  102 . The signal processor  102  can provide various standard forms of signal processing, such as analog-to-digital conversion, filtering, buffering, and gain adjustments. The signal processor  102  can be an analog signal processor. Signals are transmitted from the signal processor  102  to the CPU  70 . Additional safety protocol can be used. The first valve  92  can be used to prevent pressures from remaining in the system more than a pre-determined period of time. For example, pressures at and above about 220 mmHg may be allowed only for a period of 5 seconds, and any significant system pressure (e.g., a system pressure at and above about 15 mmHg) may be allowed only for a period of 180 seconds. When pressures remain in the system beyond the desired time period, the first valve  92  can be used to release pressure (e.g., vent fluid to the atmosphere). 
   An exemplary method of obtaining vascular measurements according to the present invention is now described. In operation, one or more pressure applicators or pressure cuffs are positioned at vascular locations at which a vascular pressure measurement is to be performed. An operative pressure cuff is first inflated to a pressure higher than a patient&#39;s systolic blood pressure, which occludes a blood vessel (i.e., causes a portion of a blood vessel to collapse and stop blood flow) at the vascular location. The particular level of pressure to which the operative pressure cuff is inflated is determined by the care provider  38  operating the vascular testing system  20 . After the blood vessel at the vascular location is occluded, pressure in the operative pressure cuff is automatically and gradually lessened. Pressure is gradually lessened in a slow, controlled manner (e.g., at a rate of about 3 to about 5 mmHg/second). Oscillations in pressure at the operative pressure cuff are caused by the patient&#39;s artery as the pressure in the pressure cuff is gradually decreased. 
   Pressure can be decreased in a number of ways, such as by decreasing the pressure supplied by the micro-diaphragm pump  88  or by adjusting the orifice size of the variable orifice valve  96 . In one embodiment, the size of the variable orifice valve  96  is utilized to adjust the applied pressure. The orifice size of the variable orifice valve  96  changes in order to maintain a generally linear decrease in pressure applied to the operative pressure cuff. A fixed orifice valve would exhibit an exponential bleed rate, whereas a generally linear bleed rate is desired. Size of the orifice can be controlled with software operative through the CPU  70 . Use of the variable orifice valve  96  to control applied pressure at an operative pressure applicator permits pressure readings to be obtained quickly. 
     FIG. 4  is a graph of a cuff pressure signal over time, as cuff pressure is gradually decreased. It is desirable to decrease the cuff pressure in a generally linear manner. Oscillations in pressure at the operative pressure cuff are recorded and amplified by the vascular testing system  20 . Such oscillations are indicative of blood flow conditions at the vascular location. 
   The cuff pressure signal is adjusted to compensate for the decreasing pressure applied to the operative pressure cuff by the micro-diaphragm pump  88 . Generally, this involves removing the ramp-shaped bias signal corresponding to the pressure applied to the operative pressure cuff.  FIG. 5  is a graph of result in pressure oscillations in the cuff pressure signal of  FIG. 4  after adjustment. Calculations, adjustments, and other appropriate data manipulation can generally be accomplished through software. Calculations, waveform analysis, and other data manipulation can be accomplished through the computer  30  and software of the interface  34 . In further embodiments, software for performing calculations, etc., can be operative through the CPU  70  of the diagnostic test unit  22 . 
     FIG. 6  is a graph plotting peak-to-trough pressure amplitude of the pressure oscillations of  FIG. 5  versus the corresponding cuff pressure of  FIG. 4 .  FIG. 6  represents raw data points corresponding to the amplitudes of the pressure oscillations. 
   After the amplitudes of pressure oscillations are collected, a bell-shaped curve is fitted to the raw data points obtained. Some noise filtering can occur throughout this process.  FIG. 7  is a graph of a bell-shaped curve fitted to the plot of  FIG. 6 . A peak amplitude of the curve, A Max , is determined. A Max  is typically determined according the bell-shaped curve, rather than by the raw data points themselves. Next, a return of blood flow is determined as a ratio of A Max . First, a value A R  is identified at a pre-determined percentage (e.g., seventy-five percent [75%]) of A Max . The value of A R  is indicative of a pressure oscillation amplitude at which blood flow returns at the vascular location. Next, a cuff pressure P R  corresponding to the peak-to-trough amplitude A R,  and taken along a higher pressure slope of the curve (i.e., the right-hand slope of the curve as shown in  FIG. 7 ), is recorded as the patient&#39;s return of blood flow pressure. The pressure P R  corresponds to a pressure measurement obtained by care providers using known types of vascular testing equipment (e.g., Doppler flow sensors). 
   Vascular testing at some vascular locations is facilitated by additional filtering and data processing. For instance, vascular locations on digits, such as on a toe, require the use of relatively small pressure cuffs sized to fit those locations. Vascular testing using relatively small pressure cuffs presents significant concerns with signal noise. In such situations, a signal-to-noise ratio is more problematic than for vascular measurements taken with relatively large pressure cuffs used on ankles, arms, etc. Methods of digit pressure filtering can be used to alleviate concerns with noise for vascular testing at vascular locations on digits. 
     FIG. 8  is a block diagapham of a digit pressure filtering algorithm. The digit pressure filtering algorithm is useful in taking pressure measurements at a vascular location on a digit (e.g., the toe locations  48 L and  48 R shown in  FIG. 2 ). 
   As seen in  FIG. 8 , an amplified cuff pressure signal is obtained. The amplified cuff pressure signal is also passed through a low pass filter. A bias signal is determined after the amplified cuff pressure signal is filtered. A bleed rate change detector permits detection of a rate of change in applied pressure, as applied pressure is decreased. This permits the vascular testing system  20  to zero out sections of the bias signal where the bleed valve is being adjusted. Using the digit pressure filtering algorithm, the vascular testing system  20  can determine an output or resultant pressure. 
     FIG. 9  is a graph of an amplified pressure signal from a vascular location on a digit. This amplified pressure signal is similar to that shown and described with respect to  FIG. 4 . 
     FIG. 10  is a graph of a bias signal curve corresponding to the pressure signal of  FIG. 9  after filtering. Portions of negative flow in the bias signal followed by a window of positive flow are shown in  FIG. 10  with a heavy line weight. Those weighted portions of the bias signal curve correspond to intervals where the bleed valve is being adjusted, meaning that an orifice size of a variable orifice (e.g., proportional) valve is changing. The orifice size of the variable orifice valve  96  changes in order to maintain a generally linear decrease in pressure applied to the pressure applicator  26 . 
     FIG. 11  is a flow chart of a bleed rate adjustment algorithm. The algorithm shown in  FIG. 11  permits opening of the valve more where a bleed rate is too low, and closing the valve more when the bleed rate is too high. In one embodiment, counters are used to increment a counter value when the bleed rate is outside a desired range. When the counter reaches a pre-determined value (e.g., 25), the variable orifice valve  96  is opened or closed more, as appropriate. 
     FIG. 12  is a graph of resultant cuff pressure oscillations after adjustment. Changing the size of the orifice introduces noise signals. Adjustment involves removing the bias signal from the amplified pressure signal and zeroing out intervals of bleed valve adjustment (i.e., regions of the bias signal curve indicated with a heavy line weight). The resultant pressure graph of  FIG. 12  is similar to that shown in  FIG. 5 . A return of flow pressure at the vascular location (e.g., the toe locations  48 L and  48 R shown in  FIG. 2 ) is then determined in a similar manner to that shown and described with respect to  FIGS. 6 and 7 . A pressure of return of blood flow, P R , can be determined as a ratio of a peak pressure oscillation amplitude A Max , such as at a point A R  that is 75% of A Max . 
   A pressure of return of blood flow, P R , obtained using any of the equipment and processes shown and described above can be utilized in diagnoses of vascular conditions. Values of P R  may differ from systolic pressures. Regardless, values of P R  can be used in segmental comparisons like the ABI, in a manner similar to the systolic pressures traditionally used in the ABI. 
   In addition to the testing processes shown and described above, the vascular testing system  20  can further take sphygmomanometric measurements such as systolic, mean and diastolic blood pressures using conventional measurement techniques. Such conventional techniques will be readily apparent to those skilled in the art. 
   Although the present invention has been described with reference to preferred embodiments, workers skilled in the art will recognize that changes may be made in form and detail without departing from the spirit and scope of the invention. For instance, vascular testing locations can include locations on a patient&#39;s body other than those specifically enumerated above.