System for measuring vital signs using bilateral pulse transit time

Not Applicable

1. Field of the Invention

The present invention relates to a system for measuring vital signs, particularly blood pressure, featuring a hand-held, cuffless vital sign monitor.

2. Description of Related Art

Pulse oximeters are medical devices featuring an optical module, typically worn on a patient's finger or ear lobe, and a processing module that analyzes data generated by the optical module. The optical module typically includes first and second light sources (e.g., light-emitting diodes, or LEDs) that transmit optical radiation at, respectively, red (λ˜600-700 nm) and infrared (λ˜800-1200 nm) wavelengths. The optical module also features a photodetector that detects transmitted radiation that passes through an underlying artery within, e.g., the patient's finger or earlobe. Typically the red and infrared LEDs sequentially emit radiation that is partially absorbed by blood flowing in the artery. The photodetector is synchronized with the LEDs to detect the transmitted radiation. In response, the photodetector generates a separate radiation-induced signal corresponding to each wavelength. The signal, called a plethysmograph, varies in a time-dependent manner as each heartbeat varies the volume of arterial blood and hence the amount of radiation absorbed along the path of light between the LEDs and the photodetector. A microprocessor in the pulse oximeter digitizes and processes plethysmographs generated by the red and infrared radiation to determine the degree of oxygen saturation in the patient's blood using algorithms known in the art. A number between 94%-100% is considered normal, while a number below 85% typically indicates the patient requires hospitalization. In addition, the microprocessor analyzes time-dependent features in the plethysmograph to determine the patient's heart rate.

Another medical device called an electrocardiograph features conductive electrodes, placed at various locations on a patient's body, that measure electrical signals which pass into an amplification circuit. The circuit generates a waveform called an electrocardiogram, or ECG, that describes a time-dependent response of the patient's cardiovascular system.

Various methods have been disclosed for using both plethysmographs and ECGs, taken alone or in combination, to measure arterial blood pressure. One such method is disclosed in U.S. Pat. No. 5,140,990 to Jones et al. The '990 patent discloses using a pulse oximeter with a calibrated auxiliary blood pressure measurement to generate a constant that is specific to a patient's blood pressure.

Another method for using a pulse oximeter to measure blood pressure is disclosed in U.S. Pat. No. 6,616,613 to Goodman. The '613 patent discloses processing a pulse oximetry signal in combination with information from a calibrating device to determine a patient's blood pressure.

U.S. Pat. Nos. 5,857,795 and 5,865,755 to Golub each discloses a method and device for measuring blood pressure that processes a time difference between points on an optical plethysmograph and an ECG along with a calibration signal.

U.S. Pat. No. 6,511,436 to Asmar discloses a device for evaluating arterial wall stiffness by using pulse wave velocity measurements. The device estimates blood pressure using pulse wave velocity and a patient's biometric parameters.

Chen et al, U.S. Pat. No. 6,599,251, discloses a system and method for monitoring blood pressure by detecting plethysmographs at two different locations on a subject's body, preferably on the subject's finger and earlobe. The plethysmographs are detected using conventional pulse oximetry devices and then processed to determine blood pressure.

Inukai et al., U.S. Pat. No. 5,921,936, discloses a system that uses an electrocardiogram to detect the start of a heart beat and uses a cuff equipped with a pressure sensor to detect pulse waves in order to calculate a pulse transit time.

Suda et al., U.S. Pat. No. 5,788,634, describes a multi-purpose, clip-on sensor featuring a ‘gripper’ that includes an electrode pair and an optical system operating in a transmission mode. The electrode pair and optical system generate information that is processed outside of the sensor to make a blood pressure measurement.

Baruch et al., U.S. Pat. No. 6,723,054, describes an arm-worn system featuring two optical systems that measure two independent signals from a patient's arm. A processor calculates mathematical derivatives of the signals to derive a pulse transit time which can be used to calculate blood pressure.

Suga et al., U.S. Pat. No. 5,316,008, describes a wrist watch that features both optical and electrical sensors for measuring signals from a patient. During operation, the patient wears the wrist watch on one wrist, and places fingers from an opposing hand on the optical and electrical sensors. A pulse transit time is extracted from the signals and then used to calculate a blood pressure.

In one aspect, the invention provides a hand-held monitoring device for measuring vital signs (e.g. blood pressure) from a patient that features: i) a housing that encloses a first sensor featuring a first electrode and a first optical system configured to generate a first optical signal; ii) a second sensor featuring a second electrode and a second optical system configured to generate a second optical signal; iii) an amplifier system, in electrical contact with the first and second electrodes, configured to processes electrical signals from the first and second electrodes to generate an electrical waveform; and iv) a microprocessor, in electrical communication with the amplifier system, first optical system, and second optical system, the microprocessor configured to process the electrical waveform and first and second optical signals (or processed versions of these signals and waveforms) with an algorithm to determine at least one of the patient's vital signs.

In preferred embodiments, the light source is an LED or diode laser configured to emit green radiation between 510 and 590 nm. Optical systems which use light sources in this spectral region are referred to herein as ‘green optical systems’. In other preferred embodiments, the optical system is configured to operate in a reflection-mode geometry, e.g. both the light source and photodetector are disposed on a same side of the substrate (e.g., a printed circuit board). In this case the photodetector is aligned to detect radiation first emitted from the light source and then reflected from the patient's tissue to generate the optical waveform.

The optical system and electrodes are typically housed within a hand-held or body-worn device. In this configuration, the electrical and optical sensors are typically oriented to measure electrical and optical signals from at least one of the patient's fingers. In still other embodiments, the monitoring device additionally includes an amplifier system (e.g. a two-stage amplifier system) configured to process the first and second electrical signals to generate an electrical waveform. The device can also use this same amplifier system, or a different amplifier system, to process the optical signals to generate an optical waveform. Alternatively, the electrical and optical sensors may be housed in distinct units that are in electronic communication with the housing containing the amplifier system and the microprocessor.

Alternatively, the first and second optical systems may be replaced by other sensor systems capable of identifying a time-dependent arrival of a pulse. Examples of other sensor systems that are capable of measuring pulse waves include tonometric sensor systems, ultrasound sensor systems, magnetic field sensor systems and oscillometric cuffs. The use of one of these alternative pulse detection systems enables the identification of a first and second pulse signal that can be used in place of the first and second optical signal, and in combination with the electrical waveform and an algorithm, to calculate at least one of the patient's vital signs.

In other alternate embodiments, calibration parameters are based on biometric data, e.g., height, arm span, weight, body mass index, and age. The calibration parameters may not be specific to an individual patient, but rather determined for a general class of patients. For example, the calibration parameters are based on correlations between blood pressure and features in the optical or electrical waveforms observed in the analysis of clinical data sets. Conjunctively, the calibration parameters may be based on correlations between biometric parameters and features in the optical or electrical waveforms observed in the analysis of clinical data sets.

In embodiments, the microprocessor or microcontroller within the monitor runs computer code or ‘firmware’ that determines blood pressure by processing: 1) a first time-dependent feature of the optical waveform; 2) a second time-dependent feature of the electrical waveform; and 3) a calibration parameter. In this case the calibration parameter is determined by a conventional device for measuring blood pressure, such as a blood pressure cuff.

In other embodiments, the system features a first light source that emits green radiation to generate a first optical waveform, and a second light source that emits infrared radiation to generate a second optical waveform. In this case the device runs computer code or firmware that processes the first and second optical waveforms to generate a pulse oximetry value using techniques that are known in the art. In a related embodiment, the device can run computer code or firmware that processes the optical waveform to generate a heart rate value. In yet another embodiment, the device can run computer code or firmware that processes the first and second electrical signals to generate an ECG waveform, which can then be processed to calculate a heart rate.

In another aspect, the invention provides a hand-held device for measuring vital signs (e.g. blood pressure) from a patient that features: i) a housing; ii) a first optical system, enclosed by the housing, configured to generate a first optical signal; iii) a second optical system, also enclosed by the housing, configured to generate a second optical signal; and iv) a microprocessor, in electrical communication with the first optical system and second optical system, the microprocessor configured to process the first and second optical signals with an algorithm to determine at least one of the patient's vital signs.

In yet another aspect, the invention provides a hand-held device for measuring vital signs (e.g. blood pressure) from a patient that features: i) a first optical system at a first location on a subject and configured to generate a first optical signal; ii) a second optical system at a second location on a subject that is approximately mirror-symmetric about the patient's sagittal plane (i.e. a plane representing the median plane of the patient's body) to that of the first location and configured to generate a second optical signal; and iii) a microprocessor, in electrical communication with the first optical system and second optical system, the microprocessor configured to process the first and second optical signals with an algorithm to determine at least one of the patient's vital signs. Examples of locations of the first and second optical systems, respectively, include the left ear lobe and right ear lobe, the left radial artery at the subject's left wrist and the right radial artery at the subject's right wrist, any left-hand finger and any right-hand finger, any left-foot toe and any right-foot toe.

In another aspect, the invention describes a method of calculating a patient's blood pressure, comprising the steps of: i) detecting an electrical waveform corresponding to the potential difference between a first electrode at a first location on a subject and a second electrode at a second location on a subject; ii) detecting a first pulse signal on a subject and calculating a first time difference between the occurrence of a first feature on the electrical waveform and a second feature on the first pulse signal; iii) detecting a second pulse signal on a subject and calculating a second time difference between the second pulse signal and the first pulse signal; and iv) calculating the subject's blood pressure using the first time difference, the second time difference, and an algorithm relating those time differences to blood pressure. The second time difference may be calculated as a time difference between a first feature on the first pulse signal and a second pulse feature on the second pulse signal. Alternatively, the second time difference may be calculated as the time delay measured using the cross correlation between the first pulse signal and the second pulse signal. The first and second pulse signals may additionally be mathematically transformed (e.g., derivatized, averaged).

The invention has many advantages. In particular, through use of an optical system operating in a reflection-mode geometry and based on a green light source, the invention measures optical waveforms that are relatively insensitive to motion-related artifacts and have a high signal-to-noise ratio, particularly when compared to waveforms measured using red or infrared radiation in a similar geometry.

In a more general sense, the invention provides an easy-to-use, low-profile system that measures a variety of vital signs, including blood pressure, without using a cuff. This and other information can be easily transferred to a central device through a wired or wireless connection to better characterize a patient. Using the system of the invention, information describing the patient's blood pressure can be viewed using an Internet-based website, personal computer, or a mobile device. Blood-pressure information measured throughout the day provides a relatively comprehensive data set compared to that measured during isolated medical appointments. For example, this approach identifies trends in a patient's blood pressure, such as a gradual increase or decrease, which may indicate a medical condition that requires treatment.

Having briefly described the present invention, the above and further objects, features and advantages thereof will be recognized by those skilled in the pertinent art from the following detailed description of the invention when taken in conjunction with the accompanying drawings.

FIG. 1 is a schematic view of the hand-held monitoring device for measuring vital signs according to the invention;

FIG. 2 is a schematic view of a patient's bilateral blood flow from the heart to the left and right sides of the body;

FIGS. 3A , 3 B, and 3 C show, respectively, graphs of optical and electrical waveforms generated with a first sensor, a second sensor, and optical waveforms generated from both the first and second sensors included in the monitor of FIG. 1 ;

FIG. 4 is a semi-schematic view of the monitoring device of FIG. 1 connected to a personal computer through a USB port or to an external radio through a wireless connection; and,

FIG. 5 is a schematic view of an Internet-based system that receives information from the monitoring device of FIG. 1 through a wireless connection.

FIG. 1 shows a hand-held vital signs monitoring device 10 according to the invention that measures blood pressure and other vital signs from a patient's fingers 13 A, 13 B (e.g., the index finger, thumb finger, etc.) using a technique referred to herein as ‘bilateral pulse transit time’, or BPTT. Blood pressure measured using BPTT may be more accurate than blood pressure measured using a technique based on conventional pulse transit time. To make a BPTT measurement, the patient holds the device 10 with both hands, gently inserting and pressing their left index finger 13 A inside a left sensor enclosure 14 A, and their right index finger 13 B inside a right sensor enclosure 14 B. Both the left 14 A and right 14 B sensor enclosures feature an LED system 15 A, 15 B, 61 A, 61 B, 62 A, 62 B that generates optical radiation at one or more wavelengths, and a photodetector 16 A, 16 B that detects radiation either reflected or transmitted from an artery in the inserted finger 13 A, 13 B. Each LED system 15 A, 15 B typically includes a green LED operating in reflection mode and red 61 A, 61 B and infrared 62 A, 62 B LEDs operating in transmission modes. An electrical system within the device detects and amplifies radiation from each index finger, as described in detail below. This generates time-resolved optical waveforms 29 A, 29 B, specific to each index finger, which are shown respectively on left 28 A and right 28 B portions of a display 18 . The optical waveforms, called an ‘optical plethysmograph’, are described in more detail below with reference to FIGS. 3A , 3 B, and 3 C. Each sensor enclosure 14 A, 14 B also includes a conductive electrode pad 17 A, 17 B that measures an electrical signal when in contact with the inserted finger 13 A, 13 B. The electrode pad 17 A, 17 B, for example, can be made of metal (e.g., brass), conductive rubber, or a conventional electrode material such as silver/silver chloride. Once generated, the electrical signals are processed with an amplifier circuit and then digitized to generate an electrical waveform 31 A, 31 B, similar to a conventional ECG, which is also shown on the left 28 A and right 28 B portions of the display 18 . Unlike the optical waveforms 29 A, 29 B, which specifically correspond to blood flowing in each index finger, a single electrical waveform 29 A, 29 B is determined by jointly processing electrical signals measured from each index finger using the amplifier circuit.

The device 10 measures blood pressure using BPTT by processing optical waveforms 29 A, 29 B and electrical waveforms 31 A, 31 B measured from each finger 13 A, 13 B or thumb 12 A, 12 B. Each waveform features a ‘pulse’ that corresponds to each of the patient's heartbeats. In the electrical waveforms 31 A, 31 B, this pulse represents electrical signals generated by the beating heart, and features a sharply varying feature within a conventional QRS complex of the ECG waveform. In contrast, for the optical waveforms 29 A, 29 B, the pulse varies more gradually and represents a time-dependent volumetric change in an underlying artery. A microprocessor in the device 10 calculates a pulse transit time (‘PTT’), described in more detail with reference to FIGS. 3A , 3 B, 3 C, by analyzing a time difference ΔT between a point on the optical 29 A, 29 B and electrical 31 A, 31 B waveforms (e.g., the peaks of these waveforms), along with other properties described in more detail below. ΔT measured from the optical waveform 29 A from the left index finger 13 A and the electrical waveform 31 A for two heartbeats are shown in the left-hand portion 28 A of the display, and are labeled ‘ΔT L,1 ’ and ‘ΔT L,2 ’. Similarly, time differences measured from the optical waveform 29 B from the right index finger 13 B and the electrical waveform 31 B for two heartbeats are shown in the right-hand portion 28 B of the display, and are labeled ‘ΔT R,1 ’ and ‘ΔT R,2 ’.

Referring to FIGS. 2 and 3A , 3 B, 3 C, the hand-held device 10 measures blood pressure using BPTT by processing optical waveforms 52 A, 52 B and electrical waveforms 50 A, 50 B measured simultaneously from each side of the patient's body. Each waveform includes a ‘pulse’ that corresponds to each of the patient's heartbeats. In the electrical waveforms 50 A, 50 B, this pulse represents electrical signals generated by the beating heart, and includes a sharply varying ‘peak’ within a conventional QRS complex of the ECG. In contrast, for the optical waveforms 52 A, 52 B, the pulse varies more gradually and represents a time-dependent volumetric change in an underlying artery. A microprocessor in the device 10 calculates a pulse transit time (‘PTT’), described in more detail below, by analyzing a time difference ΔT between a point on the optical 52 A, 52 B and electrical 50 A, 50 B waveforms (e.g., ΔT between the peaks of these waveforms). Specific points on the waveforms, such as their maxima or minima, can be determined by taking a first or second derivative of the waveform. ΔT measured from the optical waveform 52 A from the patient's left index finger and the electrical waveform 50 A is shown in FIG. 3A (labeled ΔT L ). Similarly, ΔT measured from the optical waveform 52 B from the right index finger and the electrical waveform 50 B is shown in FIG. 3B (labeled ΔT R ).

The BPTT measurement processes PTTs measured with the finger clip sensors from the patient's left finger (ΔT L ) and right finger (ΔT R ) to make an accurate measurement of blood pressure. Specifically, PTT depends on several factors, including blood pressure, distance between the heart and the portion of the body where the optical waveform is measured (e.g., the patient's finger), and properties of the patient's vasculature (e.g., arterial compliance, size, and stiffness).

BPTT as described herein can potentially improve the accuracy of a normal PTT measurement. For example, as shown in FIG. 2 , a patient's heart 48 is typically located in a relatively well-defined position on the left-hand side of their chest cavity. With each heartbeat, blood simultaneously flows along a right-hand vascular pathlength 44 A to reach a point 42 A on the patient's right hand, and along a left-hand vascular pathlength 44 B to reach a point 42 B on the patient's left hand. The right-hand vascular pathlength 44 A typically differs from the left-hand vascular pathlength 44 B. The difference in pathlengths can correlate with the patient's biometric parameters (e.g., height, arm span). The difference in pathlengths and corresponding difference in PTTs can be used in the calculation of the patient's vital signs (e.g., blood pressure), as is described in more detail below.

Following a heartbeat, electrical impulses travel essentially instantaneously from the patient's heart to electrodes within each sensor enclosure (e.g., the left 14 A and right 14 B sensor enclosures in FIG. 1 ), which detect it to generate an electrical waveform. At a later time, a pressure wave induced by the same heartbeat simultaneously propagates through the patient's right-hand 44 A and left-hand 44 B vascular pathlengths. At points 42 A, 42 B on the patient's left and right hands, elastic arteries within these vascular pathlengths increase in volume due to the pressure wave. Ultimately the pressure wave arrives at a portion of the artery underneath the LED and photodetector within each sensor enclosure. These optics combine to form an optical system that detects the pressure wave by measuring a time-dependent change in optical absorption. The propagation time of the electrical impulse is independent of blood pressure, whereas the propagation time of the pressure wave depends strongly on pressure, as well as properties of the patient's arteries.

Referring again to FIGS. 3A , 3 B, and 3 C, during a BPTT measurement, optical sensors within the right and left sensor enclosures simultaneously measure optical waveforms 52 A, 52 B, while electrodes in the sensors measure electrical waveforms 50 A, 50 B. The optical waveforms 52 A, 52 B are unique to each area enclosed by the sensor enclosure, while the electrical waveforms 50 A, 50 B are identical, and are determined by combining electrical signals from the left and right-hand sensor enclosures. A microprocessor within the device runs an algorithm that analyzes the time difference ΔT L,R between the arrivals of these signals, i.e. the relative occurrence of the optical 52 A, 52 B and electrical 50 A, 50 B waveforms for both the right-hand 44 A and left-hand 44 B vascular system. The microprocessor additionally analyzes the time difference ΔT O between the arrival of the two optical signals 52 A, 52 B.

In a BPTT measurement, the asymmetric position of the heart, coupled with the assumption that blood pressure is equivalent along the left-hand 44 B and right-hand 44 A vascular pathlengths, means the PTT for the right-hand pathlength 44 A will typically be slightly longer than the PTT for the left-hand pathlength 44 B. This time difference, ΔPTT, is the difference between ΔT L and ΔT R (i.e. ΔPTT=ΔT R −ΔT L ) and can be used to estimate the patient's arm length if a speed of the propagating pressure pulse, called a pulse wave velocity (‘PWV’) is assumed. Inclusion of arm length in a PTT-based measurement typically improves accuracy for both systolic and diastolic blood pressure. Use of BPTT to determine ΔPTT means arm length can be estimated without having to enter it through a software user interface. Alternatively, the arm length can be entered into a user interface associated with the monitor, and then processed along with ΔPTT to calculate a PWV. This is done by using the above-described assumptions describing the asymmetrical position of the heart. Blood pressure is known to depend strongly on PWV (typically an increase in PWV indicates an increase in blood pressure), and thus a measured PWV value can be compared to a look-up table stored in memory to calculate blood pressure. Alternatively, a mathematical algorithm, such as a predetermined relationship (e.g., a linear relationship) between PWV and blood pressure, may be used to calculate subsequent blood pressure values.

Referring to FIG. 3C , in another embodiment the time difference ΔT O between points (e.g., peaks) on two optical signals measured from the patient's left and right hands can be processed to determine a PWV. For example, ΔT O can be correlated to PWV and blood pressure using a predetermined relationship (e.g. a linear relationship) before making a measurement, and this correlation can be stored in a look-up table in memory on the device. The device may use an algorithm to convert ΔT O to blood pressure for subsequent measurements.

In addition, with the BPTT measurement, optical waveforms measured from the patient's left and right hands or ΔPTT can be compared to determine slight differences in waveform shape. These slight differences can then be processed to achieve a more accurate calculation of the patient's blood pressure. For example, the differences in left and right waveform shapes or arrival times measured as described above can be used to determine a particular mathematical model for calculating blood pressure from a patient, or alternatively properties other than blood pressure. An abnormally high or negative ΔPTT, for example, may indicate a profound difference between a patient's right-hand 44 A and left-hand 44 B vascular pathlength. Such a difference, for example, may indicate the presence of an occlusion (e.g., a blood clot) or stenosis in either vascular pathlength. In related embodiments, the ΔPTT or waveform shape differences may be used to estimate a patient's arterial compliance.

For example, the differences in the patient's right-hand 44 A and left-hand 44 B vascular pathlengths will result in corresponding differences in the diffusion of light-absorbing blood cells in the two pathlengths. These differences in cellular diffusion are observed as differences in the shapes of the optical waveforms 52 A and 52 B. The waveform shape differences will depend on the arterial compliance along the right-hand 44 A and left-hand 44 B vascular pathlengths. For example, the optical signals 52 A, 52 B shown in FIGS. 3A , 3 B, 3 C typically feature a main peak and a secondary peak, where the secondary peak is typically classified as a ‘dichrotic notch’. Studies published in the literature describe how the dichrotic notch, particularly when analyzed by taking a second derivative of the plethysmogram, relates to vascular compliance (see, e.g., ‘Assessment of Vasoactive Agents and Vascular Aging by the Second Derivative of Photoplethysmogram Waveform’, Takazawa et. al, Hypertension 32: 365-370, 1998; the contents of which are incorporated herein by reference). Arterial compliance determined using this or another method can then be used to group patients having similar arterial properties. An algorithm can then process ΔPTT or PWV values for patients in a particular group, or compare these values to predetermined look-up tables, to make a blood pressure measurement. For example, the algorithm may use a predetermined relationship (e.g. a linear relationship) between PWV or ΔPTT and blood pressure to calculate subsequent blood pressure values.

Referring again to FIGS. 3A , 3 B, and 3 C, in yet another embodiment, processing the electrical waveform 50 A, 50 B and optical waveforms 52 A, 52 B can be used to estimate a property called pre-ejection period (‘ΔT PEP ’), which is the time delay between the beginning of a patient's heart beat and the beginning of the patient's cardiac stroke. Specifically, both ΔT R and ΔT L depend on ΔT PEP and the time it takes the pressure pulse to leave the heart and arrive at the optical system underneath a corresponding sensor. As shown in FIG. 3C , this time difference, referred to as ΔT O , can be measured directly from sensors located near the patient's heart and finger. If the sensor is located on the patient's right hand, ΔT R −ΔT O =ΔT PEP , while if the sensor is located on the patient's left hand ΔT L −ΔT O =ΔT PEP . ΔT PEP correlates with the patient's systolic function, with a shorter ΔT PEP typically indicating a relatively healthy systolic function. A measured ΔT PEP can be used in conjunction with the time difference between a feature on the electrical waveform and one or more features on one or more optical waveforms to improve the accuracy of the calculated PTT and corresponding blood pressure. In particular, it has been shown in previous studies that systolic blood pressure can correlate better to a ΔPTT value, whereas diastolic blood pressure and mean arterial blood pressure can correlate better to a ΔPTT value corrected for ΔT PEP , i.e. ΔPTT-ΔT PEP (see, e.g., ‘Pulse transit time measured from the ECG: an unreliable marker of beat-to-beat blood pressure’, Payne et. al, J. Appl. Physiol 100: 136-141, 2006; the contents of which are incorporated herein by reference). ΔT PEP values may also vary with respiration and inspiration, thereby affecting the measured blood pressure. For this reason, in embodiments, computer code operating in the monitor described above can first process two optical waveforms to estimate ΔT PEP . Once this is done, the computer code can determine ΔPTT and ΔPTT−ΔT PEP , which are then used to calculate, respectively, systolic and diastolic blood pressure.

Referring to FIG. 4 , to transfer information to Internet-accessible devices, the device 10 includes a mini USB port 22 that connects to a personal computer 92 through a conventional USB connector terminating a first cable 94 . Alternatively, the device 10 connects to an external radio 90 through a 2-way radio connection. The external radio 90 , for example, could be within the personal computer 92 or another device, such as a scale, chest strap, or additional monitor.

FIG. 5 shows a preferred embodiment of an Internet-based system 152 that operates in concert with the device 10 and to send information from a patient 130 to an in-hospital information system 171 (e.g., a system for electronic medical records). During operation, the device 10 collects vital sign information from the patient 130 and, using an internal radio as described above, transmits information through a wireless interface 186 to a wireless network 154 (e.g., either a nation-wide or local wireless network), and from there to a web site 166 hosted on an Internet-based host computer system 133 . A secondary computer system 169 accesses the website 166 through the Internet 167 . A wireless gateway 155 connects to the host computer system 133 and ultimately to the wireless network 154 , and receives data from one or more monitors, as discussed below. The host computer system 133 includes a database 163 and a data-processing component 168 for, respectively, storing and analyzing data sent from the monitor. The host computer system 133 , for example, may include multiple computers, software systems, and other signal-processing and switching equipment, such as routers and digital signal processors. The wireless gateway 155 preferably connects to the wireless network 154 using a TCP/IP-based connection, or with a dedicated, digital leased line (e.g., a VPN, frame-relay circuit or digital line running an X.25 or other protocols). The host computer system 133 also hosts the web site 166 using conventional computer hardware (e.g. computer servers for both a database and the web site) and software (e.g., web server and database software). To connect to the in-hospital information system 171 , the host computer system 133 typically includes a web services interface 170 that sends information using an XML-based web services link to a computer associated with the in-hospital information system 171 . Alternatively, the wireless network 154 may be an in-hospital wireless network (e.g., a network operating Bluetooth™, 802.11a, 802.11b, 802.1g, 802.15.4, or ‘mesh network’ wireless protocols) that connects directly to the in-hospital information system 171 . In this embodiment, a nurse working at a central nursing station can quickly view the vital signs of the patient using a simple computer interface.

To view information remotely, the patient or medical professional can access a user interface hosted on the web site 166 through the Internet 167 from a secondary computer system 169 , such as an Internet-accessible home computer. The system may also include a call center, typically staffed with medical professionals such as doctors, nurses, or nurse practitioners, whom access a care-provider interface hosted on the same website 166 .

The device 10 can optionally be used to determine the patient's location using embedded position-location technology (e.g., GPS, network-assisted GPS, or Bluetooth™, 802.11-based location system). In situations requiring immediate medical assistance, the patient's location, along with relevant vital sign information, can be relayed to emergency response personnel.