CN102065773B - Doppler motion sensor apparatus and method of using same - Google Patents

Abstract

An apparatus for, and method of, sensing characteristics of a vessel and a fluid conveyed therein. In one embodiment, the sensing device for acquiring signals and computing measurements comprises a sensor including one or more transducers for transmitting acoustic energy, receiving acoustic energy, and converting the received acoustic'energy into one or more signals, the one or more transducers facing a side of a vessel, a computing device operating the one or more transducers and processing the one or more signals to obtain measurement values, and a housing enclosing the sensor and the computing device.

Description

The method of Doppler motion sensor device and use Doppler motion sensor device

Cross reference related application

The application required all in the 12/119th of being entitled as of submitting on May 12nd, 2008 " OPTICAL SENSORAPPARATUS AND METHOD OF USING SAME (optical sensor arrangement and use the method for optical sensor arrangement) ", No. 315 U.S. Patent applications, be entitled as " DOPPLER MOTION SENSOR APPARATUS AND METHOD OFUSING SAME (Doppler motion sensor device and use the method for Doppler motion sensor device) " the 12/119th, No. 339 U.S. Patent applications, be entitled as " INTEGRATED HEARTMONITORING DEVICE AND METHOD OF USING SAME (integrated cardiac monitoring equipment and use the method for integrated cardiac monitoring equipment) " the 12/119th, No. 325 U.S. Patent applications, be entitled as " METHOD AND SYSTEM FOR MONITORING A HEALTHCONDITION (for monitoring the method and system of health status) " the 12/119th, the 12/206th of No. 462 U.S. Patent applications and being entitled as of submitting to for 9th JIUYUE in 2008 " DOPPLER MOTIONSENSOR APPARATUS AND METHOD OF SUING SAME (Doppler motion sensor device and use the method for Doppler motion sensor device) ", the priority of No. 885 U.S. Patent applications, all applications are submitted to by identical therewith inventor, and the full content of all applications merges to herein by reference.

Technical field

The present invention relates to sensor device and, more specifically, relate to the sensor device for sense fluid velocity.

Background technology

For medical reasons, need to monitor a period of time to patient's body intrinsic parameter.The arrhythmia of heart is the variation that causes heart normal sequence of the electric pulse of pump blood between health.Because changing, abnormal cardiac pulses may only occur contingently, so can need continuous monitoring to detect arrhythmia.Healthcare givers utilizes the continuous monitoring can characterization heart and set up suitable therapeutic process.

A kind of prior art equipment of measuring the rhythm of the heart is " Reveal " monitor in Medtronic (Medtronic) (U.S., the Minnesota State, Minneapolis city).Whether this equipment comprises implantable cardiac monitor, relevant with cardiac rhythm problem for for example determining patient faint (fainting).Reveal monitor is continuously monitored the speed of heart and the length that the rhythm and pace of moving things reaches 14 months.After waking up from the experience of fainting, patient by reorder equipment be placed on skin outside, above the Reveal monitor of implanting, and touch the button data be sent to recording equipment from monitor.Recording equipment is offered to doctor, thereby doctor has determined whether to be recorded to abnormal cardiac rhythm to the information analysis being stored in recording equipment.The use of recorder neither automatically neither be autonomous and so needs patient is conscious or another person's intervention is sent to recording equipment by information from monitor.

The implantable monitoring equipment of another known type is the equipment of transponder types, wherein by transponder patients with implantation, also with hand-held electromagnetism reader, the mode with non-intrusion type conducts interviews to it subsequently.The 5th, the device examples of a rear type has been described in 833, No. 603 United States Patent (USP)s.

Summary of the invention

Disclose herein for obtaining the sensor device of signal and computation and measurement result.In one embodiment, sensor device comprises the sensor with one or more transducers, and transducer is for sending and receiving acoustic energy and the acoustic energy receiving is converted to one or more signals.One side of sensor cover conductive pipe is positioned.Computing equipment operates sensor and a plurality of signals is processed to obtain measured value.Sensor and computing equipment are enclosed in shell.

Also disclose in this article for obtaining the method for signal and computation and measurement result.An embodiment of method comprises the following steps: provide as disclosed sensor device in above paragraph, from one or more transducers, send acoustic energy, from one or more transducers, receive acoustic energy and obtain one or more signals, one or more signals are processed to obtain measured value, and measured value analysis is obtained to the parameter value that represents fluid behaviour.

In another embodiment, provide for to blood vessel with flow through the equipment that at least one characteristic of the blood of blood vessel is carried out acoustic measurement.This equipment comprises shell, sensor cluster and the computing equipment with the first side and the second side.Sensor cluster is mounted to shell and comprises one or more transducers, and transducer sends acoustic energy for the first side through shell, receives the acoustic energy through the first side of shell, and acoustic energy is converted to signal.Computing equipment is configured to one or more transducers activate and signal carried out to decipher and determine characteristic.Shell surrounds sensor and computing equipment.

In conjunction with the drawings with reference to the following description of embodiments of the invention, feature of the present invention and the mode that realizes them will become and more understand and the present invention self will better understand.

Accompanying drawing explanation

Figure 1A is the schematic side view of the exemplary embodiment of sensor device;

Figure 1B is that the outer surface of the sensor device of Fig. 1 is schemed towards (outwardly-facing);

Fig. 1 C is the perspective view of the sensor device of Fig. 1;

Fig. 2 and Fig. 3 are the schematic side view of sensor device and the blood vessel of Fig. 1;

Fig. 4 is the schematic top view of the exemplary embodiment of doppler sensor;

Fig. 5 is that the Concept Vectors of ripple and fluid flowing positioning represents;

Fig. 6 A-6D is respectively according to the schematic elevational view of the doppler sensor of another exemplary embodiment, side view, top view and perspective view;

Fig. 7 is the schematic top view of another exemplary embodiment of doppler sensor;

Fig. 8 is the concept map that is applicable to the signal of communication of the sensor device from Fig. 1 to carry out the system of sending and receiving;

Fig. 9 is the flow chart of the illustrative methods for motion is measured;

Figure 10 is the schematic diagram of cardiac cycle;

Figure 11 is the concept map that flows through the fluid of blood vessel;

Figure 12 is the curve chart of measuring during cardiac cycle;

Figure 13 is according to the concept map of the doppler sensor of exemplary embodiment;

Run through several figure, the corresponding part that corresponding Reference numeral represents.Although accompanying drawing represents embodiments of the invention, for description and interpretation the present invention better, accompanying drawing is not must be proportional and can amplify some feature.The example that proposed herein with several formal specifications embodiments of the invention and such example will can not be interpreted as by any way scope of the present invention being limited.

The specific embodiment

That embodiment discussed below does not intend limit or the present invention is limited to disclosed precise forms in following detailed description.More properly, embodiment is selected and description so that others skilled in the art can Application Example teaching.

Figure 1A shows the sensor device 1 according to an exemplary embodiment.Sensor device 1 generally includes a plurality of parts, and parts comprise doppler sensor 60, computing equipment 20, communication equipment 30 and energy storage device 40, and each parts is arranged on plate 80 and with computing equipment 20 and carries out electronic communication.Parts are enclosed in shell 90.In one embodiment, energy storage device 40 is applicable to receive the electromagnetic energy wave 44 from exterior source of energy 46.

In one embodiment, sensor device 1 is applied to determine patient's physiological situation." patient " refers to the measured human or animal of the sensed equipment 1 of physiological situation.Although invention disclosed herein is to be described under medical ground, teaching disclosed herein can be applicable to need under other background that small-sized data acquisition component measures along with the time equally.For example, in sensor cluster application in the water that submerges or that be difficult to arrive, under dangerous environment, have in the application of weight and size restrictions, enquiry-based activity is medium at the scene can be desirable.

In one embodiment, sensor device 1 is implanted in patient body by subcutaneous.Yet, should be appreciated that, can use various implanted prosthetics that sensor device 1 is implanted in to different positions.For example, can sensor device 1 be implanted in thoracic cavity, under rib wide (rib cage).Shell 90 can form with the shape of circular discs or oblong-shaped disc, and its size roughly 25 cent coins stacking with two is identical.Certainly, depend on application, shell 90 can be configured to multiple other shape.Shell can comprise four outside outstanding rings 92, shown in Figure 1B and Fig. 1 C, thus for accepting to sew up in patient's body, assembly is fixing hypodermically.The shape that depends on shell 90 can arrange more or less ring 92.When by so fixedly time, doppler sensor 60 quilt covers are upcountry located, and the following energy coupler of describing in detail towards outside.

In another embodiment of sensor device 1, by other functional part (feature) of doppler sensor 60 and sensor device 1, together with implantable cardiac integration of equipments, implantable cardiac equipment such as pacemaker, cardiac resynchronization therapy (CRT) equipment, implanted heart rate turn multiple defibrillator (ICD) etc.In one embodiment, can be by the parts of sensor device and heart equipment be combined to realize integrated.If for example heart equipment comprises computing equipment, the algorithm of manner of execution can be combined with the computing equipment of heart equipment rather than increase by the second computing equipment.In a similar fashion, can by energy accumulator and communication equipment is combined avoid repetition (duplication).In one embodiment, some parts of sensor device are comprised in the enclosure and some parts are attached to heart equipment.Parts in heart equipment and shell are operably connected.

In another embodiment, sensor device 1 is positioned to the outside of patient body.Being provided with supporting member supports sensor device 1 in health outside.Supporting member for good and all or provisionally can be coupled to sensor device 1.In one embodiment, supporting member comprises adhesive layer, for supporting member is adhesively coupled to patient body.In another embodiment, supporting member comprises it can being elastic belt, for the fixing sensor device 1 of the health with respect to patient.

Can sensor device 1 be implanted hypodermically or is positioned on patient by means of outside map (mapping) system of for example Ultrasound Instrument.Suitable placement guarantees that the blood vessel of paying close attention to is positioned at the sensing range of sensor device 1.At the blood vessel of paying close attention to, be in aortal situation, sensor device 1 can be positioned to patient's chest or certain position at back, this position make the measurement that obtains by the mode with described herein, by the caused interference of rib, reduced to some extent.

1. doppler sensor

Doppler sensor comprises one or more transducers, for object being insonated and receiving the ultrasound wave being reflected.By the insonify ripple of ultrasonic energy is guided to fluid, the frequency displacement of the ultrasonic energy being reflected measured, then calculated the speed of fluid with known angle, thereby can determine the speed of paid close attention to fluid.Doppler frequency shift is proportional with the component that is parallel to insonify wave propagation velocity vector.In order to lower equation, determine the speed v of fluid:

v＝f _d·c/(2·f·cos?θ)

Wherein c is the velocity of sound in blood, and f is insonify wave frequency, and θ is the angle between ripple and velocity vector, and f _dit is Doppler frequency shift.Hereinafter with reference to Fig. 9-Figure 12 to come the embodiment of the method for calculating blood pressure to carry out very detailed description based on tachometric survey.

Transducer is the equipment that acoustic energy is converted to the signal of telecommunication and converts electrical signals to acoustic energy.The operational approach that depends on one or more transducers, calculating frequency shift can in all sorts of ways.In a method of operation, doppler sensor can be continuous wave sensor.Continuous wave Doppler sensor comprises for sending hyperacoustic transducer and for receiving hyperacoustic transducer.By comparing two ripples, directly measure frequency displacement in the method.In another method, can use Pulsed-Wave Doppler sensor.Pulsed-Wave Doppler sensor has single transducer, for sending ultrasound wave and for receiving ultrasound wave.After sending ripple, doppler sensor switches to reception operator scheme from transmit operation pattern.By the phase shift between the ripple receiving subsequently, compare to measure frequency displacement.By a plurality of ripples of sending and receiving successively, be that to calculate phase shift necessary.Can obtain the phase shift between the pulse of reception and the pulse of transmission with the known algorithm of for example jam (Kasai) algorithm or cross correlation algorithm.

Transducer can comprise coil, piezoelectric and other applicable transducer.Transducer can be focused on to send narrow ripple or the acoustic energy beam of acoustic energy.Transducer can also send the wide ripple of acoustic energy or the not focus wave of acoustic energy.The energy that two or more transducer group synthesizing linear arrays can be sent to the enough ideal quantity of energy makes to be subject to the sound wave of acoustic wave action on a large scale.Greatly how larger than the scope of acoustic wave action that can be subject to single transducer.They linear array can be coupled together so that can be driven as being comprised of single transducer.Linear array can also be coupled together so that each transducer section operates as transducer independently.

Fig. 2 illustrates having blood vessel 3 that the blood 4 of the hemoglobin in erythrocyte 5 carries and the relation between doppler sensor 60.Doppler sensor 60 has transducer 61, and transducer 61 positions towards the fluid 4 of being carried by blood vessel 3.The ripple 62 being sent by transducer 61 is shown as along by propagating perpendicular to the indicated direction of the surperficial centrage 63 of transducer 61.Arrow 6 indicates the direction of fluid mobile in blood vessel 34.Although described in this article doppler sensor 60, the function of doppler sensor in sensing component 1 described, but other doppler sensor described herein carry out identical function and, conventionally, the doppler sensor 60 of quoting in the application and related application is equally applicable to other doppler sensor described herein.

In one embodiment, for example the driving arrangement of pulse generator provides the output corresponding with the frequency of wanting to obtain.Output can be amplified by for example transistorized amplifier, integrated or the outside at computing equipment 20 is provided with computing equipment 20.Output can comprise waveform.Computing equipment 20 can provide frequency systematic function.In an alternative embodiment, the acoustic energy that provides the voltage corresponding with the supersonic frequency of wanting to obtain and transducer to convert electrical energy into ultrasound wave form to transducer by driving arrangement.

In one embodiment, sensor device 1 has COM1, for be connected with miscellaneous equipment or with miscellaneous equipment exchange message.Show adapter 85.Below with reference to Fig. 8, to being connected to the operation of adapter 85 of other parts of sensor device 1, further doing in further detail and describe.

Fig. 3 illustrates the ultrasound wave 64 being reflected.Ripple 64 is shown as along being propagated by the indicated direction of centrage 63.Ripple 64 is propagated in the contrary direction in the direction of propagation with ripple 62.Ripple 64 also has the frequency different from the frequency of ripple 62.By the selection to transducer, determine difference.In one embodiment, ripple 62 are continuous wave and ripples 64 with 62 same times of ripple be reflected.In another embodiment, ripple 62 is to arrive at echo 64 impulse wave being sent by transducer A before transducer A.Computing equipment 20 can guide transducer A to send ripple 62 and ripple 64 is arrived to the needed times of transmitter A and measure.Ripple is propagated by soft tissue with known constant speed.Can calculate the distance along centrage 63 from transducer A to blood vessel 3 from the propagation time between the transmission of ripple 62 and the reception of ripple 64.

Fig. 4 illustrates the doppler sensor 70 that comprises linear array transducer A, B and C.Doppler sensor 70 can couple with other parts of sensor device 1 or be integrated.Transducer A, B are operationally connected with driving arrangement (not shown) with each in C, thus driving arrangement give each transducer be provided with power cause each transducer send can propagate certain distance to the fluid of paying close attention to and when the arrival fluid ultrasound wave of reflection phase shift ripple.Can to the source of the echo being received by doppler sensor 70, distinguish with different frequency drives transducer A, B and each in C.For convenience's sake, each transducer in linear array is called as transducer section (segment) in this article.In the illustrated embodiment, each linear array transducer comprises five transducer sections.Transducer section can be operably connected and be activated respectively or side by side.Separately activating of one or more transducer sections is the desirable limiting power consumption that comes.Can activate more than one transducer section simultaneously and expand the impact that each sends ripple.Certainly, if activated all sections in linear array, linear array operates as single transducer.Doppler sensor 70 can comprise three such transducers.

Transducer A, B and C are relative to each other arranged certain angle.In an embodiment shown in Figure 4, transducer B and C are arranged to respect to the angle of transducer A 45 degree 90 degree relative to each other.Transducer can with respect to other transducer different angles arrange.Position and angle are selected acoustic energy to be oriented in and from blood vessel, acoustic energy to be carried out the direction of optimum reflection.Concrete analysis based on to patient is selected at least in part.To patient's concrete analysis, can determine where sensor device 1 is positioned at, for example externally or implant ground, be positioned at above or below, and the distance from doppler sensor to the blood vessel of paying close attention to will be determined in the position of sensor device 1.In one embodiment, transducer B and C are arranged to respect to the angle of transducer A 30 degree 120 degree relative to each other.

The transducer A section of comprising A1-A5, the transducer B section of comprising B1-B5, and the transducer C section of comprising C1-C5.Each section can carry out sending and receiving to the ultrasonic energy of waveshape.The arrow of locating to start and stretch out perpendicular to section at each section represents the wave line of propagation being sent by each section.In addition, arrow 72,74 and 76 represents respectively the total direction of the ripple that produced by transducer A, B and C.According to the distance between transducer and target fluid, select the frequency of acoustic energy.Conventionally after passing through patient's soft tissue, the frequency place excitation transducer between 2-10MHz arrives the blood vessel of the common pumping blood in 3-20cm distance.In one embodiment, each in the excitation of the frequency place between 2-10MHz transducer A, B and C.In another embodiment, at 5Mhz frequency place, one or more sections of transducer A are encouraged, at 4.5Mhz frequency place, one or more sections of transducer B are encouraged, and at 5.5Mhz frequency place, one or more sections of transducer C are encouraged.Can measure echo at each section place of linear array transducer.Each section can sequentially be encouraged and can be energized repeatedly.In other embodiments, can be with more than five sections or be less than five sections and form transducer unit.In one embodiment, use ten to 15 sections.

Doppler frequency shift or frequency displacement and to be parallel to the component of velocity vector of percussion wave proportional.Because Doppler frequency shift depends on the cosine of the angle θ between ripple and velocity vector, and the scope of cosine function is between 0 to 1, so the signal being produced by the ripple with velocity vector parallel orientation produces optimum signal.In one embodiment, computing equipment 20 is only from angle θ=θ ₁the ripple that is less than or equal to 20 degree produces signal.Fig. 5 illustrate conceptually velocity vector 6 and previously in Fig. 4, presented, there is the relation between direction 72,74 and 76 ripple.Fig. 5 also illustrates with respect to velocity vector 6 angle θ ₁four arrows arranging.Arrow 74 is shown as with respect to velocity vector 6 and forms and compare θ ₁little angle.Therefore, be oriented in by the ripple in the represented direction of arrow 74, be that the ripple being produced by linear array transducer B can generate available signal in the case.Relatively, be oriented in by arrow 72 and 76 represented directions, corresponding to the ripple of transducer A and C, will not produce available signal.

In one embodiment, sensor device 1 comprises and is configured to optical sensor module that the position of blood vessel and diameter are detected.Sensor device 1 can determine which transducer will not produce available signal in the position based on blood vessel, and will only from producing the transducer of available signal, send ultrasound wave in order to save energy.

In order to increase the scope of doppler sensor, can be set to arrange with different angles by other transducer, so that can be with the one or more transducers of certain angle orientation, this angle produces and is oriented in the ripple that is less than or equal to the angle place of 20 degree with respect to velocity vector.In one embodiment, even arrange to make the relative position of working as doppler sensor 70 and blood vessel 3 along with time or other factors with the shape of K three transducers, for example patient's level of activation and posture, and doppler sensor 70 also can obtain the signal of sufficient amount when slight modification.The echo being produced by a transducer can be received by more than one transducer.Yet, because ripple has with each, send the frequency that transducer is corresponding, thus the relative position that doppler sensor 70 can be based on corresponding transmission transducer and transmission frequency thereof optionally trap signal so that Doppler frequency shift can suitably be identified.Frequency displacement is corresponding to speed and flow direction.

In one embodiment, in the time of on the blood vessel when ripple impinges upon the blood vessel except paying close attention to, the signal of the ripple that the section of next free linear array transducer A, B and C receives is filtered.Mode that can be identical with the mode of acquisition station-keeping data obtains the position of the blood vessel the blood vessel except paying close attention to, and below will make an explanation to which.In another embodiment, first computing equipment 20 is each section of definite angle θ, only has when the angle θ of section can generate available signal and just optionally encourages the section of transducer A, B and C, saves thus energy.In addition,, if all sections of transducer can produce available signal, computing equipment 20 can limit to save energy to the number of signals producing.For example, if all five sections are positioned to produce available signal, computing equipment 20 can select three signals to save five necessary energy of signal of generation of 40%.

When a plurality of transducers that comprise coil are extremely closely located, each transducer can disturb the operation of other transducer.Can offset (neutralized) by suitable filter algorithm disturbs.Yet, filter by this way and need other memorizer and energy to carry out Processing Algorithm.Fig. 6 A-6D illustrates the doppler sensor 170 that is configured to make the minimum interference between transducer.Doppler sensor 170 comprises the transducer 171,172 and 173 respectively with coil 176,177 and 178.Fig. 6 A, 6B, 6C and 6D are respectively front view, side view, top view and the perspective views of doppler sensor 171.Transducer 171,172 and 173 is used and is configured to the material of counterchecking electromagnetic wave and uses and be configured to allow the material that electromagnetic wave passes to surround coil 176,177 and 178 on the 4th face represented by symbol Y on three sides represented by symbol X.Side Y is called as electromagnetism window herein.Barrier material can be any applicable material that comprises metal, and non-barrier material can be any applicable material of plastics for example.Barrier material has physically been eliminated the interference between coil 176,177 and 178, saves thus energy and makes the further miniaturization of sensor device 1 by reducing memory requirements.Transducer 171,172 and 173 is stacking rather than is placed in common plane.For compensating the stacking computation requirement producing, for example to geometric distance, calculate and introduce third dimension degree, consume insignificant resource.In many cases, due to stacking insignificant impact, stacking impact can be ignored completely.

Fig. 7 illustrates the doppler sensor according to another exemplary embodiment.Doppler sensor 270 comprises it can being the transducer 271-279 of single transducer or linear array transducer.By transducer 271-279, with the shape localization of three K, in the situation that do not increase the profile (profile) of sensor device 1, also thereby less than introduce stacking variable in calculating provide sensing range widely.Can adapt to more or less transducer the shape of shell and the position that sensor device 1 is placed.In the illustrated embodiment, transducer 271,274 and 277 comprises the bottom of three K shape arrays.Transducer 271 and 277 is arranged with the angle of 30 degree with respect to transducer 274 and each in transducer 271 and 277 is arranged with the angle of 45 degree with respect to remaining two lower limbs of each K type array.

As discussed previously, calculate blood flow velocity and need to know the incident angle θ between ripple and blood vessel 3.Can obtain in every way angle of incidence and other data that relative position of blood vessel 3 and doppler sensor is characterized.Once obtain angle of incidence and other data, can be stored in memorizer as reference value.In one embodiment, can by communication equipment 30, station-keeping data be provided to computing equipment 20 by external equipment.External equipment can wirelessly send the signal of communication that comprises station-keeping data to communication equipment 30.In another embodiment, can by communication equipment 30, station-keeping data be provided to computing equipment 20 by another implanted equipment.Other implanted equipment includes but not limited to that pacemaker, cardiac resynchronization therapy (CRT) equipment, implanted heart rate turn multiple defibrillator (ICD) etc.In yet another embodiment, can to computing equipment 20, provide station-keeping data by another sensor or the sensor cluster that are included in sensor device 1.In " optical pickocff application " cited above, provide the sensor cluster for detection of the relative position of blood vessel.Once determined selected signal, thereby computing equipment 20 calculate blood flow velocity value by relatively sending wave frequency and receive wave frequency according to known frequency displacement and angle algorithm or form.

In another embodiment of sensor device 1, by other functional part (feature) of doppler sensor and sensor device 1, together with implantable cardiac integration of equipments, implantable cardiac equipment such as pacemaker, cardiac resynchronization therapy (CRT) equipment, implanted heart rate turn multiple defibrillator (ICD) etc.

Thereby carry out relatively occasionally blood flow velocity and measure saving power (for example once a day or twice) although can programme to sensor device 1, but should be appreciated that, along with the improvement of battery technology, power save will be no longer a problem, can measure more continually.In addition, when sensor device 1 is not implanted (being worn by patient outside), can, by adapter 85 to sensor device 1 power supply, eliminate thus the needs of saving power and allow frequent even continuous measurement.

2. computing equipment

Computing equipment 20 comprises a plurality of parts.Although parts described herein are individual components as them, can be by unit construction precedent as the single equipment of special IC.Computing equipment 20 comprises processor, memorizer, one or more program, input equipment and outut device.Memorizer can include but not limited to RAM (random access memory), ROM (read only memory), EEPROM (EEPROM), flash (flash memory) memorizer or other memory technology.Can be by processor and memory construction in integrated circuit.This integrated circuit can comprise one or more doppler sensors 60,70,170 and 270 and communication equipment 30.In addition, computing equipment 20 can comprise A/D converter and/or D/A converter on integrated circuit.Alternatively, A/D converter and/or D/A converter can be set respectively.

Program representation guidance of faulf handling device is carried out the computer instruction in response to the task of data.Program is present in memorizer.The data that comprise reference data and measurement data are also present in memorizer.Can be with reference to data-storing in ROM, or can be stored in that in RAM, make can be along with the time be in response to outside input or modify in response to the characteristic of the measurement data gathering along with the time.The agreement that measured value is responded can also be set.Agreement can be stored in permanent memory or can be stored in the volatile memory of RAM for example.

Computing equipment 20 by input equipment and outut device to doppler sensor 60,70,170 and 270 and communication equipment 30 control.Computing equipment 20 can be controlled the measurement result of using minimum energy to obtain expectation to number, frequency, power stage and the transmission of the ripple of doppler sensor 60,70,170 and 270.

Fig. 8 discloses for the system 300 with sensor device 1 exchange message.System 300 comprises the sensor device 1 (shown in Figure 1A) alternatively with adapter 85.System 300 can also comprise computer 302, via cable 303, operationally be coupled to Docking station (dockingstation) 304 and the phone 306 of computer 302.In one embodiment, system 300 is based on wirelessly sending signal of communication and from sensor device 1 receiving communication signal wirelessly by the performed processing of computing equipment 20 to sensor device 1.

Adapter 85 is applicable to be inserted in Docking station 304.Sensor device 1 is illustrated docking (dock) on Docking station 304.During being docked, sensor device 1 can be to energy storage device 40 chargings.Docking station 304 is coupled to computer 302 to be alternatively placed on patient with it by sensor device 1 or before in patient body, the program and the reference value that are stored in the memorizer of computing equipment 20 to be upgraded.In another embodiment, sensor device 2 can be positioned over to patient outside, thereby and adapter 85 be operationally coupled to energy source sensor device 2 is provided with power and prevents exhausting of energy storage device 40.

In yet another embodiment, can be by adapter 85 by other sensor and devices, coupled to sensor device 1.Other sensor and equipment can include but not limited to other sensor cluster 2, temperature sensor, pressure transducer and accelerometer.Other equipment can comprise or can not comprise computing equipment.Other equipment can also be combined in shell 90 with sensor device 1.In relevant " integrated heart application " cited above, integrated sensor device is disclosed.By downloading in the memorizer of computing equipment 20 being applicable to operate program other sensor and equipment, that revised, the operation of sensor device 1 goes for other sensor and operate.Download can occur in when computing equipment 20 is docked to Docking station.Alternatively, new procedures wirelessly can be downloaded by computing equipment 40.

Fig. 9 is illustrated in computing equipment 20 to be activated and also to carry out the flow chart of the program of the function that measured value is responded for Measure blood pressure parameter.At step 400 place, computing equipment 20 obtains the transducer signal that represents fluid velocity from doppler sensor.In one embodiment, transducer signal comprises voltage and frequency.Should be appreciated that, rate signal comes from the ripple being produced by reflective object.In the situation of blood flow velocity, to liking erythrocyte.What conventionally understand is that erythrocytic speed in blood has represented blood flow velocity exactly.

Can limit based on cardiac cycle data setting up procedure 400 blood flow velocity at the particular point place in cardiac cycle.Can also carry out setting up procedure 400 in response to the external command receiving by communication equipment 30 or because sensor device 1 detects unusual condition.Each in A, B and C in transducer is sequentially encouraged.In one embodiment, transducer A sends ripple, is then switched to receiving mode.Doppler sensor 70 is with the determined mode detection of reflected of the configuration by transducer A ripple.Activate successively in an identical manner transducer B and C.In another embodiment, each transducer comprises transmitting element and receiving element and thereby this transducer can be activated sending and receiving acoustic energy simultaneously.Transducer label or excitation are sequentially unessential.Can utilize more or less transducer.The quantity of selection transducer and orientation are come obtaining data with respect to blood vessel 3 certain angle places, and this angle is that the object of expection produces enough data.

At step 402 place, 20 pairs of signals of computing equipment process to obtain measured value.Processing can relate to and removes intrinsic signal noise, is digital form, calibration, the non-selected ripple of filtering or detection signal is regulated to convert them to measured value by signal from analog formal transformation.In one embodiment, the measurement result obtaining is averaging to obtain average blood velocity in a cardiac cycle.In another embodiment, the high value measurement result obtaining and low value measurements are averaging to obtain average blood velocity in a cardiac cycle.Can use electrocardiogram (ECG) to estimate when blood flows with maximum or minimum speed.After processing, measured value can be stored in memorizer or can analyze and first determine whether retain this value it.According to the teaching that provided herein, repeating step 400 and 402, obtains enough measured values as required, thus the parameter of calculation expectation.Referring to Figure 12 to come the embodiment of the method for calculating blood pressure to describe in detail very much based on tachometric survey.

For save energy, just it is desirable to only when quite certainly will obtaining applicable signal, operate doppler sensor 70.In one embodiment, before being activated, doppler sensor 70 can to the blood vessel of paying close attention to, with respect to the angle of each transducer, find out with low-power consumption sensor.In one embodiment, sensor device 1 has comprised infrared sensor package 2 described in detail in the application of " optical pickocff " cited above.2 pairs of sensor devices 1 of sensor cluster are positioned, and so that the ripple sending from the transducer of doppler sensor is to be approximately equal to or to be less than, the angle of 20 degree and the velocity vector of blood are crossing finds out.To not encouraged by the transducer of appropriate location.

At step 404 place, 20 pairs of measured values of computing equipment are analyzed.Analysis can comprise calculating and/or the diagnosis of the supplemental characteristic based on measured value.Supplemental characteristic refers to the value of calculation such as fluid velocity, cardiac output, cardiac rhythm etc.Diagnosis refers to the unusual condition that parameter value and reference value is compared to detect patient.Reference value is normal value or the desired value of the measurement parameter of particular patient.If unusual condition detected, computing equipment 20 can transmit alarm rather than when collecting measured value, transmit measured value (consuming unnecessary power) or wait until memorizer is full or just send measured value (patient being exposed to unnecessary danger at waiting time) when reaching the predetermined transmission time.

Can perform step 400,402 and 404 simultaneously.The described above apparatus and method that speed is calculated are useful when calculating the speed of blood and other fluid.Speed calculation in the situation that continuous fluid is mobile does not need further to calculate.But, if fluid flow be the cycle rather than continuous, other measurements and calculations are that desired coming more fully diagnosed unusual condition by flow behavior and based on flow behavior.

Reference value can comprise desired value and acceptable excursion or restriction.Reference value can also comprise by communication equipment 30, from other sensor, obtain or from miscellaneous equipment measured value that obtain, that include but not limited to relative position value.

When parameter value exceeds reference target value or scope, parameter value indication is abnormal.In certain embodiments, parameter value can produce the statistic as moving average for example, and when parameter statistic and reference statistical amount differ over anticipated number, detects abnormal.If supplemental characteristic and desired value differ a predetermined level is exceeded, computing equipment 20 can tested to supplemental characteristic to starting before extremely making diagnosis new measuring period so.

A kind of abnormal medical condition is heart arrhythmias.Computing equipment 20 can be configured to carry out the analysis of measured value is determined to for example whether thereby cardiac rhythm is the irregular arrhythmia that indicated.

Use the outside value obtaining or can other abnormal medical condition be detected from the value of other sensor.In the related application of " optical pickocff application " cited above, " integrated heart application " and " health status application ", the other sensor that can be included in sensor device 1 is disclosed.

At step 406 place, if unusual condition detected, agreement according to the rules determines that situation is serious situation or dangerous situation especially, and computing equipment 20 sends alarms.Alarm can be used for starting siren or warn patient to adopt remedial measures.Remedial measure can be to stop or minimizing physical exertion.Alarm can also provide global location (GPS) information to emergency service.With reference to Fig. 6, when the existence of the situation of noting abnormalities, can also be presented on computer 36 and/or via communication equipment 30 and be sent it to caregiver.Alarm can comprise text message or the code corresponding with situation.Computing equipment 20 can also start new measuring period and in response to the unusual condition detecting, measure continuously.

At step 408 place, computing equipment 20 can start treatment.Sensor device 1 can receive external command by communication equipment 30 and carry out treatment in response to alarm.Alternatively, based on agreement, thereby also can to being applicable to provide the equipment for the treatment of to instruct, propose this treatment with unusual condition.Treatment can comprise for example shocks by electricity or medicine is provided.

At step 410 place, parameter value or other information are passed to external equipment.Can side by side perform step 410 together with above any step.Parameter value can be stored in memorizer and use communication equipment 30 wireless transmissions.Signal of communication from communication equipment 30 can be activated periodically under following situation, situation comprises: in response to unusual condition, the order receiving in response to outside, as long as long as memorizer uses and surpasses predetermined quantity or when determining that energy storage levels is low, set up that latter two situation prevents because memorizer overflows or energy loss and the loss of data that causes.Be also to be understood that sensor device 1 can also comprise communication equipment except communication equipment 30.For example, when communication equipment 30 is situations of cellular modem, sensor device 1 can also comprise standby Bluetooth communication equipment or radio frequency communication devices.Such stand-by equipment (such as due to low, the bad network coverage of available horsepower etc.) in the situation that cellular modem obviously can not send information after many times attempting may be desirable.Under these circumstances, computing equipment 20 can activate standby communication equipment and send information or alarm to interchangeable outside receiving equipment.

Once unusual condition for example detected, just perform step 410 to substantially upgrade to caregiver in real time.Step 410 is carried out at regular intervals, for example once a day, weekly, one month one inferior.Alternatively or except these transmission, thereby can programme by the information that makes communication equipment 30 send requested data or represent requested data to by the received request of data (for example, from medical personnel) is responded of communication equipment 30 to computing equipment 20.

Signal of communication can be received to warn patient to have situation by near equipment patient, or by medical personnel, relative or other predetermined recipient, remotely (for example passes through network) and receive.

Blood flow velocity on time point depend on this time point and patient cardiac cycle where locate corresponding.Cardiac cycle has electricity part and mobile part.Electricity part refers to the electric wave that causes cardiac muscle pump blood.This ripple is through health and can be with comprising that the probe with the electrode of Body contact measures it.Electrocardiogram is to measure the particularly good method of abnormal rhythm of cardiac rhythm.Yet electrocardiogram is not the reliable means of measuring cardiac pumping ability.

Figure 10 illustrates the electrocardiogram curve chart 500 electrical activity, that show two cardiac cycles of heart.Typical electrocardiogram is by P ripple, QRS complex wave (complex) and T wave component.Equipotential line 502 is opened T ripple and P wavelength-division below.From the starting point of P ripple, to the starting point of QRS complex wave, PR interval 504 is measured.Its common length is 120 milliseconds～200 milliseconds.About 60 milliseconds～100 milliseconds of QRS composite wavelength.ST section couples together QRS complex wave and T ripple.Typical ST section approximately continues 80 milliseconds.In one embodiment, sensor device 1 comprises electrocardiography transducer and for detection of the algorithm of T ripple, QRS complex wave and P ripple.

Can obtain in every way cardiac cycle.In one embodiment, can by communication equipment 30, cardiac cycle be provided to computing equipment 20 by external equipment.External equipment can wirelessly send the signal of communication that includes cardiac cycle data to communication equipment 30.In another embodiment, can by communication equipment 30, cardiac cycle data be provided to computing equipment 20 by another implanted equipment.Other implanted equipment includes but not limited to that pacemaker, cardiac resynchronization therapy (CRT) equipment, implanted heart rate turn multiple defibrillator (ICD) etc.

In one embodiment, can to computing equipment 20, provide cardiac cycle data by another sensor or the sensor cluster that are included in sensor device 1.Sensor cluster for detection of cardiac cycle is provided in the application of " optical pickocff " cited above.In yet another embodiment, can to computing equipment 20, provide cardiac cycle data by electrocardiography transducer.In the relevant application of " integrated heart " cited above, provide the sensor cluster that comprises electrocardiography transducer.

Referring now to Figure 11-12, describe blood flow and blood flow is characterized the embodiment of the method for calculating blood pressure.Narrating as previous, blood flow velocity changes according to cardiac cycle with flowing.Can will in the short time, carry out in succession ground tachometric survey for characterizing heart contraction blood pressure and diastole blood pressure.Heart contraction arterial pressure is the surge pressure in tremulous pulse, and it occurs near the starting point of cardiac cycle.Diastole arterial pressure is minimum pressure (quiescent phase (resting phase) at cardiac cycle is located).The time of systolic pressure and diastole pressure of can estimating is estimated maximum blood flow velocity and minimum blood flow velocity.

In an embodiment of the method for calculating blood pressure, sensor device 1 obtains a plurality of velocity measurement being estimated as the moment corresponding with systolic pressure, and presses the corresponding moment to obtain other a plurality of velocity measurement being estimated as with diastole.The inner surface area of the large artery trunks 3 that computing equipment 20 use calculate for each measurement result (for example, by being determined by the diameter measurement of 2 facilitations of optical sensor module) and measure between time of consumption and application for Bernoulli Jacob (Bernoulli) equation of the simplification of incompressible fluid: PT=PS+PD is converted to pressure measxurement by tachometric survey, in Bernoulli equation, PT is gross pressure, and PS is that static pressure and PD are any dynamic pressures in stream (flowstream).

Referring now to Figure 11, the moment=T1 place dynamic pressure PD1 and diameter d 1 corresponding to the tachometric survey from carrying out under maximum blood flow state in determined pressure.At the moment=T2 place, PD2 is T2 diameter constantly corresponding to determined pressure and d2 in the tachometric survey from carrying out under minimum blood flow state.In the situation of large artery trunks 3, the static pressure under maximum fluidity situation (PS1) (being depicted as the power arrow of the outer wall of outside sensing large artery trunks 3) directly corresponding to heart contraction blood pressure measurement and the static pressure under minimal flow situation (PS2) directly corresponding to diastole blood pressure measurement.These calculate the uniform velocity section on hypothesis laminar flow (laminar flow) and blood vessel.Can use from aiming at the signal that angiocentric ripple obtains and obtain flow velocity sampling, and under these hypothesis, can sample with flow velocity, according to remove the speed time integral of dividing Doppler curve with the cycle of flowing, calculate average speed.

Heart contraction blood pressure measurement and diastole blood pressure measurement are derived in the further calculating that can cross the gross pressure (PT) of the blood of large artery trunks 3 by convection current.Because the gross pressure for being produced by cardiomotility is along with the time changes, so PT changed according to the time.For example, when blood is pumped to into blood vessel, the gross pressure of generation wants high with respect to the pressure existing when logical vasotropic valve is closed.In one embodiment, by calculating the variation of the pressure from minimal flow situation to maximum fluidity situation on time shaft, derive gross pressure.As described in this article, these pressure are derived and have been utilized diameter of the same period (and area) measurement result of blood vessel.This variation or acceleration, together with aortic stroke volume and known elasticity, allow computing equipment 20 to determine gross pressure according to principle well known in the art.Thereby at moment T1, equation PT1=PS1+PD1 can solve PS1, and at moment T2, equation PT2=PS2+PD2 can solve PS2.As indicated above, PS1 and PS2 are respectively heart contraction blood pressure measurement and diastole blood pressure measurement.

Carry out the transmutability that challenge is measured blood vessel diameter of accurately determining of blood pressure.Along with passing through blood vessel pump blood, flexible wall expansion or the contraction of blood vessel, affect blood pressure measurement thus.This impact be according to the variation of blood vessel diameter, occur, the result to the variation of the resistance of blood flow.An embodiment of the present disclosure considers this transmutability when using technology described herein and following method.

As described above, the static pressure on the inwall of blood pressure and in question blood vessel is directly related.Also as explained above, by the gross pressure in blood vessel (PT), carry out calculating blood pressure (PS), gross pressure is static pressure and the dynamic pressure sum (being PT=PS+PD) of blood flow.As described in this article, directly use doppler sensor 70 to measure dynamic pressure.More specifically, PD derives from blood flow (speed) measurement result of the standard relationship between use traffic and pressure.

Static pressure partly depends on the diameter (variation of diameter causes the variation of resistance, and the static pressure that the variable effect of resistance is measured) of blood vessel.As described in this article, under this background, use 2 pairs of blood vessel diameters of optical sensor module to measure.By the diameter of measuring, directly calculate the area that cross section is circular blood vessel substantially.Sensor device 1 of the present disclosure calculates the area of blood vessel at the minimum amplitude (Min1, Min2, Min3) in patient's heart cycle and near the increment place of tight spacing maximum amplitude (Max1, Max2, Max3).More specifically, as depicted in figure 12, the sampling of the amount of measuring by the rate calculations with 50 samplings per second carrys out generation time rate integrating.In each sampling place, this method is determined the area change (by the variation of using optical sensor module 2 to measure diameters) of blood vessel 3 and is flow through increase or the minimizing of speed of the blood 4 of blood vessel 3.In the calculating (embedding of sampling at Min1 place there is shown ten sampling C1-C10) of the independent Area and Speed of sampling place of these tight spacings, allow to determine separately according to the relation of flow=area * speed the flow of blood.Should be appreciated that, each crest of sampling shown in Figure 12 has carried out one group ten similar sampling C1-C10 with trough place.For simply, only ten samplings of a group are depicted with the time shaft of expansion.

Diastole and heart contraction blood pressure measurement are measured corresponding with the time rate integrating that crest (Max1, Max2, Max3) in the sampling shown in the curve chart of Figure 12 and trough (Min1, Min2, Min3) are located respectively.In an embodiment of the present disclosure, at crest place, carry out ten samplings (being separated by several milliseconds) and at trough place, carry out ten samplings (being separated by several milliseconds).As depicted in figure 12, each in three pump blood cycles is in succession carried out the sampling of these groups.Certainly, should be appreciated that, depend on that application can be used more or less sampling.Then these samplings are averaging to (or filter and remove irrelevant sampling in some way) and determine the flow of the sampling of each measurement.

According to known formula a=v ²/ r determines that each that measure in sequence samples separately the acceleration of the blood of next sampling, and wherein v is the speed of blood 4, and r is the radius (as mentioned above, from deriving in the performed measurement of optical sensor module 2) of blood vessel 3.Then according to principle degree of will speed up measurement result well known in the art, be converted to pressure (considering area change and velocity variations on time shaft).This pressure result represents gross pressure (PT), and measures for each the instantaneous diameter of reality (area) that sample has been considered blood vessel 3, thus the potential error of the caused blood pressure of flexibility by blood vessel 3 is compensated.With the PT and the PD that calculate for each sampling as mentioned above, by being related to that PS=PT-PD comes to determine PS for each sampling.The unit of the blood pressure measurement obtaining is gram every cubic millimeter, and converts and can be converted into (1 holder=the 1.3595e-5Kg/mm for example of unit of holder (Torr) according to standard ^Λ2).By ten samplings at crest place being averaging and ten samplings at trough place being averaging and obtaining final PS.This has produced three crest values and three trough values (each being in three cardiac cycle samplings produces).For each cycle, (along with the past of time) has determined that deceleration from crest to trough and (along with the past of time) determined the acceleration from trough to crest subsequently.This has produced three accekerations and three deceleration value.Every triplet is averaging to produce to final PT and the final PT of deceleration of acceleration.

Another aspect of the present disclosure is the acquisition pattern of the Doppler measurement result used in calculating described above.More specifically, use current sensor 1 and the geometry of the measurement of the blood vessel 3 that is just being sampled, native system can be configured to the uncorrelated part of the echo that refusal measured by doppler sensor 70.As described above, the ripple of being launched by the linear array transducer of doppler sensor 70 is propagated in all directions, and is reflected away by the many different structure in propagation path.The part signal that should only the blood flow by measured be reflected is used for determining speed.As described referring to Figure 13, sensor 1 can be isolated one or more transducer sections of the linear transducer arrays that receives this useful data.

Referring now to Figure 13, the optical measurement that the optical sensor module fully described in the related application based on by " optical pickocff " cited above 2 is carried out and learn distance H 1 and H2.More specifically, because the position at the size of sensor 1 and doppler sensor 70 center is known, so can calculate from Doppler and pass sensor 70 center to the distance on every limit of blood vessel 3 by measurement result described herein, that provided by optical sensor module 2.In this example, part transducer 70B, that relevant velocity information is provided of doppler sensor 70 will be determined.The length of transducer 70B represents by label X1, and because it is the actual hardware component that is incorporated into sensor 1, so it is known.The geometrical relationship of use standard, the K shape of computing equipment 20 use of sensor 1 based on transducer 70A, 70B, 70C configuration and the angle [alpha] learnt is calculated triangle H2, X1, the length C of C.Similarly, can determine angle beta.

Because H1 is used optical sensor module 2 as above to measure, thus can also determine angle beta 1 and length B, thus produce triangle H1, X1, all measurement results of B.As described above, the angle that Doppler technology restriction is the measurement of reflected signal should drop in +/-20 degree of flow direction.Sensor 1 use this known features of Doppler technology by represent on transducer 70B, will provide one or more snippets the imaginary point on border about the meaningful information of blood flow velocity to project on transducer 70B.More specifically, by triangle H1, X1, draw straight lines and calculate this straight line and the intersection point of transducer 70B and obtain an Xn at the following 20 degree angle places of limit B of B.Similarly, by triangle H2, X1, draw straight lines and calculate this straight line and the intersection point of transducer 70B and obtain an Xm at the angle places of following 20 degree of limit C of C.One or more sections of transducer 70B between some Xn and Xm and between some Xm and Xl to carrying out autoblood 4, the region of the transducer that the echo of the accurate expression of blood flow velocity receives is provided.Therefore, when being calculated, speed can not consider other section of detected other signal by transducer 70B.

Should be appreciated that due to the pump blood of heart and/or patient's body movement but continuously motion of the blood vessel of measuring according to mode described above.With regard to this point, carry out continually for determine blood flow velocity object and to the determining of one or more dependent segments of transducer 70A, 70B, 70C, and in blood pressure described above calculates the time with each minimum obtain speed sampling.These data can be averaging to produce velocity measurement more accurately.

Another aspect of the present disclosure is in blood pressure measurement, to consider the mode of the curvature of blood vessel 3.Each in describe for the crest place in Figure 12 ten sampling C1-C10, measure the diameter of blood vessels 3 with optical sensor module 2, and with the one or more relevant section measuring flow of doppler sensor 70.Certainly, the time consuming between sampling is also known.The shape of the given blood vessel being detected by optical sensor module described herein 23, the associated reflections that computing equipment 20 can be determined Doppler signal partly by from flow through blood vessel 3 straight part substantially blood or from flowing through the blood place of the sweep of blood vessel 3, reflect away.In the situation that the sensed part of blood vessel 3 is straight substantially, by relation: acceleration=(Δ flow)/(delta time) derived acceleration.In the situation that the sensed part of blood vessel 3 is crooked, Acceleration Formula is acceleration=v ²/ r, wherein r is the radius of blood vessel 3, but is proofreaied and correct by formula w=(ΔΦ)/(delta time), wherein Φ is the curvature angle of blood vessel 3.The result of formula w=(ΔΦ)/(delta time) produces the percentage correction of Acceleration Formula.For example, if w=.3, the Acceleration Formula after proofreading and correct is so a==(v ²/ r) * 1.3.By each sampling depicted in figure 12 is carried out to acceleration calculation, this equipment has been determined the variation of acceleration/deceleration and according to mode described above, this has been identified for calculating gross pressure.

Should be appreciated that, although blood pressure described above calculates, refer to the blood pressure of determining in large artery trunks 3, suppose that pulmonary artery is in the sensing range of monitoring equipment 1, can carry out identical processing and determine the blood pressure in pulmonary artery.Described in the application of " optical pickocff ", monitoring equipment 1 is by measuring the oxygen saturation of pulmonary artery and large artery trunks 3 and determining that the blood which blood vessel carries higher oxygen saturation distinguishes pulmonary artery and large artery trunks 3.The blood vessel that carries the blood of higher oxygen saturation must be large artery trunks 3.In another embodiment of the present invention, monitoring equipment 1 changes the blood vessel (being pulmonary artery) that the blood vessel with lower oxygen saturation is identified as to concern into.Then according to with reference to the identical mode of the described mode of large artery trunks 3, determine Pulmonic position and size.Along with Pulmonic geometry is defined, as measured flowing through the pressure of Pulmonic blood with reference to large artery trunks 3 is described above.

3. communication equipment

Again, with reference to Fig. 8, system 300 is applicable to sending and receiving signal of communication.Communication equipment 30 is for example via the bi-directional communication device of mobile telephone system and/or gps satellite system.Communication equipment 30 comprises the antenna for sending and receiving signal of communication.Signal of communication is wirelessly propagated and a propagation from a plurality of optional external communication devices to one in a plurality of optional external communication devices.

External communication device can be computer 302 or any electronic equipment that can wireless receiving signal of communication, for example, be exemplified as the phone 306 of mobile phone.Phone 306 can also be emergency service switchboard or hospital or medical centre switchboard.Signal of communication refers to the signal of the feature collection with one or more signals or is changed the signal that the information in signal is encoded.For instance,, as restriction, signal of communication does not comprise sound, radio frequency (RF), infrared ray, other wireless medium, and above any combination.External communication device can also be the health outside that is positioned at patient, the TU Trunk Unit that for example clips to patient's belt.TU Trunk Unit can comprise for receiving the receptor from the transmission of communication equipment 30, and for forward the transmitter of signal of communication to another external communication device.TU Trunk Unit can also be fix and be hard-wired, for connecing in succession with Internet connection or with medical personnel's computer direct.Similarly, TU Trunk Unit can receive from medical personnel's signal of communication and signal is sent to communication equipment 30.

Signal of communication from communication equipment 30 can comprise voice message, text message and/or measurement data.The communication being received by communication equipment 30 can comprise order or data, the reference data of for example upgrading.Order for example can comprise the instruction to computing equipment 20, is for example used for carrying out patient's treatment, collection and sends other data or upgrade the task of reference data.

4. energy storage device

Referring again to Figure 1A, 1B and 1C, the system that can be provided for energy storage device to recharge.The energy that computing equipment 20 receives from energy storage device 40.Energy storage device 40 comprises for example energy storage member of battery.Alternatively, sensor device 1 can also comprise the energy coupler that the energy for receiving from external source charges to energy storage device 40.

An example of energy coupler is electromagnetic equipment, and for example sensing coil 42, for receiving external electromagnetic signal 44 and such signal being converted to the electric energy for energy storage member is recharged.External electromagnetic equipment 46 generates electromagnetic signals 44, by energy storage device 40 receiving electromagnetic signals 44 and be converted into electric energy.Energy storage device 40 can provide charge signal to computing equipment 20.Computing equipment 20 can compare charge signal and reference charge signal start for warning patient and/or medical personnel's low electric charge signal of communication.Alternatively, the detector of for example voltage sensor can be used for monitoring the electric charge of energy storage device 40 and to computing equipment 20, provide signal when electric charge is reduced to threshold value following time.Near electromagnetic equipment 46 can being placed on to sensor device 1, energy storage device 40 is charged.

Can alternatively or additionally provide energy with the form of ultrasonic vibration.For example, can comprise piezoelectric transducer at sensor device 1.Ultrasonic vibration can be arranged on to outside.When transducer is driven by ultrasonic vibration, transducer generates electricity.

Although the present invention has been described as have exemplary design, can have revised further the present invention in the spirit and scope of present disclosure.Therefore the application is intended to contain any variation, use or the adaptability revision that the present invention is carried out that uses universal principle of the present invention.In addition, the application be intended to contain fall in the technical field of the invention known or customary practice, with the departing from of present disclosure.

Claims (24)

1. for obtaining a sensor device for signal and computation and measurement result, described sensor device comprises:

Sensor, described sensor is configured to by described patient, externally be supported in patients with implantation or by supporting member, described sensor comprises transducer, described transducer is for sending acoustic energy, receiving acoustic energy and the described acoustic energy receiving is converted to one or more signals, and described transducer is relative to each other arranged at a certain angle;

Computing equipment, which transducer of location positioning being arranged to based on blood vessel will not produce available signal and only from producing the transducer of available signal, send acoustic energy and calculate blood parameters;

Energy storage device is described computing equipment power supply; And

Shell, surrounds described sensor, described energy storage device and described computing equipment.

2. sensor device according to claim 1, wherein each transducer comprises sonic energy source and the window for allowing described acoustic energy to pass through, described sonic energy source be used to stop acoustic energy by and the material that prevents the interference between adjacent transducer partly around.

3. sensor device according to claim 1, wherein said transducer comprises the first transducer and the second transducer, and described the first transducer and described the second transducer send acoustic energy with different frequencies.

4. sensor device according to claim 1, wherein said blood parameters comprises blood flow velocity.

5. sensor device according to claim 4, wherein said sensor device also comprises and is configured to optical pickocff that a plurality of optical signallings are carried out sending and receiving and detect the position of described blood vessel, described sensor device is configured to calculate at the sample place of the minimum amplitude of the cardiac cycle with described patient and near the measurement of the incremental time of the tight spacing maximum amplitude area of described blood vessel, to determine the acceleration of the blood of each sample, and convert described acceleration to blood pressure.

6. sensor device according to claim 1, also comprises the communication equipment for sending and receiving signal of communication.

7. sensor device according to claim 6, wherein said signal of communication comprises the relative position value of the position that represents described blood vessel.

8. sensor device according to claim 7, wherein said computing equipment also maximum gauge and the minimum diameter based on maximum blood flow velocity and minimum blood flow velocity and described blood vessel carrys out calculating blood pressure, wherein said maximum blood flow velocity and minimum blood flow velocity are from pressing corresponding a plurality of blood flow velocity measurement results to calculate respectively with systolic pressure and diastole, described systolic pressure and described diastole press the echo from being detected by the section of transducer to derive, the maximum gauge of described blood vessel and minimum diameter are based on pressing the first range measurements and the second distance measurement result that the corresponding moment obtains to be calculated with described systolic pressure and described diastole.

9. sensor device according to claim 6, wherein said signal of communication comprises alarm.

10. sensor device according to claim 1, wherein said computing equipment is used described blood parameters situation to be diagnosed to and carried out the function that described situation is responded.

11. sensor devices according to claim 10, also comprise the communication equipment for sending and receiving signal of communication, wherein said function comprises at least one in following: transmit alarm, start treatment, apply electric shock, provide medicine and continuously by described communication equipment transmission data.

12. sensor devices according to claim 1, wherein said sensor device comprises adapter, described adapter is applicable to operationally be coupled to one or more in Docking station, the second sensor device and energy source.

13. sensor devices according to claim 1, wherein said shell is configured to for subcutaneous implantation.

14. sensor devices according to claim 1, also comprise energy storage device and energy coupler, and described energy coupler recharges described energy storage device for received energy.

15. 1 kinds for to blood vessel with flow through the equipment that at least one characteristic of the blood of described blood vessel is carried out acoustic measurement, and described equipment comprises:

Shell, has the first side and the second side;

Sensor cluster, be mounted to described shell and comprise one or more transducers, described transducer sends acoustic energy, receives through the acoustic energy of described first side of described shell and described acoustic energy is converted to signal for described the first side through described shell, described sensor cluster comprises optical pickocff, and described optical pickocff comprises that a plurality of emitters and a plurality of detector are to generate a plurality of optical signallings;

The computing equipment being surrounded by described shell, be configured to described one or more transducers to activate, with which transducer of the location positioning based on blood vessel, will not produce available signal and only from producing the transducer of available signal, send acoustic energy and calculate blood parameters, and

Energy storage device, is described computing equipment power supply,

Wherein said shell surrounds described sensor cluster and described computing equipment.

16. equipment according to claim 15, wherein said sensor cluster comprises acoustic energy barrier material and comprises the window for sending and receiving acoustic energy.

17. equipment according to claim 15, wherein said shell is made by acoustic energy barrier material and is comprised the window for sending and receiving acoustic energy.

18. 1 kinds for obtaining the system of signal and computation and measurement result, comprising:

Implant the heart equipment into patient;

Sensor cluster in can patients with implantation, and comprise:

Sensor, described sensor comprises transducer, and described transducer is for sending acoustic energy, receiving acoustic energy and the described acoustic energy receiving is converted to one or more signals, and described transducer is relative to each other arranged at a certain angle; Computing equipment, which transducer of the location positioning of described computing equipment based on blood vessel, by not producing available signal and only sending acoustic energy from producing the transducer of available signal, operates and described one or more signals is processed to obtain the blood flow velocity value of blood mobile in described blood vessel to described one or more transducers;

Energy storage device is described computing equipment power supply; And

Shell, described shell surrounds described sensor, described energy storage device and described computing equipment.

19. systems according to claim 18, described sensor cluster also comprises communication equipment, described communication equipment carries out sending and receiving for the described one or more signals based on obtaining from described transducer to signal of communication.

20. systems according to claim 18, wherein said heart equipment is enclosed among described shell.

21. systems according to claim 18, wherein said sensor and described computing equipment are operationally coupled to the outside described heart equipment that is positioned at described shell.

22. systems according to claim 18, wherein said transducer is selectively activated sending and receiving acoustic energy.

23. 1 kinds of sensor devices that are configured to blood pressure to measure, comprising:

Doppler sensor, described doppler sensor has a plurality of transducers for emission source ripple detection of reflected ripple, and described doppler sensor has the reference position being associated;

Optical pickocff, described optical pickocff comprises a plurality of emitters and for generating a plurality of detectors of a plurality of signals, the second distance between the first distance described in described signal indication between reference position and the nearly wall of blood vessel and the wall far away of described reference position and described blood vessel;

Computing equipment, described computing equipment is configured to determine that for each in a plurality of calculation of pressure described the first distance and described second distance calculate the area of described blood vessel, and the section of definite transducer that the echo from flowing through the blood of described blood vessel is detected, determine thus the speed of described blood, with described speed and described area, carry out calculating blood pressure; And

The position of wherein said sensor device based on blood vessel determines which transducer will not produce available signal and will only from producing the transducer of available signal, transmit ultrasound wave, shell, surrounds described doppler sensor, described optical pickocff and described computing equipment.

24. sensor devices according to claim 23, wherein said blood pressure is maximum gauge and the minimum diameter based on maximum blood flow velocity and minimum blood flow velocity and described blood vessel, wherein said maximum blood flow velocity and minimum blood flow velocity are from pressing corresponding a plurality of blood flow velocity measurement results and calculate respectively with systolic pressure and diastole, described systolic pressure and described diastole are pressed and are derived from the described echo being detected by described doppler sensor, the maximum gauge of described blood vessel and minimum diameter are based on pressing the first range measurements and the second distance measurement result that the corresponding moment obtains to be calculated with described systolic pressure and described diastole.

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