초록 ▼

A pacemaker programmer and diagnostic system retrieves information stored within a pacemaker and analyzes the retrieved data in real time. The stored information can be retrieved by means of a telemetry communication link. The pacemaker automatically lengthens a post-ventricular atrial refractory pe

A pacemaker programmer and diagnostic system retrieves information stored within a pacemaker and analyzes the retrieved data in real time. The stored information can be retrieved by means of a telemetry communication link. The pacemaker automatically lengthens a post-ventricular atrial refractory period (PVARP). The pacemaker determines atrial capture threshold by generating atrial stimulation pulses while maintaining the ventricular stimulation pulse amplitude at a level known to ensure ventricular capture, and by detecting loss of atrial capture. In response to loss of atrial capture, a processor automatically triggers a premature ventricular contraction (PVC) response to prevent a retrograde P-wave from initiating a pacemaker-mediated tachycardia. Also in response to loss of atrial capture, the processor sets the atrial stimulation pulse amplitude to a value above the atrial capture threshold in a subsequent cardiac cycle, and restores the PVARP to its pre-test value.

대표청구항 ▼

A pacemaker programmer and diagnostic system retrieves information stored within a pacemaker and analyzes the retrieved data in real time. The stored information can be retrieved by means of a telemetry communication link. The pacemaker automatically lengthens a post-ventricular atrial refractory pe

A pacemaker programmer and diagnostic system retrieves information stored within a pacemaker and analyzes the retrieved data in real time. The stored information can be retrieved by means of a telemetry communication link. The pacemaker automatically lengthens a post-ventricular atrial refractory period (PVARP). The pacemaker determines atrial capture threshold by generating atrial stimulation pulses while maintaining the ventricular stimulation pulse amplitude at a level known to ensure ventricular capture, and by detecting loss of atrial capture. In response to loss of atrial capture, a processor automatically triggers a premature ventricular contraction (PVC) response to prevent a retrograde P-wave from initiating a pacemaker-mediated tachycardia. Also in response to loss of atrial capture, the processor sets the atrial stimulation pulse amplitude to a value above the atrial capture threshold in a subsequent cardiac cycle, and restores the PVARP to its pre-test value. Guzelsu et al., 600/473; US-6393315, 20020500, Aprahamian et al., 356/402 ording to claim 1 wherein said effective wavelength emitted by said light source is in the near-ultraviolet, visible, or near-infrared spectral ranges. 9. The method according to claim 7 wherein said effective wavelength emitted by said light source is in the near-ultraviolet, visible, or near-infrared spectral ranges. 10. The method according to claim 1 wherein said light source is a modulated laser that produces periodic frequency pulses of a laser beam in a range from dc to about 100 kHz. 11. The method according to claim 1 wherein said step of comparing includes generating a baseline signal transfer function, H(f), by obtaining frequency-scan data from said reference sample with known radiometric and dynamic (ac) luminescence properties and frequency response; and comparing said portion of a surface and said known healthy portion of a tooth by means of ratios of photothermal amplitudes, ratios of luminescence amplitudes, and phase differences between photothermal phases and luminescence phases at different frequencies for cancellation of the instrumental frequency response. 12. A simultaneous photothermal radiometric and luminescence method for imaging of a tooth surface and detection of the tooth defects intraorally, comprising the steps of: scanning a tooth surface intraorally by irradiating the tooth surface with a light source at fixed frequency wherein a photothermal radiometric signals and luminescence signal is responsively emitted from said tooth; detecting said emitted photothermal radiometric signals and said luminescence signals; demodulating said emitted photothermal radiometric signals into photothermal phase and amplitude signals and said luminescence signals into luminescence phase and amplitude signals using a lock-in amplifier and normalizing said demodulated photothermal phase and amplitude signals and normalizing said demodulated luminescence phase and amplitude signals to cancel light source fluctuations and lock-in amplifier dependencies; and comparing said normalized photothermal phase and normalized amplitude signals to photothermal phase and amplitude signals of a reference sample and comparing said normalized luminescence phase and normalized amplitude signals to luminescence phase and amplitude signals of a reference sample to determine differences between said portion of said tooth and said reference sample thereby identifying defects in said tooth. 13. The method according to claim 12 wherein upon detecting a defective portion of a tooth such as cracks and fissures in the tooth, carious lesions or decayed portions including treatment of said tooth by; the preparation of the tooth surface for bonding the material by etching using one of a laser or acid, and curing or initiation of curing of a light cured or dual cured composite resin to restore the defect or carious lesion or to seal the fissure or defect in question. 14. A device for photothermal radiometric and luminescence for inspection of teeth, comprising the steps of: a light source for irradiating a portion of a surface of a tooth with an effective wavelength wherein photothermal radiometric signals and luminescence signals are responsively emitted from said portion of the tooth; detection means for detecting said emitted photothermal signals and said luminescence signals; demodulating means for demodulating said emitted photothermal signals into photothermal phase and amplitude components and said luminescence signals into luminescence phase and amplitude signals; and processing means for comparing said photothermal phase and amplitude signals to photothermal phase and amplitude signals of a reference sample and comparing said luminescence phase and amplitude signals to luminescence phase and amplitude signals of a reference sample to determine differences between said portion of said tooth and said reference sample and correlating said differences with defects in said tooth. 15. The device according to claim 1 4 wherein said light source is a laser emitting in the near-ultraviolet, visible, or near-infrared spectral ranges. 16. The device according to claim 14 wherein said demodulation means is a lock-in amplifier. 17. The device according to claim 14 including a laser for preparation of a defective tooth portion and curing of dental resins. od as claimed in claim 7, wherein a threshold value is used for the first maximum value, which is approximately 50% of the average R peak amplitude of the earlier accepted heart beat detections of the person. 9. A method as claimed in claim 7, wherein the average noise level is calculated during the measurement of the EKG signal, and a threshold value is used for the first maximum value, which is approximately 150% with respect to the average of noise. 10. A method as claimed in claim 7, wherein the same threshold value is used for the minimum value and the second maximum value as for the first maximum value. 11. A method as claimed in claim 7, wherein the time difference between the first sample and the second sample is calculated, and a part of the sample signal is accepted as a heart beat only if the time difference is within the limits defined by the threshold values set for the time difference. 12. An arrangement for detecting a heart beat and calculating heart rate on the basis of the detected heart beats, comprising: at least one measuring electrode for measuring a signal from the skin of one hand of a person, and at least one measuring electrode for measuring a signal from the skin of the other hand, an amplifier connected to said measuring electrodes for amplifying the potential difference of the signals measured by the measuring electrodes for the purpose of forming an EKG signal, an analog-to-digital converter for receiving the signal from the amplifier and for converting the signal into digital format to be a sample signal containing samples, and a computer which is arranged: to read the digital signal and to detect from the sample signal a heart beat candidate, to perform a rationality analysis for the heart beat detection, in which the computer is arranged: to calculate a time difference between the heart beat candidate and the heart beat detection preceding it, and to calculate on the basis of the time difference, a momentary heart rate value, to compare the calculated momentary heart rate value with a median value of the heart rate, which is a median of two or more earlier calculated heart rate values, to accept the heart beat candidate as a heart beat detection, if the momentary heart rate value calculated on the basis of the heart beat candidate is, when compared with the median value, within threshold values of the median value, and to update as the heart rate value the momentary heart rate value calculated on the basis of the accepted heart beat detection, the arrangement further comprising display means connected to the computer and displaying the calculated heart rate value on the basis of the accepted heart beat detections. 13. An arrangement as claimed in claim 12, wherein the computer is arranged to analyze the EKG signal in the rationality analysis using an approximately two-second time window, and to calculate the median value of the heart rate on the basis of the accepted heart beat detections in the time window. 14. An arrangement as claimed in claim 12, wherein the computer is arranged to analyze the EKG signal in the rationality analysis using a time window, and if there are more than one heart beat candidate in the time window, to select as the heart beat detection the heart beat candidate, the heart rate value calculated from which is closest to the valid heart rate value. 15. An arrangement as claimed in claim 12, wherein the computer is arranged to analyze the EKG signal in the rationality analysis using a time window, and if there are more than one heart beat candidate in the time window, to select as the heart beat detection the heart beat candidate, the heart rate value calculated from which is closest to the median of the heart rate. 16. An arrangement as claimed in claim 12, wherein the computer is arranged to analyze the EKG signal in the rationality analysis using a time window, and to calculate the median value of the heart rate on the basis of the accepted heart be at detections in the time window, and to use approximately ten beats a minute as the threshold value of the median. 17. An arrangement as claimed in claim 12, wherein the arrangement is an exercise apparatus comprising handles for supporting the hands during exercise, and measuring electrodes are placed in the handles of the exercise apparatus so that both handles have at least one measuring electrode for setting against the skin of the person's hand for the purpose of measuring the EKG signal. 18. An arrangement as claimed in claim 12, wherein the computer is arranged to read the sample signal one sample at a time until a first sample can be located from the sample signal, which exceeds a threshold value set to a first maximum value of the EKG signal and contains a local maximum, and until a second sample can be located from the sample signal, which is lower than a minimum value of the EKG signal and contains a local minimum, and until a third sample can be located from the sample signal, which exceeds a threshold value set to a second maximum value of the EKG signal and contains a second local maximum, and to accept the part of the sample signal formed by the first, second and third sample as the heart beat candidate. 19. An arrangement as claimed in claim 18, wherein the computer is arranged to use for the first maximum value a threshold value which is approximately 50% of the average R peak amplitude of the earlier accepted heart beat detections of the person. 20. An arrangement as claimed in claim 18, wherein the computer is arranged to calculate the average noise level during the measurement of the EKG signal, and to use for the first maximum value a threshold value which is approximately 150% with respect to the average of noise. 21. An arrangement as claimed in claim 18, wherein the computer is arranged to use the same threshold value for the minimum value and the second maximum value as for the first maximum value. 22. An arrangement as claimed in claim 18, wherein the computer is arranged to calculate the time difference between the first sample and the second sample, and to accept a part of the sample signal as a heart beat detection only if the time difference is within the limits defined by the threshold values set for the time difference.