WO2012036494A2 - Readout method and readout circuit for detecting x-rays with specified energy bands and x-ray sensor using same - Google Patents

Readout method and readout circuit for detecting x-rays with specified energy bands and x-ray sensor using same Download PDF

Info

Publication number
WO2012036494A2
WO2012036494A2 PCT/KR2011/006834 KR2011006834W WO2012036494A2 WO 2012036494 A2 WO2012036494 A2 WO 2012036494A2 KR 2011006834 W KR2011006834 W KR 2011006834W WO 2012036494 A2 WO2012036494 A2 WO 2012036494A2
Authority
WO
Grant status
Application
Patent type
Prior art keywords
output signal
output
ray
comparison
voltage
Prior art date
Application number
PCT/KR2011/006834
Other languages
French (fr)
Korean (ko)
Other versions
WO2012036494A9 (en )
WO2012036494A3 (en )
Inventor
소명진
안태지
Original Assignee
주식회사 룩센테크놀러지
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date

Links

Images

Classifications

    • GPHYSICS
    • G01MEASURING; TESTING
    • G01TMEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16Measuring radiation intensity
    • G01T1/17Circuit arrangements not adapted to a particular type of detector

Abstract

According to the present invention, an X-ray readout integrated circuit comprises: an amplification unit that converts a charge quantity, which was generated from a photodiode when X-rays were incident, into a voltage output signal and outputs the converted signal; comparator unit that compares the voltage output signal with an N preset reference voltage, respectively, and outputs the voltage output signal as an N comparative output signal; a band determination unit that activates a pulse output signal, if the comparative output signals satisfy a determined condition which is set to detect an X-ray of a specific energy band; and a counter unit that counts the number of pulses of the pulse output signal, and outputs photon counting data.

Description

X-ray diagnostic read out the detection of particular energy bands available methods, the read circuit and the X-ray sensor using the same.

The present invention relates to the x-ray sensor, more particularly, to a read out integrated circuit (readout circuit) used for the X-ray sensor.

X-ray sensor is a type of image sensor for creating a digital image by detecting X-rays from the x-ray digital imaging device.

Over X-rays that pass through the subject tissue will reach the photodiode region of the X-ray sensor E that remains in electronics also for (valance band) that receives a photon energy of X-rays beyond the energy gap between the band gap (band gap) conduction band (conduction band ) is excited (excitation) to.

Although the first place, the depletion (depletion) region of the photodiode e (electron) and the hole (hole), due to these excited electrons-hole pairs is generated in much the depletion region. Electron-hole pairs, and the current to flow while moving by the electric field, when detecting the magnitude of this current can be obtained an image of X-rays passing through the subject.

Measurement method of the current due to the incidence of X-rays is a photon counting type (single photon counting mode) has been widely used. Electrons, generated each time a photon corresponding to the energy of the X-ray is incident-converting and amplifying the current according to the flow of holes into a voltage signal, and then input to the comparator. The comparator compares the amplified voltage signal with a reference voltage and outputs a pulse, the counter by counting the output pulses per unit time, a comparator, and measure the magnitude of the incident X-ray. It is less influence of the noise reducing a radiation dose, and can provide the data in digital form.

In the case of the conventional photon counting type readout integrated circuit and is sent out, one pulse in the case using a single comparator, the output value from the amplifier section is greater than a reference voltage, the counter is activated at the rising edge or falling edge of the pulse .

Conventional photon counting type readout integrated circuit, because of this structure, if higher or lower than a reference voltage is amplified output unit is set in advance, that is merely a of the x-ray photon energy distinguish whether higher or lower than the certain energy level, and how much more more detailed information, such as higher does not acquire.

The problem to be solved by the present invention is to provide an X-ray sensor and the X-rays including this read out integrated circuit which is the x-ray photon counting according to the different levels of energy passing through the x-ray band has a subject.

X-ray readout integrated circuit according to an aspect of the invention,

Amplifier section for converting the amount of charge generated in the photodiode when the X-rays are incident on the output voltage signal output;

Comparator for respectively comparing the output voltage signal with a preset reference voltage output to the N of N comparison output signal;

When the comparison output signal is determined to meet the condition set for detecting the X-rays of a particular energy bands, band determination section to enable the pulse output signal; And

It may include a counter that outputs a photon count data by counting the pulse number of the pulse output signal.

According to one embodiment, the determination condition is

When the X-rays of the specific energy range is determined for the sequences that have to compare the output signal may be a condition in which the pulse sequence of the comparison output signal match.

According to one embodiment, the determination condition is

The specific energy compared to the band comparing the reference voltage and the voltage output signal corresponding to the upper limit of the output signal to be detected compared to a not appear when the pulse, comparing the reference voltage for the lower limit of the specific energy band and the voltage output signal the output signal may be a condition that the pulse appears.

According to one embodiment, the band determining section,

Decision circuit for logically determined by whether the comparison output signal to satisfy the determination condition; And

If the amount of charge generated differently depending on the bias of the photodiode work flow of electrons is applied as in the decision circuit of the comparison output signal or the determination circuit to the charge amount is inverting the comparison output signal if the hole flow of the a it may include comparing an output selection circuit for applying.

According to one embodiment,

Wherein the comparison output selection circuit comprises a plurality of two-to-one multiplexer,

Each of the two-to-one multiplexer,

Receiving respective input of the comparison output signal and the inverted comparison output signal, it can be configured by a mode selection signal corresponding to the amount of charge so as to output one of the comparison output signal or the inverted comparison output signal to the determination circuit.

The x-ray sensor according to a further aspect of the present invention may include a X-ray readout integrated circuit in accordance with various embodiments.

X-ray imaging device according to another aspect of the present invention may include a X-ray readout integrated circuit in accordance with various embodiments.

X-ray readout method according to another aspect of the invention,

The step of converting the amount of charge generated by the photodiode into a voltage output signal output when the X-ray is incident;

And outputting to the N comparison output signal in each comparing the output voltage signal with a preset reference voltage of N;

The method comprising, when said comparison output signals are determined to satisfy the condition set for detecting the X-rays of a particular energy band, activating the pulse output signal; And

It may include a step of outputting the photon count data by counting the pulse number of the pulse output signal.

According to the X-ray sensors, including X-ray readout integrated circuit of the present invention as this, the user can make it to be able to detect only the X-ray having desired energy band, common separation images only in certain tissue exposure showing the specific energy band. Therefore, in a conventional X-ray digital post-processing system it may implement a specific tissue who can not image separation.

Figure 1 is a block diagram that schematically illustrates the X-ray readout integrated circuit is capable of detecting multiple-band energy in accordance with an embodiment of the present invention.

Figure 2 is a detailed circuit diagram illustrating parts of the amplification included in the read out X-ray integrated circuit of Figure 1;

3 is a detailed circuit diagram illustrating parts of comparison included in the read out X-ray integrated circuit of Figure 1;

Figure 4 is a detailed circuit diagram illustrating parts of the band is determined to be included in the X-ray readout integrated circuit of Figure 1;

Figure 5 is a detail illustrating the detection of X-rays can read out integrated circuit schematic of a multi-band energy in accordance with another embodiment of the present invention.

6 is a waveform diagram in the case where the X-ray readout integrated circuit according to one embodiment of the present invention to operate as an e (electron) detection mode.

7 is a waveform diagram in the case where the X-ray readout integrated circuit according to one embodiment of the present invention to operate with a hole (hole) detection mode.

With respect to the embodiments of the invention disclosed in detail, specific structural to a functional description will be illustrated for the purpose of illustrating the only embodiment of the invention, embodiments of the present invention can be embodied in various forms and the body the embodiments described be construed as limited to the embodiments are not to.

With reference to the accompanying drawings, it will be described in detail preferred embodiments of the invention. The same reference numerals for the same components of the drawing and description duplicate with respect to the same elements will be omitted.

X-rays have an energy band is unique to that object or tissue while passing through a body or organization. For example, when X-rays pass through the human body, the bones, muscles, blood vessels has an energy level of the different bands. As such X-ray is to have each are converted into energy levels of the different bands, each levels are unique band of the voltage signal generated X-rays are incident on the photo diode with such energy levels, depending on the nature of the organ through.

X-ray readout integrated circuit, and this X-ray sensor using the present invention to a voltage signal generated by the X-ray incident on the photodiode as above, using a characteristic having a unique band according to the type of the object, or tissue, particular from the object or body tissue only a part or tissue of a particular type of material can be detected, it is also possible to create a complete image by a combination of such detection image. This is a digital post-processing system according to the conventional X-ray readout integrated circuit is a non-function. Using a multi-energy X-ray band read out integrated circuit, and the x-ray sensor according to the present invention may provide the potential for new applications in the medical industry, INC.

To this end, the X-ray readout of the present invention an integrated circuit is for the detection of X-rays with an energy band coming within the desired range, when the magnitude of the voltage signal generated by the X-ray entered in the range of the reference voltage, N reference voltages ( VTH_1, VTH_2, ..., it can be used to VTH_N) to detect that voltage signal.

Figure 1 is a block diagram that schematically illustrates the X-ray readout integrated circuit is capable of detecting multiple-band energy in accordance with an embodiment of the present invention.

1, the X-ray readout integrated circuit (10) comprise a sensor unit 11, an amplification section 12, a comparison section 13, band determination section 14 and the counter 15 includes a photodiode can.

Sensor unit 11 generates an output electric charge (Q IN) when the X-ray is incident. Amplification unit 12 outputs a charge output (QIN) and convert the amplified output voltage (CSAOUT) into a voltage signal accept. Comparison unit 13 is the reference voltage set by voltage output (CSAOUT) of the amplifying unit 12 in advance (VTH_1, VTH_2, ..., VTH_N), and the comparison result of N compare outputs (COMP_1 compared respectively, COMP_2, ..., and outputs the COMP_N).

A band judging unit 14, a comparison unit (13) if within the scope of at least one reference voltage corresponding to a specific energy band, a peak of the voltage output signal (CSAOUT) due to the applied X-rays exist, that is, when the comparison output (COMP_1, COMP_2, ..., COMP_N) satisfies the determination conditions set in order to detect the X-rays of a particular energy range, and activates the pulse output (COMP_D).

Specifically, band determination section 14 is the one when, for corresponding to the energy band to be detected is an energy band of an incident X-rays for example, to match the determined sequence of the thermometer code (thermometer code or unary) how the pulse output (COMP_D ) it generates.

For example, if the pulse sequence is of 011 111 N = 6 of comparison output by which the incident X-ray, the energy band of the incident X-rays can be determined to be between the first and the second reference voltage. If the band determining section 14 determines the sequence 011 111 is set to be detected in a band judging unit 14 outputs the determination and enable to be the energy band to be detected is an energy band of an incident X-ray pulse output (COMP_D). If, on the other hand, the range determining section 14 determines a sequence to be detected is set at 000 111, for the pulse sequence of comparison of the output from the preceding zone determining section 14 does not output an active output pulse (COMP_D).

Determining a sequence that is set to band determination section 14 may be also set to have any range. For example, to detect the X-rays with an energy band coming between the first and fourth reference voltages may be set to a thermometer code sequence between 000011 to 0111111. Furthermore, it may set the non-contiguous sequence is determined corresponding to the non-continuous energy bands.

In addition, the band determining section 14 inverts the pulse input of the comparison output to be applied in response to the sensor unit 11, the charge output mode selection signal (Polarity) indicating the polarity of the type and voltage signal (Q IN) is generated in the Let there be entered.

Counter 15 counts the pulse output (COMP_D) output from the band determining section 14 outputs a photon count data. Photon count data, so corresponding to the X-ray is incident to the number of times per unit time in a specific energy band, in other words, it corresponds to the amount of X-rays having the energy band that is exposed in a unit time in the photodiode region.

When arranged in a matrix receives the photon count data for each pixel of the image there is only the x-ray with a specific energy band can be obtained.

Figure 2 is a detailed circuit diagram illustrating parts of the amplification included in the read out X-ray integrated circuit of Figure 1;

2, the photodiode charge input (QIN) which (Photo Diode) (21) is generated by the X-ray irradiation of the sensor unit 11 is of the operational amplifier (22) is input to the terminal (). (+) Terminal of the operational amplifier 22 is grounded. And the output terminals of the operational amplifier 22 (-) between the terminal of the feedback capacitor (CF) and a feedback resistance (RF) is connected.

Feedback capacitor (CF) is a charge accumulation type (QIN) generated in the photodiode 21 of the sensor unit 11. (-) of the operational amplifier 22, terminal (+) terminal and a virtual ground state is due to the feedback capacitor (CF) voltage is an operation that occurs across the feedback capacitor (CF) by the accumulated charge input (QIN) in It appears at the output of the amplifier 22. Voltage output (CSAOUT) of the amplifying section 12 can be obtained by integrating electric charges / the capacitance, that is CSAOUT = QIN / CF. Thereby it is obtained an energy band of the incident X-ray is converted into the form of a voltage signal according to the charge amount.

Feedback resistance (RF) determines the time constant (time constant) of the feedback capacitor (CF). For the coefficients of the next turn, the feedback resistance (RF) is used up to the charge stored in the feedback capacitor (CF) within the time determined by the time constant.

3 is a detailed circuit diagram illustrating parts of comparison included in the read out X-ray integrated circuit of Figure 1;

Referring to Figure 3, the comparison section 13 includes a plurality of first, second to the N-th comparator (COMPARATOR) (31, 32, 33). Each of the comparators 31, 32 and 33 is the voltage output (CSAOUT) respectively amplified in the amplifying section 12 to the positive terminal is applied in common. (-) of each comparator (31, 32, 33) of the terminal, each of the first reference voltage (VTH_1), the second reference voltage (VTH_2), to the N-th reference voltage (VTH_N) is applied.

A first comparator (31) than the voltage output (CSAOUT) a first reference voltage (VTH_1) as compared with the first reference voltage (VTH_1) of a relatively highest level, the voltage output (CSAOUT) of the amplifying section 12 It outputs the first comparison output is high active (COMP_1). The second comparator 32 is greater than the voltage output by (CSAOUT) compared to the two second reference voltage (VTH_2) of the second high level, the voltage output (CSAOUT) a second reference voltage (VTH_2) of the amplifying section 12 and it outputs the second comparison output is high active (COMP_2). The N-th comparator 33 is greater than the voltage output (CSAOUT) relative to the most as compared to the N-th reference voltage (VTH_N) of low level, the voltage output (CSAOUT) the N-th reference voltage (VTH_N) to the amplifying section 12 the high-activator is N compare outputs the output (COMP_N).

Figure 4 is a detailed circuit diagram illustrating parts of the band is determined to be included in the X-ray readout integrated circuit of Figure 1;

4, the band determining section 14 is made up of the N two-to-one multiplexer (MUX) (41, 42, 43) and one decision circuit (44).

When short description of the type of charges generated in accordance with incidence of X-rays from the X-ray readout integrated circuit of the photon counting type as follows. Depending on the bias (bias) voltage across the photodiode of the sensor unit 11, the X-ray generated by the charge output (QIN) is applied to the amplifier unit 12 may be an electronic and or jeonggongil. The kind of charges stored in the feedback capacitor (CF) of the amplification part 12 and the polarity of the voltage output waveform (CSAOUT) different content changes. Then, when the comparison unit 13, the output voltage (CSAOUT) is applied to the comparison outputs (COMP_1 to COMP_N) are different from each other, the polarity change of the edge when the enable, depending on the type of charge. So in spite of having a pulse form varied comparison output according to the type of charge of the comparison unit 13, band determination section 14 is consistent form (that is, regardless of the type of charge enable a rising or falling edge, comparison of the pulse), a pulse output (COMP_D) a comparing unit 13, a comparison unit (13 output mode is eotteohanji introducing the informing mode selecting signal, according to a mode selection signal in order to output that is enabled by displaying) It can be added to the comparison output selection circuit for inverting the output or output as they are.

N number of two-to-one multiplexers 41, 42 and 43 are the first through the N compare outputs (COMP_1 to COMP_N) the same (mode selection signal is at 0), or reversed according to such a mode selection signal (Polarity) and (when the mode select signal 1-yl) constitutes a comparison output selection circuit for outputting a determination signal input.

The first 2 to 1 multiplexer 41 is optionally first determines which one of the two inputs according to a first comparison output (COMP_1) and the first inverted comparison output (COMP_1F) being respectively input to the mode selection signal (Polarity) and outputs as an input signal (DEC_1). The second two to one multiplexer 42, a second comparison output (COMP_2) and the second inverted comparison output selectively a second determination input signal to any one of the two inputs being respectively input a (COMP_2F) according to the mode selection signal ( and outputs it as DEC_2). The N 2-to-1 multiplexer 43 is the N-th comparison output (COMP_N) and the first inverted comparison output selectively the N-th decision input signal to any one of the two inputs being respectively input a (COMP_NF) according to the mode selection signal ( and outputs it as DEC_N).

Judgment circuit 44 judges the input signals to a logic circuit for calculating comparing the determined sequence by the pulse sequence of determining the input signal to determine that satisfies the determination conditions, the pulse sequence of input of N determines the input signal if a predetermined determination If a match is found and the sequence is output to activate the pulse output (COMP_D).

The decision circuit determines the sequence 44 as the baseline of the judgment are determined depending upon to detect, in which the x-ray energy bands as described above can be input into a decision circuit (44).

Figure 5 is a detail illustrating the detection of X-rays can read out integrated circuit schematic of a multi-band energy in accordance with another embodiment of the present invention.

Configuration Referring to Figure 5, which does not include a X-ray readout integrated circuit, and similar to, but the multiplexer in the front end of the decision circuit 44 of the band determination section 14 of FIG. 4 with a band determining section 14 of FIG. 4 have. Therefore, it can be applied to the decision circuit 44 determines the output of the comparison input signal for receiving the other hand, compare unit 13 are straight decision circuit (decision logic) of FIG. In the configuration that a bias of the photodiode of the sensor unit 11 fixed may have any one type of charge flow only occurs because the mode selection signal and comparing the x-ray read out of 5 with no output is required to adopt a selection circuit integrated circuit preferred.

6 is a waveform diagram in the case where the X-ray readout integrated circuit according to one embodiment of the present invention to act as electron detection mode.

Referring to Figure 6, the comparator with the reference voltage and the comparison output of the comparison unit 13, respectively illustrating a case with two.

This voltage output (CSAOUT) in the amplifying section 12 is generated as X-ray is incident on the sensor unit 11.

At this time, the set band determination section 14 for detecting only X-rays having an energy band for a voltage output (CSAOUT) of the amplifying unit 12 falls between the first reference voltage (VTH_1) and the second reference voltage (VTH_2) is.

The first X-ray photons will be in relatively high energy band has a voltage output (CSAOUT) is higher than the first and second reference voltages (VTH_1, VTH_2). The mode selection signal (Polarity) means that this is the charge generated in the sensor unit 11 e, which means that activated when the comparison output to a logic high (high) output from the comparison section 13. Voltage output (CSAOUT) a second reference voltage (VTH_2) than the higher also the If 1 exceeds the reference voltage (VTH_1) each of the second comparison output (COMP_2) and the first comparison output (COMP_1), a second determination, with the input signal (DEC_2) and the first determination signal input (DEC_1) is also a logic high. In this case, the judgment circuit 44 does not output a determination is X-ray photon is not between the first and second reference voltages, and activates the pulse output (COMP_D).

The second X-ray photons will have in the middle energy band voltage output (CSAOUT) has a peak between the first and second reference voltages (VTH_1, VTH_2). Since the voltage output (CSAOUT) 2 higher than the reference voltage (VTH_2) but lower than the first reference voltage (VTH_1), a first comparison output (COMP_1) and first decision input signal (DEC_1) is logic low (low) and a second comparison output (COMP_2) and second decision signal input (DEC_2) is a logic high. In this case, the determination circuit 44 determines that the energy between the two bands of the second X-ray photons of the first and the second reference voltage, and outputs the enable pulse output (COMP_D).

The third X-ray photon is in a relatively low energy band has a voltage output (CSAOUT) has a peak at a lower level than the first and the second reference voltage (VTH_1, VTH_2). Since the voltage output (CSAOUT) first and second reference voltage lower than (VTH_2), the first comparison output (COMP_1) and first decision input signal (DEC_1) and the second comparison output (COMP_2) and the second determining the input signal (DEC_2) are all in logic low. In this case, the determination circuit 44 determines that no between the energy band of the third X-ray photons first and second reference voltage, and maintained without reversing the output pulse (COMP_D).

Well to Figure 6 looking, band determination section determines a condition for 14 to active pulse output (COMP_D) is output from the upper limit corresponds to a specific energy range is determined by comparing the reference voltage and the voltage output signal to be detected, type the signal (or the comparison output signal) does not appear when the pulse for the determination of comparing the reference voltage and the voltage output signal corresponding to the lower limit of the specific energy band input signal (comparison output signal) can be described as conditions in which the pulse appears.

7 is a waveform diagram in the case where the X-ray readout integrated circuit according to one embodiment of the present invention to operate with a hole (hole) detection mode.

7, as when the charge unlike FIG jeonggongil, different from the voltage output, the mode selection for comparing the polarity of the output of the signal 6 and a comparison unit (13).

To X-rays, this output voltage (CSAOUT) generated in the amplification section 12 as incident on the sensor unit 11, in contrast with Figure 6, the output voltage is increased in the negative direction. The more even the reference voltage high energy band has a lower value.

Similarly, band determination section 14 is configured to detect only the X-rays having an energy band for a voltage output (CSAOUT) of the amplifying unit 12 falls between the first reference voltage (VTH_1) and the second reference voltage (VTH_2) is.

The first X-ray photons will be in relatively high energy band has a voltage output (CSAOUT) is lower than the first and second reference voltages (VTH_1, VTH_2). The mode selection signal (Polarity) means that means that the electric charge generated in the sensor unit 11, and a hole, which is activated when the comparison output to a logic low output from the comparison section 13. Voltage output (CSAOUT) the second is lower than the reference voltage (VTH_2) In addition, there is a second and results lower than the first reference voltage (VTH_1) each second comparison output (COMP_2) and logic low, as the first comparison output (COMP_1) in this order , just a two-to-one multiplexer (41, 42) due to reverse comparison output is selected in the second decision signal input (DEC_2) and the first determination signal input (DEC_1) is a logic high. In this case, the judgment circuit 44 does not output a determination is X-ray photon is not between the first and second reference voltages, and activates the pulse output (COMP_D).

The second X-ray photons will have in the middle energy band voltage output (CSAOUT) has a reverse peak between the first and second reference voltages (VTH_1, VTH_2). Voltage output (CSAOUT) is second due to, but lower than the reference voltage (VTH_2) higher than the first reference voltage (VTH_1), the first comparison output (COMP_1) is logic high, the first decision input signal (DEC_1) is a logic low and a second comparison output (COMP_2) is logic low, the second input signal is determined (DEC_2) is a logic high. In this case, the determination circuit 44 determines that the energy between the two bands of the second X-ray photons of the first and the second reference voltage, and outputs the enable pulse output (COMP_D).

The third X-ray photon is in a relatively low energy band has a voltage output (CSAOUT) has a reverse peak at a higher level than the first and the second reference voltage (VTH_1, VTH_2). Since the voltage output (CSAOUT) higher than the first and second reference voltage (VTH_2), the first comparison output (COMP_1) is logic high, the first decision input signal (DEC_1) is at a logic low, the second comparison output ( COMP_1) also a logic high, the first determining signal input (DEC_1) is also a logic low. In this case, the determination circuit 44 determines that no between the energy band of the third X-ray photons first and second reference voltage, and maintained without reversing the output pulse (COMP_D).

The present invention as described above, although been described and specific examples, the present invention is not limited to the embodiment of which various modifications to the described those skilled in the art to which the invention pertains and It can be modified. Accordingly, the scope of the invention should be identified only by the claims set forth below and, on the other equal or equivalent modifications all of which will be within the scope of the invention idea.

Claims (8)

  1. Amplifier section for converting the amount of charge generated in the photodiode when the X-rays are incident on the output voltage signal output;
    Comparator for respectively comparing the output voltage signal with a preset reference voltage output to the N of N comparison output signal;
    When the comparison output signal is determined to meet the condition set for detecting the X-rays of a particular energy bands, band determination section to enable the pulse output signal; And
    X-ray readout integrated circuit including a counter that outputs a photon count data by counting the pulse number of the pulse output signal.
  2. The method according to claim 1, wherein the determination condition is
    When the specific energy band of x-rays is applied to the X-ray readout integrated circuit, characterized in that the condition that the pulse sequence of the comparison output signal matched to the determined sequence that have to compare the output signal.
  3. The method according to claim 2, wherein the determination condition is
    The specific energy compared to the band comparing the reference voltage and the voltage output signal corresponding to the upper limit of the output signal to be detected compared to a not appear when the pulse, comparing the reference voltage for the lower limit of the specific energy band and the voltage output signal the output signal X-ray readout integrated circuit, characterized in that the pulse condition may appear.
  4. The method according to claim 1, wherein the bandwidth determination unit,
    Decision circuit for logically determined by whether the comparison output signal to satisfy the determination condition; And
    If the amount of charge generated differently depending on the bias of the photodiode work flow of electrons is applied as in the decision circuit of the comparison output signal or the determination circuit to the charge amount is inverting the comparison output signal if the hole flow of the a X-ray readout integrated circuit comprising a comparison circuit for applying the output selected.
  5. The method according to claim 4, wherein said comparison output selection circuit comprises a plurality of two-to-one multiplexer,
    Each of the 2-to-1 multiplexer
    It said comparison output signal and characterized in that is configured to output one of the comparison output signal or the inverted comparison output signal by a mode selection signal according to the received respective inputs said inverted comparison output signal, the amount of charge in the decision circuit X-ray readout integrated circuit.
  6. X-ray sensor comprising an X-ray readout integrated circuit according to any one of claims of claims 1 to 5.
  7. X-ray image pickup apparatus comprising a X-ray readout integrated circuit according to any one of claims of claims 1 to 5.
  8. The step of converting the amount of charge generated by the photodiode into a voltage output signal output when the X-ray is incident;
    And outputting to the N comparison output signal in each comparing the output voltage signal with a preset reference voltage of N;
    The method comprising, when said comparison output signals are determined to satisfy the condition set for detecting the X-rays of a particular energy band, activating the pulse output signal; And
    X-ray readout method comprising the step of outputting the photon count data by counting the pulse number of the pulse output signal.
PCT/KR2011/006834 2010-09-17 2011-09-16 Readout method and readout circuit for detecting x-rays with specified energy bands and x-ray sensor using same WO2012036494A9 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
KR10-2010-0091737 2010-09-17
KR20100091737A KR101100580B1 (en) 2010-09-17 2010-09-17 X-ray readout integrated circuit and method for detecting x-rays with specified energy bands and x-ray sensor using the same

Publications (3)

Publication Number Publication Date
WO2012036494A2 true true WO2012036494A2 (en) 2012-03-22
WO2012036494A3 true WO2012036494A3 (en) 2012-06-21
WO2012036494A9 true WO2012036494A9 (en) 2012-09-07

Family

ID=45507186

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/KR2011/006834 WO2012036494A9 (en) 2010-09-17 2011-09-16 Readout method and readout circuit for detecting x-rays with specified energy bands and x-ray sensor using same

Country Status (2)

Country Link
KR (1) KR101100580B1 (en)
WO (1) WO2012036494A9 (en)

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2006101926A (en) * 2004-09-30 2006-04-20 M & C:Kk Radiation detector, radiation image diagnostic device and generation method of radiation image
US20090140155A1 (en) * 2007-12-03 2009-06-04 Canon Kabushiki Kaisha Radiation imaging apparatus and its driving method and program

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2006101926A (en) * 2004-09-30 2006-04-20 M & C:Kk Radiation detector, radiation image diagnostic device and generation method of radiation image
US20090140155A1 (en) * 2007-12-03 2009-06-04 Canon Kabushiki Kaisha Radiation imaging apparatus and its driving method and program

Also Published As

Publication number Publication date Type
WO2012036494A9 (en) 2012-09-07 application
KR101100580B1 (en) 2011-12-29 grant
WO2012036494A3 (en) 2012-06-21 application

Similar Documents

Publication Publication Date Title
US6657200B2 (en) Readout system for solid-state detector arrays
JP2006101926A (en) Radiation detector, radiation image diagnostic device and generation method of radiation image
US7326903B2 (en) Mixed analog and digital pixel for high dynamic range readout
US20050105687A1 (en) Computer tomograph comprising energy discriminating detectors
US20100181491A1 (en) Digitizer for a digital imaging system
Judenhofer et al. Evaluation of high performance data acquisition boards for simultaneous sampling of fast signals from PET detectors
Jordanov et al. Digital pulse-shape analyzer based on fast sampling of an integrated charge pulse
US8988267B1 (en) Signal processing device and signal processing method
US20080265169A1 (en) Multi-functional radiation/photon identifying and processing application specific integrated circuit and device
CN101680956A (en) Digital pulse processing for multi-spectral photon counting readout circuits
Popov et al. Readout electronics for multianode photomultiplier tubes with pad matrix anode layout
Streun et al. Coincidence detection by digital processing of free-running sampled pulses
CN101893972A (en) Sensing method of a capacitance type touch control screen and driving circuit
US20030053587A1 (en) CT-data pick-up
Fallu-Labruyere et al. Time resolution studies using digital constant fraction discrimination
US6576907B1 (en) High count rate gamma camera system
US20100065746A1 (en) Systems and methods for calibrating a silicon photomultiplier-based positron emission tomography system
Wong et al. Feasibility of a high-speed gamma-camera design using the high-yield-pileup-event-recovery method
US20100270473A1 (en) Method and circuit arrangement for determining an intensity of ionizing radiation
US6324244B1 (en) Computed tomography apparatus
US20110168909A1 (en) X-ray detector
US20080191139A1 (en) X- or gamma-ray detector
US7138635B2 (en) Detector module for CT and/or PET and/or SPECT tomography
JPH09230052A (en) Different kind ray discriminating radiation detector
US4454423A (en) Circuit arrangement for a radiation detector

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 11825454

Country of ref document: EP

Kind code of ref document: A2

NENP Non-entry into the national phase in:

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 11825454

Country of ref document: EP

Kind code of ref document: A2