WO2012110162A1 - Single photon counting detector system having improved counter architecture - Google Patents

Single photon counting detector system having improved counter architecture Download PDF

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Publication number
WO2012110162A1
WO2012110162A1 PCT/EP2011/074237 EP2011074237W WO2012110162A1 WO 2012110162 A1 WO2012110162 A1 WO 2012110162A1 EP 2011074237 W EP2011074237 W EP 2011074237W WO 2012110162 A1 WO2012110162 A1 WO 2012110162A1
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Prior art keywords
threshold
readout
detector
photo
readout unit
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Application number
PCT/EP2011/074237
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French (fr)
Inventor
Bernd Schmitt
Original Assignee
Paul Scherrer Institut
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
Application filed by Paul Scherrer Institut filed Critical Paul Scherrer Institut
Priority to US13/985,961 priority Critical patent/US9121955B2/en
Priority to AU2011359088A priority patent/AU2011359088B2/en
Priority to JP2013553817A priority patent/JP5875606B2/en
Priority to CN201180067558.6A priority patent/CN103430533B/en
Priority to EP11805061.6A priority patent/EP2676434B1/en
Publication of WO2012110162A1 publication Critical patent/WO2012110162A1/en

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/24—Measuring radiation intensity with semiconductor detectors
    • G01T1/247—Detector read-out circuitry
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N25/00—Circuitry of solid-state image sensors [SSIS]; Control thereof
    • H04N25/70—SSIS architectures; Circuits associated therewith
    • H04N25/76—Addressed sensors, e.g. MOS or CMOS sensors
    • H04N25/77—Pixel circuitry, e.g. memories, A/D converters, pixel amplifiers, shared circuits or shared components
    • H04N25/772—Pixel circuitry, e.g. memories, A/D converters, pixel amplifiers, shared circuits or shared components comprising A/D, V/T, V/F, I/T or I/F converters
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N25/00—Circuitry of solid-state image sensors [SSIS]; Control thereof
    • H04N25/70—SSIS architectures; Circuits associated therewith
    • H04N25/76—Addressed sensors, e.g. MOS or CMOS sensors
    • H04N25/77—Pixel circuitry, e.g. memories, A/D converters, pixel amplifiers, shared circuits or shared components
    • H04N25/772—Pixel circuitry, e.g. memories, A/D converters, pixel amplifiers, shared circuits or shared components comprising A/D, V/T, V/F, I/T or I/F converters
    • H04N25/773—Pixel circuitry, e.g. memories, A/D converters, pixel amplifiers, shared circuits or shared components comprising A/D, V/T, V/F, I/T or I/F converters comprising photon counting circuits, e.g. single photon detection [SPD] or single photon avalanche diodes [SPAD]
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N5/00—Details of television systems
    • H04N5/30—Transforming light or analogous information into electric information
    • H04N5/32—Transforming X-rays

Definitions

  • the present invention relates to a single photon counting detector system having an improved counter architecture.
  • the present subject matter describes the read out chips and parts of the detector systems for x-ray applications at synchrotrons or with lab equipment (lab diffractometers ) in material sciences, crystallography, non destructive testing and medical applications.
  • the energy of the photons to be detected ranges roughly from about 0.1 to 150 keV.
  • the detectors are hybrid detectors comprising an x-ray sensitive layer (silicon sensor) and readout chips.
  • x-ray sensitive layer silicon sensor
  • readout chips 2-dimensional detectors (pixel detectors) each pixel in the sensor is directly connected (bump bonding or flip chip bonding) to the corresponding pixel in the readout chip.
  • the pixel size is therefore limited by the pixel size in the readout chip, and the number of electronic components per pixel in the readout chip is therefore rather limited as to find a suitable pay-off between the pixel size and
  • the readout chip contains n (either 1-or 2 dimensional) independently working channels. Each channel has a charge sensitive preamp, gain stages and a counter. Each channel can count single photons independently of the other channels. An image requires two phases: 1) acquisition mode (where the counters count the incoming photons) and 2) readout mode (where the counting is disabled and the number of counts per channel are read out) . The readout can overlap the acquisition.
  • a single photon counting detector system comprising :
  • each of said photo- detector diodes having a bias potential interface and a diode output interface, said bias potential interface of each photo-detector diode being connected to a bias potential ;
  • each readout unit cell comprising:
  • a high-gain voltage amplifying means comprising an integration capacitor
  • each line comprising a comparator having an
  • indivudually gateable section which determines the counting intervals for each line of the digital counters .
  • a multiplexing means allowing to access the readout cell unit either on a per pixel basis or for several pixels in parallel to read out the digital counter to a data processing means transfering the data off the chip to the data processing means, in particular external readout electronics which do not form an integral part of the readout unit cells.
  • This detector system overcomes the limitations for pump and probe measurements of todays single photon counting systems. By having more than two independently gateable digital counters it is now possible to measure (probe) at different times during the relaxation of the system (one fixed
  • the individually selectable threshold helps to mitigate or completely
  • the counter at the lower level e.g. half the beam energy
  • the counter at the upper level e.g. 1.5 times the beam energy, counts only the pulses where two photons arrived so close in time that the pulse of the second photon arrived during the pulse of the first photon and the total analogue signal did not fall below the
  • comparator threshold half the beam energy in between the photons causing a pulse height of above 1.5 times the photon energy.
  • the detector system according to the present invention may be adapted for the purpose when the gateable sections are controllable in order to be adapted to pump and probe measurements, wherein for a determined number of readout unit cells the hits during a pump phase are counted in one digital counter and the hits during a probe phase are counted in another digital counter.
  • a further preferred embodiment of the present invention can be achieved when for a determined number of readout unit cells at least two thresholds are set-up to build a window discriminator thereby having one threshold to be set to the lower edge of the window and another threshold to be set to the upper edge of the window.
  • this kind of a dual digital counter enables to count the number of photons having an energy within the energy window by subtracting from the number of counts of the lower threshold the number of counts of the higher threshold.
  • This mode of usage is mainly interesting outside of pump and probe experiments for measurements with x-ray tubes (i.e. laboratory diffractometers ) which have a wider energy spectrum where the higher energies contribute only to the background which can be cut-off by using only photons within a window.
  • x-ray tubes i.e. laboratory diffractometers
  • Another preferred embodiment of the present invention can be achieved when the gate sections are gateable with a fixed frequency signal, preferably an count enable signal which is run with a fixed frequency of e.g. 10 to 200 MHz, with the output of the comparator thereby counting the pulses of the fixed frequency signal only when the analogue signal at the output of the high gain voltage amplifying means is above the threshold which is set-up for the respective comparator.
  • a fixed frequency signal preferably an count enable signal which is run with a fixed frequency of e.g. 10 to 200 MHz
  • the output of the comparator thereby counting the pulses of the fixed frequency signal only when the analogue signal at the output of the high gain voltage amplifying means is above the threshold which is set-up for the respective comparator.
  • This is the so-called time over-threshold-mode where the counter measures the time during which the analogue signal was above the comparator threshold during the acquisition time. For signals with pile up of 2 photons (as explained above) the time during which the signal is above the
  • comparator threshold is longer and the time-over-threshold measurement mode determines exactly this circumstance. The measured time then can be converted into the number of photons. Having the count rate in single photon counting mode from the first counter allows immediately the
  • Figure 1 a schematic view of the design of a photo-detector diode
  • Figure 2 a schematic view of a part of a detector module comprising an array of photo-detector diodes as one of them is shown in Figure 1 ;
  • Figure 3 a schematic view of a design of a readout cell comprising two gateable digital counters
  • Figure 4 a schematic view of a design of a readout cell comprising four gateable digital counters.
  • Figures 1 illustrates schematically the architecture of a photo-detector diode 2 having a doped semiconductor p + , n ⁇ , n ++ trespassing section 4.
  • the most commonly used material is a silicon crystal but also germanium, gallium arsenide or cadmium telluride are used.
  • An incident photon 6 having an energy in the range of 100 eV to several KeV before entering the doped semiconductor p + , n ⁇ , n ++ trespassing section 4 passes through a possible cover layer (e.g. aluminum) 8 and causes according to its energy and to the energy needed to create an electron hole pair a respective number of electron hole pairs 10 after x-ray absorption.
  • this number of electron hole pairs is exemplarily shown by three electron-hole pairs 10 being divided by the electrical field generated by a source of bias potential 12.
  • Figure 2 shows a schematic view of a two-dimensional pixel detector 14 having a number of photo-detector diodes 2 arranged in an array of n rows and m columns.
  • the photo detector diodes 2 have a length 1 and a width w of about 25- 200 ⁇ and a height of about 200 ⁇ to 2 mm.
  • a readout chip 16 having a corresponding number of readout unit cells RO is arranged for collecting the charge from the electron hole pairs 10 generated in the respective photo-detector diodes 2.
  • FIG. 3 illustrates schematically the design of a readout unit cell RO comprising two lines 30, 32 of digital counters 34, 36.
  • the charge generated in the photo detector diode 2 by the x-ray is amplified by a low noise charge sensitive amplifier ampl where the charge is integrated on the integration capacitance Ci nt .
  • a feedback resistor who's value can be changed by the voltage applied to Rgpr discharges the capacitor, therefore, forming a pulse at the input of the capacitor CI.
  • the amplifier amp2 then further amplifies the signal with a gain given by the ration of C1/C2.
  • the signals Rgpr and Rgsh change the value of the feedback resitors therefore influencing the discharge time (shaping) and the gain of the amplifiers ampl and amp2.
  • the analogue pulse at the output of amp2 is then feed in parallel into the comparators compl and comp2. Compl and comp2 in all readout cells on a chip have in general the same comparator
  • threshold voltages thresholdl and threshold2 respectively.
  • An individual threshold per cell fine tuning (adjustment) can be done with the help of the per cell programmable digital to voltage converters DAC1 and DAC2 allowing to increase the uniformity of the effective threshold
  • the comparators compl, comp2 each belong to one line 30, 32 of digital counters 34, 36.
  • the two counters 34, 36 per channel are independently gateable by gateable sections 42, 44.
  • One counter 34 measures the pumped and the other counter 36 the unpumped state of pump and probe measurements. This overcomes the limitations for pump and probe measurements of todays single photon counting systems.
  • the counter values are usually read out sequentially such that the multiplex means MM transvers the data of the selected counter to the data processing means which might further serialize the data of the selected counter.
  • the readout chip can have several multiplexing data processing means working in parallel thus increasing the readout speed.
  • the second counter 36 at 1.5 times the beam energy counts only the pulses where two photons arrived so close in time that the pulse of the second photon arrived during the pulse of the first photon and the total analogue signal did not fall below the comparator threshold 38 (half the beam energy) in between the photons causing a pulse height of above 1.5 times the photon energy.
  • having two (or more) counters allows to operate the first counter 34 in standard operation mode (single photon counting) and the second counter 36 in time over threshold mode.
  • the second counter 36 measures the time during which the analogue signal was above the threshold 40 during the acquisition time.
  • measurements can easily be done by gating a fixed frequency signal (this can for example be the count enable signal which is run with a fixed frequency of e.g. 10 to 200 MHz) with the output of the comparator comp2, i.e. counting the pulses of the fixed frequency signal only when the analogue signal is above the threshold 40.
  • a fixed frequency signal this can for example be the count enable signal which is run with a fixed frequency of e.g. 10 to 200 MHz
  • the comparator comp2 i.e. counting the pulses of the fixed frequency signal only when the analogue signal is above the threshold 40.
  • the time-over-threshold measurement measures this.
  • the measured time then can be converted into the number of photons. Having the count rate in single photon counting mode from the first counter 34 allows immediately the determination of the conversion from time-over-threshold mode to number of photons (i.e. single photon counting mode) for low count rates, i.e. the
  • a dual counter system will also be usable as window discriminator, by subtracting from the number of counts of the lower threshold the number of counts of the higher threshold.
  • a multi counter system can also be designed in such a way that one counter can be read out while an other counter acquires data. This allows a dead-time free operation of the system since data can continuously be acquired as
  • the preamp would be reset (i.e. the analogue pulse be cut-off) if the analogue signal is above threshold. This shortens the pulse width of the analogue signal, therefore again increasing the count rate capability .

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Abstract

The present invention relates to a single photon counting detector system (14), comprising: a) a layer of photosensitive material (4); b) an NxM array of photo-detector diodes (2) arranged in said layer of photosensitive material (4); each of said photo-detector diodes (2) having a bias potential interface (12) and a diode output interface, said bias potential interface (12) of each photo-detector diode (2) being connected to a bias potential (Vbias ); c) an NxM array of high gain, low noise readout unit cells (RO), one readout unit cell (RO) for each photo- detector diode (2); d) each readout unit cell (RO) comprising: d1) an input interface (IN) connected to said diode output interface, a high-gain voltage amplifying means (amp) comprising an integration capacitor (Cint ), d2) at least two parallel lines of digital counters, d3) each line comprising a comparator having an individually selectable threshold (threshold1, threshold 2) and a gateable section (gate1, gate2) to determine the counting intervals of the digital counters. e) a multiplexing means allowing to access the readout cell unit either on a per pixel basis or for several pixels in parallel to read out the digital counter to a data processing means transfering the data off the chip to the data processing means, in particular external readout electronics which do not form an integral part of the readout unit cells.

Description

Single photon counting detector system having improved counter architecture
The present invention relates to a single photon counting detector system having an improved counter architecture.
The present subject matter describes the read out chips and parts of the detector systems for x-ray applications at synchrotrons or with lab equipment (lab diffractometers ) in material sciences, crystallography, non destructive testing and medical applications. The energy of the photons to be detected ranges roughly from about 0.1 to 150 keV.
The detectors are hybrid detectors comprising an x-ray sensitive layer (silicon sensor) and readout chips. In case of 2-dimensional detectors (pixel detectors) each pixel in the sensor is directly connected (bump bonding or flip chip bonding) to the corresponding pixel in the readout chip. The pixel size is therefore limited by the pixel size in the readout chip, and the number of electronic components per pixel in the readout chip is therefore rather limited as to find a suitable pay-off between the pixel size and
capabilities of the electronics in the readout chip. In case of microstrip detectors the sensors are usually wire bonded to the readout chip and space is usually limited in the direction perpendicular to the strips. Pixel detectors and strip detectors of that kind are disclosed in the
International Patent Application WO 2004/064 168 Al which is incorporated herewith by reference.
The readout chip contains n (either 1-or 2 dimensional) independently working channels. Each channel has a charge sensitive preamp, gain stages and a counter. Each channel can count single photons independently of the other channels. An image requires two phases: 1) acquisition mode (where the counters count the incoming photons) and 2) readout mode (where the counting is disabled and the number of counts per channel are read out) . The readout can overlap the acquisition.
The largest current problems are:
i) For high incoming photon rates (500 KHz to 3 MHz) the analogue signal starts to pile up and counts get lost. The measured rate therefore has to be corrected (rate
correction) . Above 3 MHz single photon counting systems as implemented today are basically not usable anymore. This is specifically for protein crystallography a problem. Due to the pixel to pixel variations in the effective parameters of the transistors there are also pixel to pixel variations of the shaping time. Since the rate correction measurements are quite difficult, they are made for an average shaping time of all the pixels. Therefore, the shaping time correction can only slightly extend the linear counting region as a function of the incoming photon rate. ii) For pump and probe measurements a sample is excited (pumped) and then after a selectable time the counting is enabled for a short period (probe) . This is then repeated as often as required for the collection of the statistics and only then read out. Since usually the conditions are not constant or the sample degrades (e.g. tensile tests or fatigue measurements in powder diffraction) it is necessary to make (at least) 2 measurements quasi simultaneously (usually pumped and unpumped) . This is currently not possible at high repetition rates of the pump signal since the counts can only be accumulated in a single counter per pixel making a readout for each probe interval and an offline summation of the pumped and unpumped intervals necessary. Since for the pump and probe measurements the statistic is usually very limited the pump repetition rate needs to be maximized which prevents a readout for each interval (both pumped and unpumped) . Also for rapidly changing systems the possibility of reading the detector out for each probe interval is not always given.
It is therefore an objective of the present invention to provide a single photon counting detector system that offers a high sampling rate and copes with the problem of fast changes of counting intervals, in particular in pump and probe measurements .
This objective is achieved according to the present
invention by a single photon counting detector system, comprising :
a) a layer of photosensitive material;
b) an NxM array of photo-detector diodes arranged in said layer of photosensitive material; each of said photo- detector diodes having a bias potential interface and a diode output interface, said bias potential interface of each photo-detector diode being connected to a bias potential ;
c) an NxM array of high gain, low noise readout unit cells, one readout unit cell for each photo-detector diode ;
d) each readout unit cell comprising:
dl) an input interface connected to said diode output interface, a high-gain voltage amplifying means comprising an integration capacitor,
d2 ) at least two parallel lines of digital counters, d3) each line comprising a comparator having an
individually selectable threshold and an
indivudually gateable section which determines the counting intervals for each line of the digital counters .
e) a multiplexing means allowing to access the readout cell unit either on a per pixel basis or for several pixels in parallel to read out the digital counter to a data processing means transfering the data off the chip to the data processing means, in particular external readout electronics which do not form an integral part of the readout unit cells.
This detector system overcomes the limitations for pump and probe measurements of todays single photon counting systems. By having more than two independently gateable digital counters it is now possible to measure (probe) at different times during the relaxation of the system (one fixed
selectable time for each of the counters) . This last option is specifically interesting for measurements with a
continuous beam, like pump and probe measurements in powder di ffraction .
In todays single photon counting detector systems, the problem of pile-up of the analogue signal at high incoming photon rates is an unsolved problem. In a preferred
embodiment of the present invention, the individually selectable threshold helps to mitigate or completely
eliminate the pile-up problem when at least two thresholds are set-up to have one threshold on a level below the photon energy, e.g. about half of the photon energy, and at least another threshold on a level above the beam energy, e.g. about 1.5-times the photon energy. The counter at the lower level, e.g. half the beam energy, is the standard counter as used in todays systems. The counter at the upper level, e.g. 1.5 times the beam energy, counts only the pulses where two photons arrived so close in time that the pulse of the second photon arrived during the pulse of the first photon and the total analogue signal did not fall below the
comparator threshold (half the beam energy) in between the photons causing a pulse height of above 1.5 times the photon energy. By adding the number of counts for the two counters the count rate capability is increased by about a factor of 2 which is a significant improvement.
As already mentioned further above, the handling of pump and probe measurements have been a serious problem with todays single photon counting detector systems. The detector system according to the present invention may be adapted for the purpose when the gateable sections are controllable in order to be adapted to pump and probe measurements, wherein for a determined number of readout unit cells the hits during a pump phase are counted in one digital counter and the hits during a probe phase are counted in another digital counter. When talking about a determined number of readout unit cells, in most of the applications all readout unit cells are addressed but there are envisionable examples that may require only subgroups of the readout unit cells having the gateable sections controlled accordingly, such as subgroups in a region of interest.
A further preferred embodiment of the present invention can be achieved when for a determined number of readout unit cells at least two thresholds are set-up to build a window discriminator thereby having one threshold to be set to the lower edge of the window and another threshold to be set to the upper edge of the window. For photon intensities which do not cause pile up, this kind of a dual digital counter enables to count the number of photons having an energy within the energy window by subtracting from the number of counts of the lower threshold the number of counts of the higher threshold. This mode of usage is mainly interesting outside of pump and probe experiments for measurements with x-ray tubes (i.e. laboratory diffractometers ) which have a wider energy spectrum where the higher energies contribute only to the background which can be cut-off by using only photons within a window. At synchrotron, for some
applications, like e.g. Laue diffraction, which have a certain energy range of the photons, it might also be advantageous to count photons only in a certain energy window .
Another preferred embodiment of the present invention can be achieved when the gate sections are gateable with a fixed frequency signal, preferably an count enable signal which is run with a fixed frequency of e.g. 10 to 200 MHz, with the output of the comparator thereby counting the pulses of the fixed frequency signal only when the analogue signal at the output of the high gain voltage amplifying means is above the threshold which is set-up for the respective comparator. This is the so-called time over-threshold-mode where the counter measures the time during which the analogue signal was above the comparator threshold during the acquisition time. For signals with pile up of 2 photons (as explained above) the time during which the signal is above the
comparator threshold is longer and the time-over-threshold measurement mode determines exactly this circumstance. The measured time then can be converted into the number of photons. Having the count rate in single photon counting mode from the first counter allows immediately the
determination of the conversion from time over threshold mode to single photon counting mode for low count rates, i.e. the calibration of the time-over-threshold counter with the single photon counter. This allows to extend the count rate capability of single photon counting systems at synchrotrons to a level where pile up is not a problem anymore .
Further preferred embodiments of the present invention can be taken from the remaining depending claims.
Preferred embodiments of the present invention are
hereinafter discussed in more detail with reference to the following drawings which depicts in:
Figure 1 a schematic view of the design of a photo-detector diode ;
Figure 2 a schematic view of a part of a detector module comprising an array of photo-detector diodes as one of them is shown in Figure 1 ;
Figure 3 a schematic view of a design of a readout cell comprising two gateable digital counters; and
Figure 4 a schematic view of a design of a readout cell comprising four gateable digital counters.
Figures 1 illustrates schematically the architecture of a photo-detector diode 2 having a doped semiconductor p+, n~, n++ trespassing section 4. The most commonly used material is a silicon crystal but also germanium, gallium arsenide or cadmium telluride are used.
An incident photon 6 having an energy in the range of 100 eV to several KeV before entering the doped semiconductor p+, n~, n++ trespassing section 4 passes through a possible cover layer (e.g. aluminum) 8 and causes according to its energy and to the energy needed to create an electron hole pair a respective number of electron hole pairs 10 after x-ray absorption. In the drawings, this number of electron hole pairs is exemplarily shown by three electron-hole pairs 10 being divided by the electrical field generated by a source of bias potential 12.
Figure 2 shows a schematic view of a two-dimensional pixel detector 14 having a number of photo-detector diodes 2 arranged in an array of n rows and m columns. The photo detector diodes 2 have a length 1 and a width w of about 25- 200 μπι and a height of about 200 μπι to 2 mm. Below the plane of these photo-detector diodes 2 a readout chip 16 having a corresponding number of readout unit cells RO is arranged for collecting the charge from the electron hole pairs 10 generated in the respective photo-detector diodes 2. The electrical conjunction between a diode output interface of the photo-detector diodes 2 and an input interface IN of the readout unit cell RO is achieved by bump bonding using for example indium bumps 24. Figure 3 illustrates schematically the design of a readout unit cell RO comprising two lines 30, 32 of digital counters 34, 36. The charge generated in the photo detector diode 2 by the x-ray is amplified by a low noise charge sensitive amplifier ampl where the charge is integrated on the integration capacitance Cint. A feedback resistor who's value can be changed by the voltage applied to Rgpr discharges the capacitor, therefore, forming a pulse at the input of the capacitor CI. The amplifier amp2 then further amplifies the signal with a gain given by the ration of C1/C2. The signals Rgpr and Rgsh change the value of the feedback resitors therefore influencing the discharge time (shaping) and the gain of the amplifiers ampl and amp2. The analogue pulse at the output of amp2 is then feed in parallel into the comparators compl and comp2. Compl and comp2 in all readout cells on a chip have in general the same comparator
threshold voltages thresholdl and threshold2 respectively. An individual threshold per cell fine tuning (adjustment) can be done with the help of the per cell programmable digital to voltage converters DAC1 and DAC2 allowing to increase the uniformity of the effective threshold
fluctuations caused by variations in the transitor
parameters on the chip. The comparators compl, comp2 each belong to one line 30, 32 of digital counters 34, 36. For pump and probe measurements the two counters 34, 36 per channel are independently gateable by gateable sections 42, 44. One counter 34 measures the pumped and the other counter 36 the unpumped state of pump and probe measurements. This overcomes the limitations for pump and probe measurements of todays single photon counting systems.
Due to the large number of counter cells in a readout chip and the limited number of readout pins the counter values are usually read out sequentially such that the multiplex means MM transvers the data of the selected counter to the data processing means which might further serialize the data of the selected counter. The readout chip can have several multiplexing data processing means working in parallel thus increasing the readout speed.
Having more than two independently gateable counters 34, 36, 46 (see Figure 4) also allows to measure (probe) at
different times during the relaxation of the system (one fixed selectable time for each of the counters) . This last option is specifically interesting for measurements with a continuous beam, like pump and probe measurements in powder diffraction and is shown in Figure 4. Having two or more counters 34, 36, 46 also allows to measure the pile-up of the analogue signal by using for one counter 34 a first threshold 38 of half the beam energy (standard value) and for the second counter 36 a second threshold 40 of 1.5 times the beam energy. The counter 34 at half the beam energy is the standard counter as used in todays systems. The second counter 36 at 1.5 times the beam energy counts only the pulses where two photons arrived so close in time that the pulse of the second photon arrived during the pulse of the first photon and the total analogue signal did not fall below the comparator threshold 38 (half the beam energy) in between the photons causing a pulse height of above 1.5 times the photon energy. By adding the number of counts for the two counters the count rate capability is increased by about a factor of 2 which is a significant improvement.
Further, having two (or more) counters allows to operate the first counter 34 in standard operation mode (single photon counting) and the second counter 36 in time over threshold mode. In time over-threshold-mode, the second counter 36 measures the time during which the analogue signal was above the threshold 40 during the acquisition time. These
measurements can easily be done by gating a fixed frequency signal (this can for example be the count enable signal which is run with a fixed frequency of e.g. 10 to 200 MHz) with the output of the comparator comp2, i.e. counting the pulses of the fixed frequency signal only when the analogue signal is above the threshold 40. For signals with pile up of two photons (as above) the time during which the signal is above threshold is longer and the time-over-threshold measurement measures this. The measured time then can be converted into the number of photons. Having the count rate in single photon counting mode from the first counter 34 allows immediately the determination of the conversion from time-over-threshold mode to number of photons (i.e. single photon counting mode) for low count rates, i.e. the
calibration of the time-over-threshold counter (second counter 36) with the single photon counter (first counter 34) . This allows to extend the count rate capability of single photon counting systems at synchrotrons to a level where pile up is not a problem anymore.
For intensities which do not cause pile up, a dual counter system will also be usable as window discriminator, by subtracting from the number of counts of the lower threshold the number of counts of the higher threshold.
A multi counter system can also be designed in such a way that one counter can be read out while an other counter acquires data. This allows a dead-time free operation of the system since data can continuously be acquired as
illustrated in Figure 4.
A possible option for all single photon counting systems is an active reset of the preamp. The preamp would be reset (i.e. the analogue pulse be cut-off) if the analogue signal is above threshold. This shortens the pulse width of the analogue signal, therefore again increasing the count rate capability .

Claims

Patent claims
1. A single photon counting detector system (14),
comprising :
a) a layer of photosensitive material (4);
b) an NxM array of photo-detector diodes (2) arranged in said layer of photosensitive material (4); each of said photo-detector diodes (2) having a bias potential
interface (12) and a diode output interface, said bias potential interface (12) of each photo-detector diode (2) being connected to a bias potential (Vbias)
c) an NxM array of high gain, low noise readout unit cells (RO) , one readout unit cell (RO) for each photo-detector diode ( 2 ) ;
d) each readout unit cell (RO) comprising:
dl) an input interface (IN) connected to said diode
output interface, a high-gain voltage amplifying means (amp) comprising an integration capacitor
Figure imgf000013_0001
d2 ) at least two parallel lines of digital counters, d3) each line comprising a comparator having an
individually selectable threshold (thresholdl, threshold2) and a gateable section (gatel, gate2) to determine the counting intervals of the digital counters individually for each line of counters. e) a multiplexing means allowing to access the readout cell unit either on a per pixel basis or for several pixels in parallel to read out the digital counter to a data processing means transfering the data off the chip to the data processing means, in particular external readout electronics which do not form an integral part of the readout unit cells.
2. The detector system according to claim 1 wherein at least two thresholds are set-up to have one threshold on a level of about half of the photon energy and at least another threshold on a level of about 1.5-times the photon energy.
3. The detector system according to claim 1 or 2 wherein the gateable sections are controllable in order to be adapted to pump and probe measurements, wherein for a determined number of readout unit cells (including all) the hits during a probe phase (pumped) are counted in one digital counter and the hits during another probe (unpumped, i.e. without the pumping of the sample) phase are counted in another digital counter .
4. The detector system according to any of the preceding claims wherein for a determined number of readout unit cells (including all) at least two thresholds are set-up to build a window discriminator thereby having one threshold to be set to the lower edge of the window and another threshold to be set to the upper edge of the window.
5. The detector system according to any of the preceding claims wherein the gate sections are gateable at a fixed frequency signal, preferably an count enable signal which is run with a fixed frequency of e.g. 10 to 200 MHz, which is gated with the output of the comparator thereby counting the pulses of the fixed frequency signal only when the analogue signal at the output of the high gain voltage amplifying means (amp) is above the threshold which is set-up for the respective comparator (compl, comp2, comp4) .
6. The detector system according to any of the preceding claims wherein the multiplexing and data processing means allow the readout of one line of counters while the other line of counters is used for the next acquisition of data.
7. The detector system according to any of the preceding claims wherein the charge integrating amplifier ampl is individually reset for each cell by the cell's comparator the signal at the comparator input is above the comparator threshold .
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